WO2022004688A1 - Radiation camera - Google Patents

Abstract

Provided is a radiation camera which can project visible light toward a radiation source, and which does not require correction of a projection direction according to the position of the radiation camera. The radiation camera (1) is provided with: a collimator (8) that collimates incoming radiation; a radiation detection unit (13) that detects the radiation having passed through the collimator (8); and a light-emitting unit (14) that emits visible light toward a direction opposite to the incoming direction of the radiation detected by the radiation detection unit (13).

Description

Radiation camera

The present invention relates to a radiation camera for gamma rays, X-rays, annihilation radiation, etc.

Conventionally, cancer cells that easily take up a specific compound or tissues in which a compound of a specific size easily stays are known. In order to locate such cancer cells or tissues, a compound containing a radionuclide is administered to a patient and the location is determined by a gamma camera. For example, ^{a method is known in which a compound preparation containing 99 m} Tc is administered to a patient, and the lymph node in which the compound is accumulated is identified and dissected. Non-Patent Document 1 discloses a portable gamma camera capable of determining the presence or absence of cancer metastasis to the sentinel lymph node during surgery in order to carry out this method.

Further, Non-Patent Document 2 discloses a handheld imaging device having a built-in projector. This imaging device has a camera that detects the near-infrared fluorescence of indocyanine green from the surgical site, and is configured to project light from the projector to the site where the near-infrared fluorescence is detected.

However, in the gamma camera disclosed in Non-Patent Document 1, since the image of the detected radiation intensity distribution is displayed on a separate display, it is difficult to grasp the positional relationship between the displayed image and the surgical site. .. On the other hand, the imaging apparatus disclosed in Non-Patent Document 2 aims to project light onto a portion where near-infrared fluorescence is detected. However, in this imaging device, the optical axis of the camera that detects near-infrared fluorescence and the optical axis of the projector do not match. Therefore, a distance sensor and a calibration calculation program for calibrating the projected position according to the position of the imaging device are required so that the light is projected at the correct position. However, in addition to the size of the distance sensor itself, a high-performance processor for performing calibration calculations in real time according to the ever-changing distance, and its cooling function and power supply function are required, which may increase the size of the device. There is.

One aspect of the present invention is to provide a radiation camera capable of projecting visible light toward a radiation source without having to calibrate the projection direction according to the position of the radiation camera.

In order to solve the above problems, the radiation camera according to one aspect of the present invention has a collimator that collimates the incident radiation, a radiation detection unit that detects the radiation that has passed through the collimator, and the radiation detection unit. It is provided with a light emitting unit that emits visible light in the direction opposite to the incident direction of radiation.

According to one aspect of the present invention, it is possible to provide a radiation camera capable of projecting visible light toward a radiation source without having to calibrate the projection direction according to the position of the radiation camera.

It is a figure which conceptually shows the function of the gamma camera which concerns on one Embodiment of this invention. FIG. 2A is a schematic vertical sectional view showing the configuration of the gamma camera according to the first embodiment of the present invention, and FIG. 2B is a schematic vertical sectional view showing the configuration of the gamma camera according to the modified example, FIG. 2 (). c) is a perspective view of a radiation detection element of a modified gamma camera. It is a block diagram which shows the structure of the gamma camera which concerns on Embodiment 1. FIG. It is a schematic vertical sectional view which shows the structure of the gamma camera which concerns on Embodiment 2 of this invention, and is the partially enlarged view of the tip part. FIG. 5A is a perspective view showing an example of the shape of the gamma camera according to the second embodiment, and FIG. 5B is a perspective view showing another example of the shape of the gamma camera. It is a schematic vertical sectional view which shows the structure of the gamma camera which concerns on Embodiment 3 of this invention. 7 (a) to 7 (c) are schematic views showing the operation of the gamma camera according to the third embodiment of the present invention, and FIG. 7 (d) is a flowchart thereof. FIG. 8A is a schematic vertical sectional view showing the configuration of the gamma camera according to the fourth embodiment of the present invention, and FIG. 8B is a flowchart showing the operation thereof. It is a schematic vertical sectional view which shows the structure of the gamma camera which concerns on Embodiment 5 of this invention. 10 (a) to 10 (j) are schematic vertical sectional views showing an arrangement example of a radiation detection element and a laser light emitting element according to the sixth embodiment of the present invention. 11 (a) is an example of the control flow of the gamma camera according to the sixth embodiment, and FIG. 11 (b) is a block diagram showing the configuration of the gamma camera. FIG. 12 (a) is a schematic vertical sectional view of the gamma camera according to the seventh embodiment of the present invention, and FIG. 12 (b) is a control flow thereof. It is a top view which shows the arrangement of the radiation detection element and the laser emission element of the gamma camera which concerns on Embodiment 7. It is a perspective view which shows the arrangement of the radiation detection element and the laser light emitting element of the gamma camera which concerns on Embodiment 7. It is a figure which shows the preferable range of the deviation angle between the incident axis of the gamma ray and the laser optical axis which emits in the gamma camera which concerns on Embodiment 7. 16 (a) is a perspective view of a shield of a gamma camera according to the eighth embodiment of the present invention, and FIG. 16 (b) is a vertical sectional view thereof. FIG. 17 (a) is an example of a shield of a gamma camera according to the ninth embodiment of the present invention, and FIG. 17 (b) is a vertical sectional view showing another example of the embodiment. It is a schematic diagram which shows the application example of the gamma camera which concerns on embodiment of this invention to medical treatment.

(Function of gamma camera)
First, the function of the gamma camera as an example of the radiation camera in the embodiment of the present invention will be described with reference to the drawings. FIG. 1 is a diagram conceptually showing the function of a medical gamma camera according to an embodiment of the present invention. The gamma camera shown in FIG. 1 is a medical gamma camera that detects radiation (for example, gamma rays) from a radiation source of a target (for example, a human body) and emits visible light in the direction opposite to the incident direction of the detected gamma rays. .. With such a configuration, visible light is irradiated to the position where the radiation source exists in the target. As a result, the operator of the gamma camera can easily visually grasp the position where the radiation source exists in the target. In the example shown in FIG. 1, the radiation source (hereinafter, also simply referred to as “radioactive source”) exists inside the object, but the radiation source may exist on the surface of the object. Gamma rays are generally emitted from a radiation source in an unspecified direction, but a gamma camera is configured to determine the incident direction of gamma rays and emit visible light in the direction opposite to the incident direction. Hereinafter, a specific configuration example of a gamma camera for realizing such a function will be described. In addition, "toward the opposite direction of the incident direction" means not only the reverse direction corresponding to the incident axis but also the reverse direction deviated by a certain angle with respect to the incident axis. It is preferable that the accuracy of the injection angle is, for example, the same as the accuracy of detecting the incident angle of radiation. The radiation camera is a radiation camera for gamma rays, X-rays, annihilation radiation, and the like.

[Embodiment 1]
(Configuration and operation of gamma camera 1)
Next, the gamma camera 1 (an example of a “radiation camera” in the claims) according to the first embodiment of the present invention will be described with reference to the drawings. FIG. 2 is a schematic vertical sectional view showing the configuration of the gamma camera 1 according to the first embodiment and the gamma camera 1A according to a modification thereof. As shown in FIG. 2A, the gamma camera 1 includes a housing 9 and a shield 8 provided at one end of the housing 9. In the following, the vertical direction of the drawing will be described as the vertical direction of the gamma camera 1 for convenience. The shield 8 has a conical upper portion 8A and a cylindrical lower portion 8B. The shape of the shield 8 may be rectangular. For example, the upper 8A may be a pyramid and the lower 8B may be a prism. The shield 8 is formed to have a predetermined thickness by using a high-density material such as lead or tungsten in order to shield gamma rays. The predetermined thickness is a thickness capable of shielding gamma rays of a predetermined energy. The gamma camera 1 according to the present embodiment is intended to detect gamma rays of about 140 keV emitted from ^{, for example, 99 m Tc.} Therefore, the shield 8 is designed to have a thickness capable of shielding 140 keV gamma rays. The shield 8 is formed with a pinhole 8D (an example of a “collimator” in the claims) which is a minute opening at the tip portion 8C in order to collimate the incident gamma ray. The pinhole 8D is formed in a pore shape so as to allow only gamma rays R incident from above to pass through.

The gamma camera 1 includes a radiation detection unit and a light emitting unit. The radiation detection unit is composed of one radiation detection element 13 provided inside the shield 8, and the light emitting unit is one light emission corresponding to the radiation detection element 13 provided inside the shield 8. It is composed of an element 14. In the present embodiment, the light emitting element 14 is arranged on the side closer to the pinhole 8D, and the radiation detection element 13 is arranged on the side farther from the pinhole 8D. The light emitting element 14 and the radiation detecting element 13 are arranged adjacent to each other along the traveling direction of the gamma ray R (that is, vertically) in this order. The traveling direction of the gamma ray is a direction from the side near the pinhole 8D (light emitting element 14 side) to the side far from the pinhole 8D (radiation detection element 13 side). Further, "adjacent" includes a case where they are in contact with each other and a case where they are separated from each other. That is, the light emitting element 14 and the radiation detecting element 13 may be arranged in contact with each other or may be arranged apart from each other. Further, when the light emitting element 14 and the radiation detection element 13 are arranged in contact with each other, both may be directly laminated, and in addition, a support member that transmits gamma rays R between the light emitting element 14 and the radiation detection element 13 or the like may be used. Spacers may be interposed.

The type of the radiation detection element 13 is not particularly limited, but a small detection element such as a scintillation detection element or a semiconductor detection element is preferable. As the scintillation detection element, a CsI (Tl) scintillator, a NaI (Tl) scintillator, or the like can be used. As the semiconductor detection element, a CdTe semiconductor detection element, a CZT semiconductor detection element, a Si semiconductor detection element, a Ge semiconductor detection element, or the like can be used. The radiation detection element 13 converts the energy of radiation into an electric signal and outputs it, but since a known configuration can be used for the configuration of converting the energy into an electric signal, the illustration and description thereof will be omitted. The type of the light emitting element 14 is not particularly limited, but for example, a light emitting diode (Light Emitting Diode, LED) that emits visible light (hereinafter, also simply referred to as “light”) can be used.

As described above, in the gamma camera 1, the light emitting element 14 is arranged on the radiation detection element 13. Therefore, as shown in FIG. 2A, the gamma ray R incident on and passing through the pinhole 8D passes through the light emitting element 14 and reaches the radiation detection element 13. However, for example, ^{the energy of the gamma ray R emitted from 99 m} Tc is about 140 keV, and the light emitting element 14 can be easily transmitted, and there is little possibility of affecting the detection efficiency of the gamma ray R.

The control unit 16 is arranged inside the housing 9 and outside the shield 8. By providing the control unit 16 inside the housing 9, portability is improved. By integrating the radiation detection element 13, the light emitting element 14, and the control unit 16, a more compact configuration can be obtained. As shown in FIG. 3, the control unit 16 receives an electric signal that the radiation detection element 13 receives and outputs a gamma ray, and the light emitting element 14 is excited for a predetermined time by receiving the electric signal to generate light. Control is performed to emit (emit) L. If the light emitting element 14 is made to emit light for a long time, the light L is overlapped and continuously projected when the radiation intensity (counting rate or air dose rate) is strong, which is not preferable. On the other hand, if the light emission time is too short, it becomes difficult to visually recognize the light emission time, so that a certain amount of light emission time is required. Therefore, the control unit 16 may be configured so that the light emission time can be adjusted based on the intensity of radiation so that appropriate visual inspection is possible. Further, the control unit 16 may be configured so that the emission intensity (luminance) can be adjusted in place of or in addition to the emission time. The control unit 16 includes a processor such as an MPU (Micro Processing Unit) or a CPU (Central Processing Unit), and a memory for storing various programs and data. Alternatively, the control unit 16 may use a dedicated processor such as an ASIC (Application Specific Integrated Circuit) or an FPGA (Field Programmable Gate Array) as the processor.

Returning to FIG. 2, as for the light L emitted from the light emitting element 14, only the light L directed in the direction opposite to the incident direction of the gamma ray R is emitted to the outside through the pinhole 8D. As a result, the light L is projected at the position of the target corresponding to the radiation source. The position corresponding to the radiation source is the position of the radiation source when the radiation source is on the surface of the target, and the line segment connecting the radiation source and the light emitting element 14 when the radiation source is inside the target. Is the position where is the intersection with the surface of the object.

As described above, the radiation detection element 13 detects the gamma ray R that has passed through the pinhole 8D, and the light emitting element 14 emits visible light L in the direction opposite to the incident direction of the gamma ray R. The emitted visible light L is emitted toward the radiation source and projected at the position of the target corresponding to the radiation source.

When this configuration is applied to a medical gamma camera as in the present embodiment, the position of the affected area can be visualized on the skin. Specifically, the medical gamma camera 1 can ^{detect gamma rays emitted from, for example, 99 m} Tc, and emit light in the direction opposite to the incident direction. For example, when ^{a labeled compound such as albumin or futinic acid containing 99} mTc is administered to a breast cancer patient, the labeled compound accumulates in the affected part of the breast cancer. Therefore, when the doctor makes a diagnosis using the gamma camera 1, light is emitted from the gamma camera 1 in the direction of the source of the gamma rays emitted from ^{99 mTc.} That is, the light from the gamma camera 1 is directly projected onto the patient's skin toward the affected area where the labeled compound is accumulated and visualized. Therefore, the doctor can visually grasp the position of the affected area. The gamma camera 1 can also be used during surgery, in which case the position of the affected area can be visualized on the surface of the organ.

When the affected area is inside the human body, light is projected at the position where the line connecting the pinhole 8D of the gamma camera 1 and the affected area intersects the skin. By diagnosing the position of the affected area by changing the position of the gamma camera 1, even if the position of the affected area is inside, the position can be grasped.

In the prior art, the incident axis of the detected radiation and the projection axis of the projected light do not match, so complicated calibration calculation is required depending on the position where the light is projected. However, according to the gamma camera 1, visible light can be projected toward a radiation source without calibrating the projection direction according to the position of the gamma camera 1.

(Modification example)
In the first embodiment, the light emitting element 14 is arranged on the radiation detection element 13. However, as shown in FIG. 2B, the light emitting element 14 and the radiation detection element 13 may be arranged in reverse. In the example shown in FIG. 2B, the radiation detection element 13 is arranged inside the shield 8, and the light emitting element 14 is arranged inside the housing 9 below the shield 8. As shown in FIG. 2C, a cylindrical opening 13A is provided in the central portion of the radiation detection element 13, and the light emitting element 14 emits light through the opening 13A. The light emitting element 14 may also be provided inside the shield 8. Even with such a configuration, the same effect as that of the first embodiment can be obtained.

In the first embodiment, the control unit 16 is provided inside the housing 9. However, the control unit 16 may also be provided inside the shield 8. Further, the light emitting element 14 may be a laser light emitting element. Although the "gamma camera" is exemplified in this embodiment, the radiation to be detected as described above does not necessarily have to be gamma rays. For example, it may be configured to detect beta rays or electromagnetic waves of various energy levels and emit light in the opposite direction. In that case, the radiation detection element 13 is appropriately changed to one having a configuration suitable for detecting radiation.

[Embodiment 2]
(Configuration of gamma camera 2)
Next, the gamma camera 2 according to the second embodiment of the present invention will be described with reference to the drawings. FIG. 4 is a schematic vertical sectional view showing the configuration of the medical gamma camera 2 according to the second embodiment. As shown in FIG. 4, the gamma camera 2 includes a radiation detection unit 12 and a control unit 16 inside the shield 10. The shield 10 also serves as a housing for the gamma camera 2, and the upper portion 10A is conical and the lower portion 10B is cylindrical. Similar to the shield 8 of the first embodiment, the shield 10 is formed with a pinhole 11 (an example of a “collimator” in the claims) which is a minute opening for collimating a gamma ray at the tip portion 10C. .. The pinhole 11 of the gamma camera 2 is formed so as to collimate gamma rays from a wide angle. The material and thickness of the shield 10 are as described in the first embodiment.

The radiation detection unit 12 includes a plurality of radiation detection elements 13 (an example of a "radiation detection unit" within the scope of claims). The plurality of radiation detection elements 13 are regularly arranged on a circular plane according to the cross-sectional shape of the lower portion 10B of the shield 10. As the radiation detection element 13, the scintillation detection element, the semiconductor detection element, or the like is preferable as in the first embodiment.

As shown in the enlarged view in FIG. 4, a light emitting portion including a light emitting element 14 and a reflecting portion 15 is arranged on the tip portion 10C of the shield body 10. The light emitting element 14 is arranged at one place of the open end portion 10D of the pinhole 11. The reflecting portion 15 is arranged at a position of the opening end portion 10D facing the light emitting element 14. The light emitting element 14 is, for example, a light emitting diode that emits light L toward the reflecting unit 15. When the radiation detection element 13 detects a gamma ray, the light emitting element 14 is controlled by the control unit 16 so as to emit light L toward the reflection unit 15 for a predetermined time. The reflecting unit 15 is composed of a planar reflecting plate 15A and a driving unit 15B for driving the reflecting plate 15A. The drive unit 15B is a piezoelectric actuator that can, for example, rotate the reflector 15A in two orthogonal axial directions to arbitrarily change the direction of the reflector 15A. The drive unit 15B is driven and controlled by the control unit 16. In the present embodiment, the orientation of the reflector 15A that reflects the light L emitted from the light emitting element 14 corresponds to the position of each of the plurality of radiation detection elements 13.

(Operation of gamma camera 2)
When the gamma ray is detected by the radiation detection element 13, the incident direction of the detected gamma ray is determined from the position of the detected radiation detection element 13 and the position of the pinhole 11. That is, the line connecting the detected radiation detection element 13 and the pinhole 11 is the incident direction of the gamma ray. When the control unit 16 receives the signal from the radiation detection element 13, the control unit 16 drives the drive unit 15B according to the radiation detection element 13 that has detected the gamma ray. Specifically, the control unit 16 drives the drive unit 15B to change the direction of the reflector 15A so that the light L is reflected in the direction opposite to the incident direction of the gamma ray. After that, the light emitting element 14 is made to emit light for a predetermined time. If the light emitting element 14 emits light for a long time, the light L continues to be emitted even after the gamma camera 2 is moved, which is not preferable. On the other hand, if the light emission time is too short, it becomes difficult to visually recognize, so a certain amount of light emission time is required. Further, when the radiation intensity (counting rate or air dose rate) is high, the emission times may overlap and the intensity of the radiation source depending on the position may not be separated. Therefore, it may be configured so that the user can adjust the light emission time so that appropriate visual inspection is possible. Further, it may be configured so that the user can adjust the emission intensity (luminance) instead of or in addition to the emission time.

With the above configuration, the gamma camera 2 can obtain the same effect as that of the first embodiment. That is, according to the above configuration, visible light can be projected toward the radiation source without calibrating the projection direction depending on the position of the gamma camera. Further, by providing a plurality of radiation detection elements 13, when the radiation detection element 13 detects the radiation that has passed through the pinhole 11, the incident direction of the radiation can be easily determined from the positions of the pinhole 11 and the radiation detection element 13. Can be decided. Visible light can be emitted from the light emitting element 14 in the direction opposite to the incident direction of the radiation.

(Modification example)
In the second embodiment, as shown in FIG. 5A, the shield 10 has a cylindrical shape at the lower portion and a conical shape at the upper portion. However, the shape of the shield 10 is not limited. For example, as shown in FIG. 5B, the shape of the shield 10 may be rectangular. That is, the lower portion of the shield 10 may be prismatic and the upper portion may be pyramidal. Further, in the above example, the light emitting element 14 and the reflecting portion 15 are arranged at the tip portion 10C of the shielding body 10, but the positions thereof are not limited. As described above, the incident direction of the gamma ray is determined by the position of the radiation detection element 13 that has detected the gamma ray. .. Further, the light emitting element 14 and the reflecting portion 15 may be arranged at different positions, and the light may be guided so as to be emitted from the tip portion 10C of the shielding body 10.

In the second embodiment, the shield 10 also serves as a housing for the gamma camera 2. However, the housing may not be shared with the shield 10 and may be configured separately. In that case, the control unit 16 may be arranged inside the housing unit.

[Embodiment 3]
(Structure of gamma camera 3)
Next, the medical gamma camera 3 according to the third embodiment will be described with reference to the drawings. For convenience of explanation, in each of the following embodiments, the members having the same functions as the members described in the previous embodiments are designated by the same reference numerals, and the description thereof will not be repeated. FIG. 6 is a schematic cross-sectional vertical view showing the configuration of the gamma camera 3. As shown in FIG. 6, the gamma camera 3 includes a cylindrical shield 20 similar to the shield 10 described in the first embodiment. The shield 20 has a pinhole 11 (an example of a "collimator" in the claims) at the tip thereof. The shield 20 includes a plurality of radiation detection elements 13, a plurality of light emitting elements 30, and a control unit 16 inside.

The plurality of radiation detection elements 13 and the plurality of light emitting elements 30 are arranged adjacent to each other in the direction along the traveling direction of the gamma ray. In the present embodiment, the radiation detection element 13 and the light emitting element 30 are arranged adjacent to each other in the vertical direction of the drawing. In this embodiment, the number of radiation detection elements 13 and the number of light emitting elements 30 are the same, and one light emitting element 30 is arranged on one radiation detection element 13. The radiation detection element 13 and the light emitting element 30 arranged adjacent to each other in the vertical direction are associated with each other. The light emitting element 30 is arranged so as to emit light upward. Since the emitted light is collimated by the pinhole 11, the light emitting element 30 does not need to emit directional light. The light emitting surface of the light emitting element 30 and the detection surface of the radiation detection element 13 are preferably geometrically similar in shape and size, and more preferably equivalent. As a result, the distribution of the projected light and the distribution of the radiation source can be made more consistent.

(Operation of gamma camera 3)
The operation of the gamma camera 3 will be described with reference to FIG. 7. As shown in the flowchart shown in FIG. 7 (d), in the present embodiment, when gamma rays are detected by the radiation detection element 13 (step S71), the control unit 16 causes the corresponding light emitting element 30 to emit light (step S72). ). As a result, when gamma rays from, for example, a radiation source (affected portion) 50 existing in the body are detected by the radiation detection element 13, light is projected onto the skin 51 at a position corresponding to the radiation source 50.

More specifically, as shown in FIG. 7A, gamma rays incident through the pinhole 11 are detected by the radiation detection element 13. When the control unit 16 receives the gamma ray detection signal from the radiation detection element 13, as shown in FIG. 7B, the control unit 16 emits visible light from the light emitting element 30 corresponding to the radiation detection element 13 that has detected the gamma ray for a predetermined time. Let me. The reason for emitting visible light for a predetermined time and the fact that the predetermined light emission time may be adjusted are the same as those in the first and second embodiments. As shown in FIG. 7 (c), the light emitted upward from the light emitting element 30 is collimated by the pinhole 11, and only the light directed in the direction opposite to the incident direction of the incident gamma ray is emitted to the outside. , Lymph nodes, etc. are projected onto the skin 51 at a position corresponding to the radiation source 50. This operation is repeated in each radiation detection element 13 and the corresponding light emitting element 30.

By stacking the radiation detection element 13 and the light emitting element 30 adjacent to each other in the direction along the traveling direction of the gamma ray, only the light emitting element 30 is made to emit light, and the direction is opposite to the incident direction of the gamma ray incident from the pinhole 11. Light can be emitted to the outside. Then, the light from the gamma camera 3 is directly projected onto the patient's skin 51 and visualized toward the radiation source (affected portion) 50 in which the labeled compound that emits gamma rays is accumulated. This allows the doctor to visually grasp the position of the affected area 50. When used during surgery, it may be the surface of an organ instead of the skin 51.

In the gamma camera 3, the light emitting element 30 is arranged adjacent to the radiation detection element 13. Therefore, the incident gamma rays pass through the light emitting element 30 and reach the radiation detection element 13. However, as described above, for example, ^{the energy of gamma rays emitted from 99} mTc is about 140 keV, and the light emitting element 30 can be easily transmitted, and there is little possibility of affecting the gamma ray detection efficiency.

In the gamma camera 3 according to the third embodiment, the number of light emitting elements 30 is larger than that in the gamma camera 2 of the second embodiment, but the reflector 15A that reflects the light L emitted from the light emitting element 14 is driven by the driving unit 15B. It is not necessary to drive using. The simple configuration in which the corresponding radiation detection element 13 and the light emitting element 30 are arranged adjacent to each other along the traveling direction of the radiation makes it easy to emit light in the opposite direction of the incident radiation. That is, it is possible to emit light in the opposite direction of the incident radiation simply by emitting light from the light emitting element 30 corresponding to each of the radiation detection elements 13. The modifications shown in the first and second embodiments can be appropriately applied to the third embodiment.

[Embodiment 4]
Next, the configuration and operation of the gamma camera 4 according to the fourth embodiment will be described with reference to FIG. As shown in FIG. 8A, the gamma camera 4 has a shield 20 similar to that of the third embodiment. The gamma camera 4 has a radiation detection element 13 and a laser light emitting element 32 (an example of a “light emitting unit” in the claims) inside the shield 20. The radiation detection element 13 and the laser light emitting element 32 are arranged adjacent to each other along the traveling direction of gamma rays. The radiation detection element 13 and the laser light emitting element 32 are arranged correspondingly in the same number. The laser light emitting element 32 is arranged so as to emit visible laser light toward the pinhole 11.

As shown in the flowchart of FIG. 8B, when the control unit 16 receives the gamma ray detection signal from the radiation detection element 13 (step S81), the control unit 16 is connected to the laser light emitting element 32 corresponding to the radiation detection element 13 that has detected the gamma ray. Visible light is emitted for a predetermined time (step S82). This flowchart is repeated between the corresponding radiation detection element 13 and the laser light emitting element 32.

According to the gamma camera 4, brighter light can be projected by replacing the non-directional light emitting element 30 in the third embodiment with the directional laser light emitting element 32. Since the laser light emitting element 32 has high directivity, it is preferable to arrange the laser light emitting direction with high accuracy toward the pinhole 11. Specifically, the light emitting surface of the laser light emitting element 32 is adjusted so as to face the pinhole 11, and the center of the light emitting surface is a line connecting the center of the detection surface of each radiation detection element 13 and the pinhole 11. It is preferably on the minute.

With the gamma camera 4 having the above configuration, the same effect as that of the gamma camera 3 according to the third embodiment can be obtained. Further, according to the gamma camera 4, the brightness of the projected light can be increased as compared with the gamma camera 3 of the third embodiment. The modifications shown in the first and second embodiments can be appropriately applied to the fourth embodiment.

[Embodiment 5]
Next, the gamma camera 5 according to the fifth embodiment will be described with reference to FIG. The gamma camera 5 has a shield 20 similar to that of the third embodiment. The gamma camera 5 has a radiation detection element 13 and a laser light emitting element 32 inside the shield 20. As shown in FIG. 9, the radiation detection element 13 and the laser light emitting element 32 are arranged adjacent to each other along the traveling direction of gamma rays. The radiation detection element 13 and the laser light emitting element 32 are arranged correspondingly in the same number.

More specifically, the corresponding radiation detection element 13 and the laser light emitting element 32 are integrated. More specifically, the detection surface of the radiation detection element 13 and the light emission surface of the laser light emitting element 32 are integrated along the traveling direction of the gamma ray so as to face the same direction. The integrated radiation detection element 13 and the laser light emitting element 32 are arranged toward the pinhole 11. By manufacturing the integrated radiation detection element 13 and the laser light emitting element 32 in advance, it becomes easy to arrange each of them in the direction of the pinhole 11. The operation of the gamma camera 5 is the same as the operation of the gamma camera 3 described in the third embodiment.

With the gamma camera 5 having the above configuration, the same effect as that of the gamma camera 3 according to the third embodiment can be obtained. Further, by integrating the radiation detection element 13 and the laser light emitting element 32, it becomes easy to arrange them adjacent to each other in the direction of the pinhole 11. In the fifth and subsequent embodiments, the laser light emitting element 32 is used as the light emitting element, but a light emitting element other than the laser light emitting element may be used. Further, the modifications shown in the first and second embodiments can be appropriately applied to the fifth embodiment.

[Embodiment 6]
Next, as the sixth embodiment, the arrangement of the radiation detection element 13 and the laser light emitting element 32 will be described with reference to FIG. In the gamma camera 4 and the gamma camera 5, as shown in FIGS. 10 (a) and 10 (i), the laser light emitting elements 32 and the radiation detection elements 13 correspond to the same number and are arranged on a substantially plane. I explained the aspect.

However, as shown in FIGS. 10 (c), (d), (e), and (f), the pitch of the laser light emitting element 32 does not have to match the pitch of the radiation detection element 13. That is, the number of radiation detection elements 13 and the number of laser light emitting elements 32 do not have to match. For example, as shown in FIGS. 10 (c) and 10 (d), when the number of laser light emitting elements 32 is larger than the number of radiation detection elements 13, a plurality of laser light emitting elements 32 corresponding to one radiation detection element 13 Is decided in advance. Then, the corresponding plurality of laser light emitting elements 32 are arranged so as to emit light in the same direction as the line connecting the one associated radiation detection element 13 and the pinhole 11. When a gamma ray is detected by one radiation detection element 13, a plurality of laser light emitting elements 32 associated with the radiation detection element 13 are controlled to emit light.

On the contrary, as shown in FIGS. 10 (e) and 10 (f), when the number of the laser light emitting elements 32 is smaller than the number of the radiation detection elements 13, one laser light emitting element corresponding to the plurality of radiation detection elements 13 is used. 32 is decided in advance. Then, the corresponding laser light emitting element 32 is arranged so as to emit light in the same direction as the line connecting the vicinity of the center of the detection surface of the associated plurality of radiation detection elements 13 and the pinhole 11. When a gamma ray is detected by any of the plurality of radiation detection elements 13, one laser light emitting element 32 associated with the radiation detection element 13 is controlled to emit light.

Further, as shown in FIGS. 10 (g) and 10 (h), the radiation detection element 13 may not be pixelated. When the radiation detection element 13 is not pixelated, the control shown in the flowchart of FIG. 11A is performed. That is, when the control unit 16 receives the gamma ray detection signal from the radiation detection element 13 (step S111), the control unit 16 calculates at which position of the radiation detection element 13 the gamma ray is detected (step S112). Next, the control unit 16 determines the laser light emitting element 32 located at the position closest to the line segment connecting the gamma ray detection position and the pinhole 11 (step S113). Then, the control unit 16 causes the determined laser light emitting element 32 to emit light (step S114). FIG. 11B shows a block configuration diagram of the gamma cameras 4 and 5 that perform such control.

Further, as shown in FIGS. 10 (b), (d), (f), and (h), a plurality of laser light emitting elements 32 may be arranged in a curved surface. If the element array in which a plurality of laser light emitting elements 32 are arranged is curved so that the light emitting surface (emission direction) faces the pinhole 11, light can be efficiently emitted to the outside, and a gamma camera can be manufactured and assembled. Becomes easier. Further, instead of or in addition to these forms, a plurality of radiation detection elements 13 may be arranged in a curved surface (not shown). If the element array in which a plurality of radiation detection elements 13 are arranged is curved so that the gamma ray detection surface faces the pinhole 11, the gamma ray detection efficiency is increased.

Further, as shown in FIG. 10 (j), the integrated laser light emitting element 32 and the radiation detection element 13 may be curvedly arranged. By integrating the laser light emitting element 32 and the radiation detection element 13, it is possible to improve the gamma ray detection efficiency and the accuracy of the light emission direction. Further, both the light emitting surface of the laser light emitting element 32 and the detection surface of the radiation detecting element 13 can be arranged toward the pinhole 11, and both the gamma ray detection efficiency and the light emission efficiency to the outside are increased. .. It also facilitates the manufacture and assembly of gamma cameras.

As described above, there are various types in which the radiation detection element 13 and the light emitting element 32 corresponding to the radiation detection element 13 are arranged adjacent to each other along the traveling direction of radiation. The radiation detection element 13 and the light emitting element 32 corresponding to the radiation detection element 13 may be arranged apart from each other or may be arranged in contact with each other. By arranging the radiation detection element 13 and the light emitting element 32 corresponding to the radiation detection element 13 apart from each other, the degree of freedom in the arrangement of both is improved. Therefore, the degree of freedom in structural design of the gamma camera is increased.

Further, the radiation detection element 13 and the light emitting element 32 do not have to have a one-to-one correspondence. It is preferable that at least the light emitting surface of the laser light emitting element 32 is arranged toward the pinhole 11. This is because the laser beam emitted by the laser light emitting element 32 has high directivity. Further, the detection surface of the radiation detection element 13 does not necessarily have to face the direction of the pinhole 11, but it is preferable to arrange the radiation detection element 13 toward the pinhole 11 as much as possible. Thereby, the detection efficiency of the radiation detection element 13 can be improved.

[Embodiment 7]
Next, the gamma camera 6 according to the seventh embodiment will be described with reference to the drawings. FIG. 12 is a schematic vertical sectional view of the gamma camera 6 and its control flow. FIG. 13 is a plan view showing an arrangement of the radiation detection element 13 and the laser light emitting element 32. FIG. 14 is a perspective view showing an arrangement of the radiation detection element 13 and the laser light emitting element 32.

As shown in FIG. 12A, in the gamma camera 6, the radiation detection element 13 is arranged closer to the pinhole 11 than the laser light emitting element 32. The laser light emitting element 32 is arranged on the side farther from the pinhole 11 than the radiation detection element 13. The corresponding radiation detection element 13 and the laser light emitting element 32 are arranged adjacent to each other in a direction intersecting the traveling direction of the gamma ray. Further, the radiation detection element 13 and the laser light emitting element 32 are arranged apart from each other. The flowchart shown in FIG. 12B will be described later.

The arrangement of the radiation detection element 13 and the laser light emitting element 32 will be described in more detail. As shown in FIG. 13, the radiation detection element 13 and the laser light emitting element 32 are arranged in two orthogonal directions with a distance L1 and a distance L2, respectively. The shifting direction is a direction that intersects with the traveling direction of the gamma ray, and in the present embodiment, is a direction orthogonal to the traveling direction of the gamma ray. The distance L1 and the distance L2 are both more than half the width of the radiation detection element 13 along each direction of the distance L1 and the distance L2. By arranging in this way, the laser beam can be emitted from the laser light emitting element 32 while avoiding the radiation detection element 13. Further, the radiation detection elements 13 can be arranged as closely as possible, and the accuracy of the detection position is improved. The amount of shift may be larger, but the detection efficiency or the position accuracy of detection may be lowered accordingly.

In order to easily form the above arrangement, it is preferable to use a spherical support portion 40 centered on the pinhole 11 as shown in FIGS. 12 (a) and 14 (a). The support portion 40 has a curved plate shape and supports the radiation detection element 13 on the side close to the pinhole 11. Further, the support portion 40 supports the laser light emitting element 32 on the side farther from the pinhole 11 than the radiation detection element 13. The support portion 40 is provided with a plurality of through holes 41 through which the laser beam L is passed in advance. The through hole 41 is provided so as to face the light emitting surface of the plurality of laser light emitting elements 32 and to face the gap between the plurality of radiation detection elements 13.

In other words, the support portion 40 supports the laser light emitting element 32 so that the laser light L can be irradiated toward the pinhole 11 from the gap between the radiation detection elements 13. If the support portion 40 is used, the laser beam L from the laser light emitting element 32 can be arranged so as to pass through the hole of the pinhole 11 without performing complicated optical axis adjustment work. Although the radiation detection element 13 and the laser light emitting element 32 are drawn as if they are arranged apart from the support portion 40 in FIG. 14, they are actually in contact with each other as shown in FIG. 12 (a).

The gamma camera 6 is one of the effective embodiments when the laser light emitting element 32 becomes large in the incident direction of the gamma ray. By arranging the radiation detection element 13 and the corresponding laser light emitting element 32 adjacent to each other in the intersecting direction in this way, the degree of freedom in the arrangement of the radiation detection element 13 and the laser light emitting element 32 is improved. Therefore, the degree of freedom in structural design of the gamma camera is increased.

In the gamma camera 6, since the radiation detection element 13 and the laser light emitting element 32 are arranged adjacent to each other in the direction intersecting the traveling direction of the gamma ray, the incident axis of the gamma ray and the optical axis of the laser are slightly deviated. Therefore, after gamma ray detection, it is preferable to perform control to select an appropriate laser emitting element 32 corresponding to the vicinity of the radiation detecting element 13. Specifically, as shown in the flowchart shown in FIG. 12B, when the control unit 16 receives the gamma ray detection signal from the radiation detection element 13 (step S121), the control unit 16 receives a gamma ray detection signal (step S121), and the laser is located near the radiation detection element 13. The light emitting element 32 is selected (step S122). Then, the control unit 16 causes the selected laser light emitting element 32 to emit light (step S123).

The method of selecting the laser emitting element 32 in the above flowchart includes (1) a method of selecting all the laser emitting elements 32 adjacent to the radiation detecting element 13, and (2) (for example, the right side) the radiation detecting element 13. There is a method of selecting only a specific adjacent laser emitting element 32, or (3) a method of randomly selecting only one element from the laser emitting elements 32 adjacent to the radiation detecting element 13.

In the present embodiment, as described above, in principle, the incident axis of the gamma ray and the optical axis of the laser beam emitted corresponding to the gamma ray are slightly deviated from each other. Therefore, the projection position of the laser beam is also slightly deviated. However, since the size (width in the direction intersecting the traveling direction of the gamma ray) of the radiation detection element 13 (or the laser light emitting element 32) that causes the deviation is small and the projection distance is small, the magnitude of the deviation is small. Therefore, there is no problem in practical use even if the position of the projected light shifts. It is preferable that the angle of deviation between the incident axis of the gamma ray and the emitted laser optical axis is within the same angle as the angle error when detecting the incident angle of the gamma ray. Specifically, as shown in FIG. 15, when the angle seen by the adjacent radiation detection elements 13 with respect to the pinhole 11 is θ1, the deviation between the incident axis of the gamma ray R and the emitted laser optical axis L The angle θ2 is more preferably half or less of θ1.

[Embodiment 8]
Next, the shield 22 of the gamma camera according to the eighth embodiment will be described with reference to the drawings. 16 (a) is a perspective view of the shield 22 according to the eighth embodiment, and FIG. 16 (b) is a vertical sectional view thereof. The collimator shown in the first to seventh embodiments is a pinhole collimator. On the other hand, the shield 22 according to the eighth embodiment has a parallel porous (parallel hole) collimator as shown in FIGS. 16A and 16B. In this case, the plurality of holes 22A provided serve as a collimator. As described above, in the embodiment of the present invention, not only the pinhole collimator but also a general parallel porous collimator can be applied. In the case of a parallel porous collimator, the wider the opening area of the hole 22A, the higher the radiation detection sensitivity. On the other hand, since the size of the imaging / projection field of view and the size of the detector match, it is preferable to apply it to a handheld size device used outside the body. Even when such a collimator is used, it is possible to easily emit light in the direction opposite to the incident direction of the incident radiation.

[Embodiment 9]
Next, the shields 23 and 24 of the gamma camera according to the ninth embodiment will be described with reference to the drawings. As shown in FIG. 17A, the shield 23 according to the ninth embodiment has a condensing porous type collimator. In this case, a plurality of holes 23A are provided as a collimator. In this embodiment, the size of the image pickup / projection field of view is smaller than the size of the detector portion, but the spatial resolution finer than the spacing of the radiation detection elements 13 can be obtained due to the enlargement effect. Further, as shown in FIG. 17B, a shield 24 having a divergent porous collimator may be used. In this case, the plurality of holes 24A provided serve as a collimator. In this form, the size of the image pickup / projection field of view can be made larger than the size of the detector portion, but the spatial resolution is deteriorated more than the distance between the radiation detection elements 13. It is preferable to use these collimators 23A and 24A properly according to the place of use and the purpose of use. Even when such a collimator is used, it is possible to easily emit light in the direction opposite to the incident direction of the incident radiation.

(Application example)
The gamma camera of each of the above embodiments can be applied to medical treatment. FIG. 18 is a schematic view showing an example of application of the gamma camera according to each of the above embodiments to microscopic surgery or robotic surgery. As shown in FIG. 18, in addition to the optical camera and forceps to be inserted into the port in normal arthroscopic surgery or robotic surgery, the gamma camera of each of the above embodiments is inserted near the affected area. Since the gamma camera alone projects the distribution of the radioactive drug on the surface of the affected area, the operator can visually recognize the distribution of the radioactive drug projected on the surface of the affected area through the image of a normal optical camera.

(Modification example)
In each of the above embodiments, a medical gamma camera has been described as an example. However, embodiments of the present invention do not necessarily have to be for medical use. For example, it may be configured as a radiation camera for confirming the position of a pollution source in, for example, a nuclear power plant, a facility for using radioactive materials, a nuclear fuel processing facility, a reprocessing facility, or the like. Alternatively, it may be constructed as a radiation camera for security purposes to monitor the presence or absence of radioactive substances and nuclear substances in luggage at airports, borders, and the like.

With such a configuration, it is possible to visualize, for example, the part to be decontaminated. In this case, the light emitting element may be configured so that the light emitting time or the light emitting intensity of the emitted light can be changed according to the detected radiation intensity (energy intensity, counting rate or air dose rate). Since the distance to the radiation source is long, it is preferable to use a laser light emitting element having high directivity as the light emitting element. Further, when the radiation energy intensity of the radiation source to be detected covers a wide range, it is preferable to set the thickness of the shield to a thickness capable of shielding the radiation of the maximum energy.

〔summary〕
The radiation camera according to the first aspect of the present invention has a collimator that collimates incident radiation, a radiation detection unit that detects radiation that has passed through the collimator, and a radiation detection unit that directs the radiation detected in the direction opposite to the incident direction. It is provided with a light emitting unit that emits visible light.

According to the above configuration, when the radiation detection unit detects the radiation that has passed through the collimator, the incident direction of the radiation is determined from the positions of the collimator and the radiation detection unit. By emitting visible light from the light emitting element in the direction opposite to the incident direction of the radiation, it is possible to project visible light toward the radiation source without having to calibrate the projection direction according to the position of the radiation camera. This makes it possible to visualize, for example, the position of the affected area on the skin.

In the radiation camera according to the second aspect of the present invention, the radiation detection unit is composed of one or a plurality of radiation detection elements, and the light emitting unit is composed of one or a plurality of light emitting elements. The detection element and the light emitting element that emits visible light in the direction opposite to the incident direction of the radiation detected by the radiation detection element may be associated with each other.

According to the above configuration, by associating one or more radiation detection elements with one or more light emitting elements, visible light is easily emitted from the light emitting unit in the direction opposite to the incident direction of the radiation. be able to.

In the radiation camera according to the third aspect of the present invention, the radiation detection element and the light emitting element corresponding to the radiation detection element may be arranged adjacent to each other along the traveling direction of the radiation.

According to the above configuration, by arranging the radiation detection element and the corresponding light emitting element adjacent to each other along the traveling direction of the radiation, the direction of the emitted light can be easily aligned with the incident direction of the incident radiation. Can be done.

In the radiation camera according to the fourth aspect of the present invention, the radiation detection element and the light emitting element corresponding to the radiation detection element may be integrated.

According to the above configuration, by integrating the radiation detection element and the corresponding light emitting element, the radiation detection element and the corresponding light emitting element can be easily arranged adjacent to each other.

In the radiation camera according to the fifth aspect of the present invention, the radiation detection element and the light emitting element corresponding to the radiation detection element may be arranged adjacent to each other in a direction intersecting the traveling direction of the radiation.

According to the above configuration, by arranging the radiation detection element and the corresponding light emitting element adjacent to each other in the direction intersecting the traveling direction of the radiation, the direction of the emitted light can be easily directed to the incident direction of the incident radiation. Can be matched.

In the radiation camera according to the sixth aspect of the present invention, the radiation detection element and the light emitting element corresponding to the radiation detection element may be arranged apart from each other.

According to the above configuration, by arranging the radiation detection element and the corresponding light emitting element apart from each other, the degree of freedom in the arrangement of the radiation detection element and the corresponding light emitting element is increased. Therefore, the degree of freedom in the structural design of the radiation camera is increased.

The radiation camera according to the seventh aspect of the present invention has a support portion that supports the radiation detection element on the side closer to the collimator and supports the light emitting element on the side farther from the collimator than the radiation detection element. The support portion may have a plurality of through holes provided so as to face each of the light emitting surfaces of the plurality of the light emitting elements and to face the gaps between the plurality of radiation detection elements.

According to the above configuration, the light from the light emitting element can be arranged so as to pass through the hole of the pinhole without complicated optical axis adjustment work.

In the radiation camera according to the eighth aspect of the present invention, the plurality of radiation detection elements and the plurality of light emitting elements may be arranged in a plane or a curved surface, respectively.

According to the above configuration, by arranging the radiation detection element or the light emitting element in a plane, manufacturing becomes easy. Further, by arranging the radiation detection elements in a curved surface (that is, toward the incident portion), the radiation detection efficiency is increased. Further, by arranging the light emitting elements in a curved surface, the emitted light can be efficiently emitted to the outside.

In the radiation camera according to the ninth aspect of the present invention, the collimator may be at least one of a pinhole collimator, a parallel hole collimator, a condensing porous collimator, and a divergent porous collimator.

According to the above configuration, it is possible to easily match the direction of the emitted light with the incident direction of the incident radiation regardless of which one is used.

The radiation camera according to the tenth aspect of the present invention may further include a control unit that controls the light emitting unit so as to emit visible light in the direction opposite to the incident direction of the radiation detected by the radiation detection unit. ..

According to the above configuration, the portability is improved by providing the control unit inside the radiation camera. Further, by integrating the radiation detection unit, the light emitting unit, and the control unit, a compact configuration can be obtained.

In the radiation camera according to the eleventh aspect of the present invention, the control unit may adjust the light emission time or the light emission intensity of the light emitting unit based on the intensity of the radiation detected by the radiation detection unit.

According to the above configuration, when the accumulation amount of radionuclides correlates with the malignancy of cancer, the information on the intensity of radiation is considered to be useful for distinguishing cancer. More detailed information can be obtained by displaying the radiation intensity by adjusting the light emission time or the light emission intensity based on the radiation intensity. Further, when measuring an environment in which a plurality of radiations having different intensities are detected, since the light can be projected to the position of the radiation source, it is possible to directly recognize how much radiation is emitted from which position.

Further, the method of operating the radiation camera according to one aspect of the present invention includes a step of detecting collimated radiation and a step of emitting visible light in the direction opposite to the incident direction of the detected radiation. More specifically, for example, in the method of operating a medical radiation camera, a step of collimating and detecting gamma rays emitted from a radiopharmaceutical accumulated in a specific part of a living body and the reverse of the incident direction of the detected gamma rays are used. Includes a step of emitting visible light in a direction.

The present invention is not limited to the above-described embodiments, and various modifications can be made within the scope of the claims, and the embodiments obtained by appropriately combining the technical means disclosed in the different embodiments. Is also included in the technical scope of the present invention.

1,1A, 2,3,4,5,6 Gamma camera (radiation camera)
8,10,20,22,23,24 Shielding body 8A, 10A Upper part 8B, 10B Lower part 8C, 10C Tip part 8D, 11 Pinhole (collimator)
9 Housing 10D Open end 12 Radiation detection unit 13 Radiation detection element (radiation detection unit)
14,30 light emitting element (light emitting part)
15 Reflector 15A Reflector 15B Drive 16 Control 22A, 23A, 24A Hole (collimator)
32 Laser light emitting element (light emitting part)
40 Support 41 Through hole 50 Radioactive source 51 Skin

Claims (11)

1. A collimator that collimates the incident radiation,
   A radiation detection unit that detects radiation that has passed through the collimator,
   A light emitting unit that emits visible light in the direction opposite to the incident direction of the radiation detected by the radiation detection unit, and a light emitting unit.
   Radiation camera equipped with.
2. The radiation detection unit is composed of one or a plurality of radiation detection elements, and the light emitting unit is composed of one or a plurality of light emitting elements, and the radiation detection element and the radiation detection element detect. The radiation camera according to claim 1, wherein the light emitting element that emits visible light in the direction opposite to the incident direction of the radiation is associated with the light emitting element.
3. The radiation camera according to claim 2, wherein the radiation detection element and the light emitting element corresponding to the radiation detection element are arranged adjacent to each other along the traveling direction of the radiation.
4. The radiation camera according to claim 3, wherein the radiation detection element and the light emitting element corresponding to the radiation detection element are integrated.
5. The radiation camera according to claim 3, wherein the radiation detection element and the light emitting element corresponding to the radiation detection element are arranged adjacent to each other in a direction intersecting the traveling direction of the radiation.
6. The radiation camera according to claim 5, wherein the radiation detection element and the light emitting element corresponding to the radiation detection element are arranged apart from each other.
7. It has a support portion that supports the radiation detection element on a side closer to the collimator and supports the light emitting element on a side farther from the collimator than the radiation detection element, and the support portion emits light from a plurality of the light emitting elements. The radiation camera according to claim 6, which has a plurality of through holes facing each other and facing a gap between the plurality of radiation detection elements.
8. The radiation camera according to any one of claims 3 to 7, wherein the plurality of radiation detection elements and the plurality of light emitting elements are arranged in a plane or a curved surface, respectively.
9. The radiation camera according to any one of claims 1 to 8, wherein the collimeter is at least one of a pinhole collimeter, a parallel hole collimeter, a condensing porous collimeter, and a divergent porous collimeter.
10. The radiation according to any one of claims 1 to 9, further comprising a control unit that controls the light emitting unit so that visible light is emitted in the direction opposite to the incident direction of the radiation detected by the radiation detection unit. camera.
11. The radiation camera according to claim 10, wherein the control unit adjusts the light emission time or the light emission intensity of the light emitting unit based on the intensity of the radiation detected by the radiation detection unit.

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