JPH0481682A - Radioactive ray detecting endoscope - Google Patents

Abstract

PURPOSE:To detect even weak radioactive rays by detecting radioactive rays at the tip of an insertion unit and converting the radioactive rays into electric signals at the tip. CONSTITUTION:Radioactive rays radiated from a part to be examined are incident from an opening 31 of a collimator 27 into a scintillator 28. A photoelectric conversion element 29 photoelectrically converts light from the incident scintillator 28 and outputs it as electric signals to a preamplifier 30. An amplifier 8 amplifies the input signals with a predetermined amplification rate and outputs the amplified signal to a counting circuit. Thus the number of radioactive rays incident to the collimator 27 can be recognized while the opening 31 is directed upward/downward and right/left by an angle wire controller 25 drawing an angle wire 24. Thus a direction of directivity of the scintillator 28 is changed so that it is possible to detect radioactive rays over a wide range without moving a tip 13.

Description

DETAILED DESCRIPTION OF THE INVENTION [Field of Industrial Application] The present invention relates to a radiation detection endoscope with improved radiation dose detection accuracy.

[Prior Art] In recent years, endoscopes (scopes, fiberscopes, or electronic endoscopes) that can diagnose and examine internal organs in body cavities by inserting an elongated insertion section into body cavities have become available.
is widely used. Moreover, it is used not only for medical purposes but also for industrial purposes to observe and inspect objects such as inside pipes of boilers, machines, chemical plans 1 to 1, etc., or inside machines.

By the way, as a means of detecting and diagnosing cancer, the presence of cancer is discovered by labeling substances that specifically gather on cancer cells with radioisotopes and detecting the radiation emitted from cancer cells. .

As a radiation detection endoscope for detecting cancer cells as described above, the applicant has developed a scintillator that emits radiation (scintillation) using radiation in the insertion part and a scintillator that emits light from the scintillator, as shown in Japanese Patent Laid-Open No. 63-252277, for example. We are proposing a device that is equipped with a light kite that guides the light to the proximal base and a photomultiplier tube that photoelectrically converts and amplifies the light guided by the light guide.

According to this radiation detection endoscope, radiation can be detected and an image of the tissue emitting the radiation can be visually recognized, making it extremely useful for discovering and diagnosing cancer.

[Problems to be Solved by the Invention] However, in the above-mentioned radiation detection endoscope, the light from the weak radiation source is attenuated when guided to the light guide, or is mixed with noise, etc., and cannot be accurately transmitted to the photomultiplier. There is a problem in that there are cases where the information is not transmitted to the computer and cannot be detected.

The present invention has been made in view of the above-mentioned points, and an object of the present invention is to provide a radiation detection endoscope that can accurately detect even light from a weak radiation source.

[Means for Solving the Problems] A radiation detecting means is provided at the distal end of the elongated insertion portion to detect radiation and output an electric signal according to the detected radiation, and is capable of changing the detection direction.

[Function] With the above-mentioned configuration, radiation is detected at the distal end of the insertion section, this radiation is converted into an electrical signal at the distal end, and transmitted to the proximal base, and can be transmitted in multiple directions without moving the distal end. It makes it possible to detect radiation.

[Example] Hereinafter, the present invention will be described in detail with reference to the drawings.

1 to 3 show a first embodiment of the present invention, FIG. 1 is a configuration diagram of a radiation detection endoscope device, and FIGS.
The figure is an explanatory diagram of the distal end portion of the radiation detection endoscope.

As shown in FIG. 1, a radiation detection endoscope (hereinafter referred to as an endoscope) 1 includes an elongated and flexible insertion section 2 and an operation section connected to the rear end of this insertion section 2. 3, and an eyepiece section 4 is provided at the rear end of the operation section 3. Further, a flexible universal cord 5 extends from the side of the operating section 3, and a connector 6 is provided at the end of the universal cord 5.

The connector 6 is connected to an amplifier 8 that amplifies an electrical signal, a counting circuit that is connected to the output terminal of the amplifier 8, and a counting circuit that counts the amplified electrical signal, and is connected to the output terminal of this counting circuit 9, and is connected to the output terminal of the counting circuit 9. A display device 10 that displays the count value of 9, and a DC power supply 1 that supplies power to radiation detection means to be described later.
1, and a light source lamp 12 that supplies illumination light to the endoscope 1.
It is designed to be detachably connected to an external unit 7 provided therein.

An observation window 14 and an illumination window 15 are disposed on the distal end surface of the distal end 13 of the insertion section 2, and an objective lens system 16 is disposed inside the observation window 14. An incident end face of an image guide 17 formed of, for example, a fiber bundle is disposed at the image position, a light distribution lens 18 is disposed inside the illumination window 15, and a fiber bundle, for example, is disposed at the rear end face of the light distribution lens 18. light guide 1 by
Nine emission end faces are provided. The tip portion 13 includes:
Furthermore, a radiation detection means 20 that detects radiation and converts it into an electrical signal, and a length measuring element 21 that measures the distance between the distal end surface of the distal end portion 13 and a test portion (not shown) are provided.

The eyepiece section 4 includes an eyepiece lens 22 for observing a subject image.
is disposed, and an output end face of an image guide 17 disposed inside the insertion section 2 and working section 3 is disposed opposite to the eyepiece lens 22.

The light guide 1 is installed inside the insertion section 2, the operating section 3, and the universal cord 5, and has an incident end surface protruding from the connector 6.

The illumination light generated from the light source lamp 12 is condensed and irradiated onto the input end face of the light guide 19, and guided by the light guide 19 to the output end face. rf light distribution lens 1
8 and an illumination window 15 to illuminate a subject (not shown).

As described above, the object image of the object irradiated with illumination light enters the objective lens system 16 through the observation window 14, and the objective lens system 16 directs the image guide 1.
The image is formed on the incident end face of the image kite 17, guided to the outgoing end face by the image kite 17, and observed through the eyepiece lens 22, for example, with the naked eye.

A signal line 23 and an angle wire 24 are connected to the radiation detection means 20.

The signal line 23 is installed inside the insertion section 2, the operation section 3, and the universal cord 5, and is connected to the amplifier 8 and the DC power supply 11 via the connector 6.

The operating section 8 is provided with an angle wire control device 25 for controlling the pulling of the angle wire 24, and the angle wire control device 25 includes a signal line 26 connected to the length measuring element 21, and a signal line 26 connected to the length measuring element 21, A wire 24 is connected thereto.

The radiation detection means 20 includes, for example, a hole formed in a substantially spherical collimator 27 as shown in FIGS. 2 and 3, and a scintillator 28 disposed on the tip side of the hole. It has a structure in which a photoelectric conversion element 29 is disposed on the rear end surface, and a preamplifier 30 is disposed on the rear end of the photoelectric conversion element 29. The collimator 27 is further provided with a shielding member 32 having an opening 31 (described later) in a substantially hemispherical front surface.

Further, the signal line 23 is connected to the preamplifier 30, and the angle wire wires 24 are connected to the collimator 27, for example, in the upper, lower, left, and right directions.

The operation of the endoscope configured in this way will be explained.

The insertion section 2 of the endoscope 1 is inserted into the subject, and the distal end 13 is brought close to the subject (not shown).

The radiation emitted from the subject part enters the scintillator 28 through the opening 31 of the collimator 27.

The scintillator 28 emits light (scintillation) due to the incident radiation as described above, and the emitted light is incident on two photoelectric conversion elements disposed on the rear end surface of the scintillator 28.

The photoelectric conversion element 29 photoelectrically converts the incident light from the scintillator 28 as described above, and outputs it to the preamplifier 30 as an electrical signal.

The preamplifier 30 preamplifies the input electrical signal at a predetermined amplification factor as described above, and outputs the amplified signal to the amplifier 8 via the signal line 23.

The amplifier 8 amplifies the input signal at a predetermined amplification factor as described above, and outputs the amplified signal to the counting circuit 9.

The counting circuit 9 performs counting based on the input signal as described above, and outputs the counting result to the display device 10.

The display device 10 displays the above-mentioned count value.

Thereby, the number of radiations incident on the collimator 27 can be recognized.

Further, the opening 31 of the collimator 27 is oriented vertically and horizontally by the angle wire control device 25 pulling the angle wire 24.

As a result, the direction of directivity of the scintillator 28 changes, making it possible to detect radiation over a wide range without moving the tip 13.

Further, when the direction of the directivity of the scintillator 28 is changed and the maximum value of radiation is detected, the angle wire control device 25 controls the direction of the directivity of the scintillator 28 so that the longitudinal direction of the tip portion 13 coincides with the direction of the directivity of the scintillator 28. The curved portion (not shown) is driven as shown in FIG. 3. As a result, the area to be examined where the maximum value of radiation has been detected can be observed through the observation window 14, objective lens system 16, image guide 17, and eyepiece lens 22.

Further, when the longitudinal direction of the tip section [3] and the direction of the directivity of the scintillator 28 are matched, the length measuring element 21 measures the distance between the subject and the tip surface of the tip section 13. , and outputs this measurement result to the angle wire control device 25 via the signal line 26.

Thereby, even if the object to be examined or the distal end portion 13 moves, the angle wire control device 25 drives the curved portion (not shown) so that the distal end portion 13 follows the object to be examined.

That is, the scintillation is converted into an electrical signal at the rear end surface of the scintillator 28 and output to the amplifier 8 after being preamplified by a preamplifier, so that it is possible to detect even weak light emission (scintillation) and to detect noise. This has the effect that the influence can be reduced, and furthermore, the detection direction can be varied and the radiation generation site can be easily identified.

4 and 5 relate to the second embodiment of the present invention.
The figure is a configuration diagram of the radiation detection endoscope device, and FIG. 5 is an explanatory diagram of the distal end portion of the radiation detection endoscope.

Note that the same reference numerals are used for the same components as those in the above-described embodiment, and the description thereof will be omitted.

As shown in FIG. 5, the distal end portion 13 of the endoscope according to this embodiment has the same radiation detecting means as the radiation detecting means described in the first embodiment, except that the length measuring element described in the first embodiment is removed. Means 20
a, 20b, 20c, and 20d are arranged vertically and horizontally, respectively, and angle wires 24a are connected to the upper and lower positions of the radiation detecting means 20a and 20b.
0. There are angle wires 24.c at the left and right positions of c20d. b
are fixed, and on the rear end surface of the distal end portion 13 are bending wires 41a, 41b41c for bending a curved portion (not shown).
41d are connected to the bottom, left and right, respectively.

Each of the radiation detection means 20a to 20d has a signal line 23.
a, 23b, 23c, and 23d are connected, and this signal line 2
As shown in FIG. 4, 3a to 23d are connected as signal lines 23 to the input terminals of amplifiers 8a, 8b, 8c, and 8d, which are installed inside the external unit 7'' and are similar to the amplifiers described in the first embodiment. It is connected.

The external unit 7' includes the amplifiers 88 to 8d,
A counting circuit 9a similar to the counting circuit described in the Fth embodiment,
9b, 9c, 9d, and a control circuit 42 which controls an angle wire control device 25', which will be described later, using the counted values of the counting circuits 9a to 9d, and outputs the counted value of 1 to the display device 10. A DC power supply 11 and a light source lamp 12 are provided.

The operation section 3 of the endoscope 1 includes the radiation detection means 20.
Angle wire A'24a, 24 connected to a~20d
b and a curved wire 41 .b connected to the tip 13 .
An angle wire control device 25° is provided for controlling the traction of a to 41d using control signals from the control circuit 42. This angle wire control device 25'' is connected to the control circuit 42 by a signal line 43.

The operation of the endoscope configured in this way will be explained.

When searching for the approximate location of a radiation generation site caused by, for example, cancerous tissue in the examined area, the angle wire control device 25' is controlled by the operator, and the angle wire control device 25' is connected to the radiation detection means 20a to 20(''). The fixed angle wires 24a, 24b and the curved wires 41'a to 41d fixed to the tip 13 are pulled.

When the rough position of the radiation generating site can be grasped by this, the control of the angle wire control device 25' is switched to the control circuit 42 provided inside the external unit 7'.

The control circuit 42 controls the radiation detection means 20a,
A control signal is output to the angle wire control device 25' via the signal line 43 so as to pull the angle wire 24a connected to the radiation detecting means 20c and 20d, and the angle wire 24b connected to the radiation detecting means 20c and 20d. (3) to the angle wire control device 25' so as to pull the
A control signal is output via the return line 43.

As a result, the radiation detection means 20a and 20b scan the directional characteristics in the radiation detection direction in the vertical direction, and the radiation detection means 20c and 20d scan the directional characteristics in the radiation detection direction in the horizontal direction.

When the counts of the counting circuits 9a to 9d converge to a predetermined value due to the scanning of the radiation detection means 20a to 20d, the control circuit 42 determines that the directional characteristics of the radiation detection means 20a to 20d are as follows. The curved wire 4 is anchored to the tip 13 so as to be in the longitudinal plane of the tip 13. ], towing a to 41d.

Further, when the count values of the counting circuits 9a to 9d do not converge to a predetermined value, the control circuit 42 controls the counting circuit 9a to 9d.
The radiation detection means 20a to 20 exhibiting a maximum value of ~9d
The curved wire 41a is fixed to the distal end portion 13 such that the directivity characteristic of d is in the longitudinal direction of the distal end portion 13.
~ 41d, repeat from the operation of scanning the directional characteristics of the radiation detection means 20a to 20d in each direction as described above 1-1 in the direction in which the count values of the counting circuits 9a to 9d converge to a predetermined value I'm starting to look for it.

That is, the four radiation detecting means have the effect that the radiation generation site can be specified more accurately, and the subject image of the radiation generation site can be easily observed.

Other configurations, operations, and effects are the same as those of the embodiments described above.

6 and 7 are kept in the third embodiment of the present invention;
The figure is a configuration diagram of the radiation detection endoscope device, and FIG. 7 is an explanatory diagram of the tip of the radiation detection probe.

Note that the same reference numerals are used for the same components as those in the above-described embodiment, and the description thereof will be omitted.

As shown in FIG. 6, in the endoscope 1 of this embodiment, the channel 5 communicates from the distal end 13 of the insertion section 2 to the operating section 3.

For example, an elongated and flexible probe 52 is inserted into the channel 51.

As shown in FIG. 7, a radiation detection means 20 is disposed at the tip 53 of the probe 52, and a signal line 23 is connected to the radiation detection means 20, and an angle wire 24 is connected thereto. .

As shown in FIG. 6, the signal line 23 is installed inside the probe 52 and connected via the connector 54 to the input end of an amplifier 8 installed inside the external unit 7''.

The angle wire 24 is installed inside the probe 52, and is connected via the connector 54 to an angle wire driving means (not shown) of a detection unit driving device 55 installed inside the external uni-sol 7''. There is.

The detection unit driving device 55 further includes the probe 52.
A probe driving means (not shown) for controlling the forward and backward movement of the probe is installed inside the probe.

The input end of the detection unit driving device 55 is connected to the output end of an angle control circuit 56 that outputs a control signal for changing the direction of directivity of the radiation detection means 20,
It is connected to the output end of a linear drive control circuit 57 that outputs a control signal for controlling the advance and retreat of the probe 52.

The input terminal of the angle angle control circuit 56 and the input terminal of the linear drive control circuit 57 output a control signal instructing the directivity direction of the surface number ray detection means 20, and also control the forward and backward movement of the probe 52. It is connected to an input section 58 that outputs a control signal to instruct.

The operation of the endoscope configured in this way will be explained.

The operator inputs the probe 5 from the input section 58 of the external unit 7''.
2. Input the position and direction in which you want to move the radiation detection means 20 installed inside the device.

This allows the input section 58 to control the forward and backward movement of the probe 52 to move the position of the probe 52. ! The Il signal is output to the linear drive control circuit 57, and the radiation detection means 20
A control signal instructing the direction of the directivity is output to the angle control circuit 56.

The detection unit driving device 55 advances and retreats the probe 52 to move the tip 53 of the probe 52 to a predetermined position, and also pulls the angle wire 24 to indicate the directivity direction of the radiation detection means 20. point in a direction.

That is, the distal end portion 13 of the endoscope 1 can direct the direction of radiation detection means 20 toward a subject to be examined that is difficult to approach, or direct radiation to a subject to be examined whose amount of radiation is weak. By bringing the detection means 20 close, it is possible to specify a radiation generating site such as a cancerous area, and the identified radiation generating site can be observed, which has the effect of allowing a detailed radiation detection examination to be performed. .

Other configurations, operations, and effects are the same as those of the embodiments described above.

Note that observation of a subject image using an endoscope is not limited to an image guide, and may be an electronic endoscope using a solid-state image sensor or the like.

Further, the radiation detection means detects radiation and generates an electrical signal J.
＼Anything can be used as long as it can be converted and output.

[Effects of the Invention] As explained above, according to the present invention, the tip of the endoscope,
In other words, by detecting radiation at the position closest to the object to be examined and converting the radiation dose detected at the tip into an electrical signal, the noise characteristics of weak signals are improved. It is possible to detect even weak radiation, and by changing the detection direction, it is possible to easily find and identify the part to be examined.

[Brief explanation of the drawing]

1 to 3 relate to the first embodiment of the present invention, in which FIG. 1 is a configuration diagram of a radiation detection endoscope device, and FIGS.
The figures are explanatory diagrams of the tip of the radiation detection endoscope, Figures 4 and 5.
The figures relate to the second embodiment of the present invention, FIG. 4 is a configuration diagram of a radiation detection endoscope device, FIG. 5 is an explanatory diagram of the tip of the radiation detection endoscope, and FIGS. Regarding the third embodiment of the invention, FIG. 6 is a configuration diagram of a radiation detection endoscope apparatus, and FIG. 7 is an explanatory diagram of the tip of a radiation detection probe. 1... Endoscope 20... Radiation detection means 2
3...Signal line procedure correction section) Page 7 of detailed reading, No. 1. The shielding part in the first line is corrected to "Light shielding material" on July 18, 1990.

Claims (1)

[Claims] 1. A radiation detection endoscope, comprising a radiation detection means that detects radiation at the distal end of an elongated insertion portion, outputs an electrical signal according to the detected radiation, and is capable of varying the detection direction.