JPH02272384A - Radiation detector - Google Patents

Abstract

PURPOSE:To quickly and accurately detect the position of a cancer by providing a radiation attenuating means which gives a directivity to the radiation made incident on a scintillator and driving the scintillator or the radiation attenuating means and displaying data. CONSTITUTION:The radiation whose direction of incidence is limited by a radiation attenuating means 14 is made incident on a scintillator 16 to generate scintillation. The scintillation is led to an optical signal converting means 19 by an optical fiber bundle 18 and is converted to an electric signal. The electric signal is amplified by an amplifier 26 and is counted by a counting means 27, and the operation is performed in a control means 28 based on the condition inputted from a detection condition input means 4. The control means 28 controls a driving means 22 to drive the scintillator 16 or the radiation attenuating means 14 through a driving transmission means 21 and outputs the extent of driving of the scintillator 16 or the radiation attenuating means 14 and the counted value on a display means 6.

Description

DETAILED DESCRIPTION OF THE INVENTION [Field of Industrial Application] The present invention relates to a radiation detection device that is inserted into the body to detect radiation.

[Prior art and problems to be solved by the invention] As a means of detecting and diagnosing cancer, substances that specifically concentrate on cancer cells are labeled with radioisotopes, and radiation emitted from cancer cells is detected to detect cancer. We are trying to discover its existence.

As a means of discovering this, conventional methods include detecting radiation from outside the body using a gamma camera, as has been commonly done, or using semiconductor radiation at the tip of a catheter for insertion into the body, as shown in Japanese Patent Publication No. 47-40995. Some are equipped with a detector.

In addition, the patent application No. 62-231 proposed by the present applicant
No. 870 proposes an endoscope in which a radiation detector is provided in the insertion section.

However, with a gamma camera, although it is possible to know the general location of cancer, such as which organ it is in, it is not possible to know the detailed location of cancer, such as where in that organ it is.

In addition, the catheter type disclosed in Japanese Patent Publication No. 47-40995 requires the user to manually move the direction of the catheter in order to find cancer, making the operation cumbersome and the distance traveled inaccurate. There are problems such as it takes time.

Furthermore, in the case of the endoscope disclosed in Japanese Patent Application No. 62-231870, the endoscope must be moved forward and backward in the same manner, and there are problems similar to those of the catheter type.

The present invention has been made in view of the above circumstances, and allows the position of cancer to be detected quickly and accurately without the need for the operator to move the radiation detection means directly inserted into the body cavity. The purpose is to provide a radiation □ detection device that can detect radiation.

[Means for Solving Problem 01] The radiation detection device of the present invention includes a scintillator that generates scintillation when radiation is incident, an optical fiber bundle that is optically connected to the scintillator and guides the scintillation, and the scintillator. established around the
A detection probe comprising a radiation attenuation means for limiting the direction of incident radiation, a drive transmission means for driving a scintillator or a J-ray attenuation means, and a tube containing the scintillator, an optical fiber bundle, and the radiation attenuation means. , a drive means for driving the drive transmission means, an optical signal conversion means for optically connecting with the optical fiber bundle and converting scintillation into an electrical signal, an amplifier for amplifying the electrical signal, and a signal amplified by the amplifier. A counting means for counting the number of radiation incident on the scintillator, a detection condition input means for inputting various conditions necessary for detecting radiation, an output of the counting means, and a condition input from the detection condition input means. The apparatus is equipped with a control means for outputting counting results from the control means and controlling the driving means, and a display means for displaying the counting results of the control means.

[Operation] In the present invention, radiation whose direction of incidence is limited by the radiation attenuation means enters the scintillator and generates scintillation. The scintillation is guided by an optical fiber bundle to an optical signal conversion means and converted into an electrical signal. The electric signal is amplified by an amplifier and counted by a counting means, and a calculation is performed by a control means based on the conditions entered from the detection condition input means. The control means controls the drive means to drive the scintillator or the radiation attenuation means via the drive transmission means. The control means outputs the drive IJI ffi of the scintillator or the radiation attenuation means and the count value to the display means.

[Example 1 Hereinafter, the present invention will be described in detail with reference to the drawings.

Figures 1 to 6 relate to the first embodiment of the present invention.
Figure 2 is an explanatory diagram of the tip of the detection probe, Figure 2 is an explanatory diagram of the radiation detection device, Figure 3 is a perspective view of the radiation attenuation means and scintillator, Figure 4 is an explanatory diagram of the detection probe inside the body cavity, and Figure 5 is an explanatory diagram of the detection probe inside the body cavity.
The figure is an explanatory diagram of the moving state of the detection probe, and FIG. 6 is an explanatory diagram of a display example of the detection results.

In FIG. 2, the radiation detection apparatus 1 includes a detection probe 2, a detector 3 to which the detection probe 2 is connected, a keyboard 4 as a detection condition input means for inputting data to the detector 3, and a detector 3. A monitor 6 is provided as a display means for displaying data output from the computer.

The detection probe 2 is inserted, for example, through a forceps insertion port 9 provided in the operating section 8 of the endoscope 7, and is inserted into the forceps channel 11.
It is inserted through the inside and protrudes from the distal end of the endoscope 7. Detection block A-72 protruding from this inner celebration VT7
The distal end portion is constructed as shown in FIG.

In FIG. 1, the detection probe 2 is a flexible tube 1.
The distal end of this tube 12 is closed, and the rear end thereof is provided with a connecting portion 10/'fi connected to the detector 3. The distal end of this closed tube 12 has a cylindrical shape and a closed distal end.
A collimator 14 is provided as radiation attenuation means, which has an opening 13 in a part of its peripheral wall that transmits radiation. The collimator 14 is made of a material that attenuates radiation, such as lead, and has directivity in the direction of radiation incidence.

A scintillator 16 made of, for example, thallium-activated sodium iodide (Nal (TI>)) is provided inside the collimator 14 so as to be slidable in the longitudinal direction of the tube 12 .

The input end face of an optical fiber bundle 18 is bonded to the rear end of the scintillator 16 with an optical adhesive 17, so that scintillation (flash) generated when radiation enters the scintillator 16 can be transmitted. It has become. The optical fiber bundle 18 is inserted through the tube 12 and connected via the connecting portion 10 to a photomultiplier tube 19 as an optical signal conversion means in the detector 3.

The optical fiber bundle 18 is connected to the photomultiplier tube 19 within the detector 3 with a sufficient margin so that it will not be cut even if the scintillator 16 moves within the collimator 14.

The tip of a wire 21 as a drive transmission means inserted through the tube 12 is fixed to the outer periphery of the scintillator 16, and the rear end of this wire 21 is connected to a motor 22 as a drive means in the detector 3. It is connected. Further, the scintillator 16 is connected to the scintillator 1 by a wire 21.
A spring (not shown) is provided which is biased when the sensor 6 is pulled toward the detector 3.

A scale 23 is provided on the outer periphery of the tube 12 near the forceps insertion port 9, so that the collapse of the tip of the detection probe 2 protruding from the tip of the endoscope 7 can be measured. There is.

The photomultiplier tube 19 in the detector 3 is connected to a high voltage power supply circuit 24 and is supplied with electric power. Furthermore, the signal output end of the photomultiplier tube 19 is connected to the amplifier 2.
6 to a counting device 27 as a counting means. The output terminal of this count \A line 27 is connected to a control device 28 as a control means, so that a count value can be input.

The control device 28 is connected to the motor 22,
This motor 22 can be driven and controlled. Note that the control device 28 is capable of controlling the high voltage power supply circuit 24.

The control bag @28 is connected to the scale 23 from the keyboard 4.
It is connected so that the ω read from the sensor can be inputted, and furthermore, the results of the paralysis can be displayed on the monitor 6.

The operation of the radiation detection device 1 configured as described above will be explained.

After the endoscope 7 is inserted into the body cavity, the detection probe 2 is inserted through the forceps insertion port 9 of the endoscope 7. After protruding the detection probe 2 by an appropriate length from the tip of the endoscope 7, the tip of the detection probe 2, which is read from the scale 23 provided on the detection probe 2, protrudes from the tip of the endoscope 7. The input term and counting time are input from the keyboard 4, and the input data is sent to the control device 28. After that, input the start of measurement from the keyboard 4.

On the other hand, cancer antibodies marked with radioisotopes, deoxyglucose, etc., which tend to collect in cancer, are injected into the patient's body by intravenous injection at a predetermined time before the test. As shown in FIG. 4, these reagents are concentrated in the cancer 29, and radiation is emitted from the cancer 29.

The 11i copper wire emitted from the cancer 29 passes through the opening 13 of the collimator 14 and enters the scintillator 16. At this time, the direction of radiation incident on the scintillator 16 is only in the radial direction of the scintillator 16, and radiation from other directions is attenuated by the collimator 14.

The scintillator 16 generates scintillation (flash of light) when radiation is incident thereon. This scintillant is conveyed to the optical fiber bundle 18 via an optical adhesive 17;
The optical fiber bundle 18 passes through the photomultiplier tube 19.
incident on . A photomultiplier tube 19 converts scintillation into an electrical signal. This electrical signal is amplified by an amplifier 26, processed by a counting device 27, and counted. This counting method is similar to that used in ordinary radiation detectors. The counted amount is sequentially input to the control device 28, and the control device 28 performs counting until the counting time inputted in advance from the keyboard 4 has elapsed, and temporarily stores the result. After the counting time has elapsed, the control device 28 prohibits input of the counted value from the counting device 27 and instructs the motor 22 to drive. The motor 22 pulls the wire 21 to move the scintillator 16 as shown in FIG.
Move by the length (L). After the movement is completed, the control device 28 cancels the inhibition of inputting the count value from the counting device 27 and performs counting within the counting time. Thereafter, the scintillator 16 is moved and counting is performed in the same manner.

The control device 28 compares the first input input from the tip of the endoscope 7 to the tip of the detection probe 2 by pulling the scintillator 16 with the kick motor 22, and when the pulled amount becomes equal to Finish the measurement. When the measurement is completed, the temporarily stored count values for each part are displayed on the monitor 6 in a bar graph shown in FIG. 6(a).

In the example shown in Fig. 6, the detection probe 2 is 20 cm from the endoscope 7.
Measurement was started from the protruding position, and measurements were taken by retracting the scintillator 16 every 2.5 cm. The measurement results at each site are displayed in a bar graph as shown in FIG. The operator observes the bar graph on the monitor 6 and learns that the position of the cancer 29 is within a range of 20 cm to 7.5 cm from the tip of the endoscope 7.

In this embodiment, by providing the opening 13 in the peripheral wall of the collimator 14, the direction of the radiation incident on the scintillator 16 is given directivity, and radiation at a predetermined position can be detected. Furthermore, the scintillator 16 is connected to the collimator 14.
The size of the cancer 29 can be accurately determined because the radiation detection device is moved within the body cavity and divides the inner wall of the body cavity for radiation detection.

In this embodiment, a photomultiplier tube 19 is used as the optical signal conversion means.
However, the present invention is not limited to this, and for example, a photodiode may be used.

7 to 9 relate to the second embodiment of the present invention, and FIG.
FIG. 8 is an explanatory diagram of the tip of the detection probe, FIG. 8 is an explanatory diagram of a display example of detection results, and FIG. 9 is an explanatory diagram of the detection range.

In this embodiment, the radiation detection direction is in front of the tip of the detection probe 31, and the configuration is the same as that of the first embodiment except that an opening 33 is provided at the tip of the collimator 32.

In FIG. 7, a collimator 32 formed in a cylindrical shape and made of a material such as lead for attenuating radiation is provided within the tip of the detection probe 31.

The tip of the collimator 32 is provided with an opening 33 that opens toward the front to prevent radiation from entering the collimator 32 from the radial direction.

The operation of this embodiment will be explained using FIGS. 8 and 9. Note that a case will be described in which the cancer 29 is located in front of the detection probe 31.

Measurement is started by aligning the distal end surface of the scintillator 16 and the distal end surface of the opening 33. If the tip surfaces match,
The range θ where radiation can enter the scintillator 16 is 360
Since the cancer 29 is located in front of the detection probe 31, the radiation enters the scintillator 16. This count value is shown by the bar graph 35 in FIG. 8(a). keyboard 4
scintillator 16 sequentially according to the counting time input from
As the radiation is drawn into the collimator 32, the angle of entry θ of the radiation into the scintillator 16 becomes narrower. In FIG. 9, if the cancer 29 is within the range of the angle of entry θ1, the count displayed on the monitor 6 will be almost the same as 35 in FIG. The invasion angle becomes 02, and cancer 29 is detected from the range of angle θ2 as shown in Figure 9.
When this happens, the amount of radiation incident on the scintillator 16 decreases, resulting in a result as shown in the bar graph 36 in FIG. 8(a).

In this case, the operator determines the distance from the distal end surface of the scintillator 16 to the distal end surface of the frontage portion 33, that is, the distance from the distal end surface of the scintillator 16,
The penetration angle θ2 at which the radiation is reduced can be determined from the amount by which the radiation is drawn into the collimator 32. From this angle θ2, the cancer 2
Know the size of 9.

As described above, in this embodiment, the size of the cancer 29 can be measured by drawing the scintillator 16 into the collimator 32 while sequentially detecting radiation. Further, by drawing the scintillator 16 into the collimator 32, the directivity for radiation detection can be improved.

FIG. 10 is an explanatory view of the tip of the detection probe according to the third embodiment of the present invention.

In this embodiment, the scintillator 16 and collimator 14 in the first embodiment are fixed, and by pulling the wire 21 with a motor 22, the collimator 14 can be moved together with the scintillator 16. In addition,
The axial length of the opening 13 of the collimator 14 is equal to or shorter than the axial length of the scintillator 16.

In this embodiment, since the collimator 14 is fixed to the scintillator 16, the directivity in the direction in which the radiation enters can be further improved compared to the first embodiment.

Other configurations, operations, and effects are the same as those in the first embodiment.

11 and 12 relate to a fourth embodiment of the present invention, in which FIG. 11 is a schematic diagram of a detection device, and FIG. 12 is an explanatory diagram showing an example of display on a monitor.

A collimator 41 formed in a cylindrical shape and made of, for example, lead is provided at the tip of the detection probe 39 in this embodiment to attenuate radiation. The tip of this collimator 41 is closed, and an opening 42 is provided in the peripheral wall. A tube 43 is connected to the rear end of the collimator 41 as a drive transmission means that can rotate the collimator 41 about the center in the axial direction. A driven gear 44 is provided concentrically with the tube 43 at the rear end of the tube 43. A driving gear 47 driven by a motor 46 meshes with this gear 44, and the motor 46 drives the collimator. 4
1 is rotated. Note that an ultrasonic motor may be used as the motor 46.

The rotation of the motor 46 is controlled by a control device @28 within the detector 3, and its rotational position is detected by an encoder 48 and fed back to the control device 28.

A scintillator 16 is provided within the collimator 41, and the input end surface of an optical fiber bundle 18 is connected to the rear end of the scintillator 16 via an optical adhesive 17. Note that the scintillator 16 and the optical fiber bundle 18 are connected to a collimator 41 and a tube 43 that are rotated.
It is designed to stand still against. This optical fiber bundle 18 is connected to the detector 3 described in the first embodiment.

The other configurations are the same as in the first embodiment.

The collimator 41 of this embodiment is rotated by a motor 46. The motor 46 is controlled by a control Il device 28. That is, as shown in FIG. 12, the detection probe 3
When detecting radiation at 8 surrounding locations in the radial direction of 9, the device rotates 45 degrees, stops for a certain period of time, and then counts, and then rotates 45 degrees again, stops for a certain period of time, and then counts. I do.

This process is repeated one after another to perform counting and display an image as shown in FIG. 12 on the monitor 6. In the same figure, a circle 66 is shown in the center of the screen of the monitor 6 without indicating the position of the scintillator 16, and axes 67, 67, . . . are shown radially from this circle 66. An axis 67 indicates the region where radiation was detected by the probe 39, and indicates that the farther from the circle 66 the more detected counts. When the collimator 41 rotates once and the measurement is completed, the count value of each part is 67.67
. . . and the plotted points are connected to each other by a line 68. Therefore, it can be seen that the region where the line 68 protrudes the most is the location where the cancer 29 is located.

In this embodiment, the collimator 41 is rotated by the motor 46 via the tube 43, so that radiation can be detected over the entire circumference of the scintillator 16. The detected count values are displayed as shown in FIG. 12, and the count values in each radial direction can be known over the entire circumference of the detection probe 39.

Other functions and effects are similar to those of the first embodiment.

13 and 14 relate to a fifth embodiment of the present invention, in which FIG. 13 is a schematic diagram of a detection device, and FIG. 14 is an explanatory diagram showing an example of display on a monitor.

In this embodiment, a motor 46 for rotating the collimator 41 of the fourth embodiment is added to the configuration of the first embodiment, so that radiation in the axial direction and the radial direction can be detected simultaneously.

The configuration of this embodiment is similar to the first embodiment and the fourth embodiment.

Note that the display on the monitor 6 is performed as shown in FIG.

FIG. 14 shows a case where measurements are taken at nine equal locations in the axial direction, the screen is divided into nine parts, and the image shown in FIG. 12 is displayed on each divided screen.

In this embodiment, it is possible to obtain two-dimensional positional information of the cancer 29, which cannot be obtained in each of the embodiments described above.10) The accuracy of diagnosis can be improved.

Other functions and effects are similar to those of the first embodiment.

FIG. 15 is a schematic diagram of a radiation detection device according to a sixth embodiment of the present invention.

In this embodiment, the radiation detection device v11 described in the first embodiment and the electronic endoscope device 51 are used together.

In the electronic endoscope 50 constituting the endoscope apparatus 51 of this embodiment, a large-diameter operating section 53 is connected to the rear end of an elongated insertion section 52 . A universal cord 54 extends from the side of the operating section 53, and a connector 56 provided at the rear end of the universal cord 54 is connected to a control device 57 and a light control device 61. The control device 57 includes a monitor 58
is connected, and a mirror image of the wedding ceremony is displayed.

A forceps insertion port 59 is provided on the side of the operating section, and the detection probe 2 described in the first embodiment is inserted through the forceps insertion port 59.

The rear end of the detection probe 2 is a control device 2 having a monitor 6.
8 are connected.

The other configurations are the same as in the first embodiment.

In this embodiment, before detection is performed by the radiation detection device 1, the electronic endoscope 50 detects the site where radiation is being emitted, that is, the cancer 2.
You can check the approximate location of 9.

In other words, when radiation enters a solid-state image pickup device (not shown) provided in the electronic internal reception 1t50, a bright spot appears on the screen of the monitor 58 displaying the endoscopic image. The operator knows the approximate location of the cancer 29 from the appearance of the bright spot, and then uses the radiation detection device 1 to detect the detailed location and size of the cancer 29.

According to this embodiment, the electronic endoscope 50 roughly detects cancer 2.
9 can be known, and the time required to detect the position of cancer 29 can be shortened.

Other functions and effects are similar to those of the first embodiment.

[Effects of the Invention] As explained above, according to the present invention, the radiation attenuating means for imparting directivity to the direction of radiation incident on the scintillator is provided, and by driving the scintillator or the radiation attenuating means, the operator can There is no need to perform operations such as moving the radiation detection means directly inserted into the body cavity, and radiation can be detected quickly and accurately.

[Brief explanation of drawings]

Figures 1 to 6 relate to the first embodiment of the present invention.
Figure 2 is an explanatory diagram of the tip of the detection probe, Figure 2 is an explanatory diagram of the radiation detection device, Figure 3 is a perspective view of the radiation attenuation means and scintillator, Figure 4 is an explanatory diagram of the detection probe inside the body cavity, and Figure 5 is an explanatory diagram of the detection probe inside the body cavity.
FIG. 6 is an explanatory diagram of the moving state of the detection probe, FIG. 6 is an explanatory diagram of an example of display of detection results, FIGS. 7 to 9 relate to the second embodiment of the present invention, and FIG. 7 is the tip of the detection probe. FIG. 8 is an explanatory diagram of a display example of the detection result, FIG. 9 is an explanatory diagram of the detection range, and FIG. 10 is related to the third embodiment of the present invention.
11 and 12 are explanatory diagrams of the tip of the detection probe, and FIG. 11 is a schematic diagram of the detection device;
Fig. 12 is an explanatory diagram showing an example of the display on the 72, Fig. 13 and Fig. 14 relate to the fifth embodiment of the present invention, Fig. 13 is a schematic diagram of the detector, and Fig. 14 is the display on the monitor. FIG. 15 is a schematic diagram of a radiation detection apparatus according to a sixth embodiment of the present invention. 1... Radiation detection device 2... Detection probe 3...
・Detector 4...Keyboard 6...Monitor 7...Endoscope 12...Wire 1
3... Opening 14... Collimator 16... Scintillator 18... Optical fiber bundle 19... Photomultiplier tube 21... Wire 22...
Motor 27... Counting device 28... Control device Agent Patent attorney Susumu Ito Figure 3 Figure 4 Figure 5 + Figure 6 taY Figure 111 Figure 8 Figure 9 Figure 13 Figure 142 Figure 11 Figure 15

Claims (1)

[Scope of Claims] A scintillator that generates scintillation when radiation is incident; an optical fiber bundle that is optically connected to the scintillator and guides the scintillation; a radiation attenuating means for limiting the direction of radiation; a drive transmission means for driving the scintillator or the radiation attenuating means; and a tube housing the scintillator, the optical fiber bundle, and the radiation attenuating means. a probe; a drive means for driving the drive transmission means; an optical signal conversion means for optically connecting with the optical fiber bundle and converting the scintillation into an electric signal; an amplifier for amplifying the electric signal; a counting means for counting the number of radiation incident on the scintillator from a signal amplified by an amplifier; a detection condition input means for inputting various conditions necessary for detecting radiation; an output of the counting means; A detector comprising: a control means for outputting a count result based on conditions input from a detection condition input means and controlling the driving means; and a display means for displaying the count result of the control means. Characteristic radiation detection device.