Radiation detector

Abstract

A radiation detector is provided that enables an operator to more accurately identify the location of tissues in the body that have absorbed radioactive nuclides. The radiation detector (1) includes: a probe (10) with a built-in radiation detection element (20) that can be inserted into the body, a notification unit (30) provided on the probe (10), and a control unit (50) that activates the notification unit (30) based on the radiation detection result measured by the radiation detection element (20).

Description

Technical Field

[0001] This invention relates to a radiation detector. Background Technology

[0002] In the past, it has been known that cancer cells readily absorb specific compounds, or that compounds of a certain size easily accumulate in tissues. To locate such cancer cells or tissues, a compound containing a radionuclide is administered to the patient, and its location is then pinpointed using a gamma camera. For example, a known method involves administering a compound preparation containing 99mTc to the patient, followed by locating and removing lymph nodes where the compound has accumulated. To implement this method, Non-Patent Document 1 discloses a portable gamma camera capable of determining during surgery whether cancer cells have metastasized to sentinel lymph nodes.

[0003] Furthermore, Non-Patent Literature 2 discloses a method that involves intravenously administering F-18-labeled FDG (fluorodeoxyglucose), which has demonstrated excellent performance in PET (Positron Emission Tomography) examinations, and then detecting lymph node metastasis based on the degree of FDG absorption in lymph nodes. This is a method designed to minimize the scope of resection and reduce surgical invasiveness.

[0004] [Existing Technical Documents]

[0005] [Non-patent literature]

[0006] Non-patent literature 1: Kunihiko Yokoyama, Norihisa Rinami, Koichiro Tsugawa, and Koichi Miwa, “Detection method of isotopes in sentinel lymph nodes”, Nichi-De-i-ho (Japanese Medical Journal), Vol. 46, No. 2, pp. 212-217, 2001.

[0007] Non-patent document 2: Douglas A.Murrey, Jr. et al., "Perioperative18F-fluorodeoxyglucose-guided imaging using the becquerel as a quantitative measure for optimizing surgical resection in patients with advanced malignancy," The American Journal of Surgery, 198, pp.834-840, 2009. Summary of the Invention

[0008] [The problem the invention aims to solve]

[0009] However, because the gamma camera disclosed in Non-Patent Document 1 displays the detected radiation energy distribution image on a separate monitor, it is difficult to determine the positional relationship between the displayed image and the surgical site. Furthermore, the technology disclosed in Non-Patent Document 2 does not involve a method for immediately transmitting the degree of FDG absorption in the lymph nodes to the surgeon. In the past, gamma probes, forceps-type PET scanners, embedded detectors, and methods combining in-body and external detectors have been developed as intraoperative radiation detectors. However, in all cases, since the mechanism involves displaying an image of isotope distribution or radiation energy value on the radiation device's monitor, the operator must remove their viewpoint from the surgical field each time a measurement is performed. Therefore, it is difficult to accurately identify the location of the affected area based on the measured radiation energy. For example, in endoscopic or robot-assisted surgery, it is expected that the operator can accurately determine the location of the affected area from the viewed camera image.

[0010] One aspect of the present invention is to provide a radiation detector that enables an operator to more accurately identify the location of tissues in the body that have absorbed radionuclides.

[0011] [Technical means to solve the problem]

[0012] To solve the above problems, a radiation detector of one aspect of the present invention includes: a probe having a built-in radiation detection element and being insertable into a body; a notification unit disposed on the probe; and a control unit that activates the notification unit based on the radiation detection result measured by the radiation detection element.

[0013] Furthermore, in one aspect of the present invention, the radiation detector is configured as a surgical grasping forceps that can be inserted into the body. The two front ends of the grasping forceps are configured as two probes, each with a built-in radiation detection element. The radiation detector includes: a notification unit disposed in the grasping forceps; and a control unit that activates the notification unit based on the detection result of annihilated gamma rays, wherein the detection result is obtained by simultaneous counting by the radiation detection elements each built into the two probes.

[0014] [Invention Effects]

[0015] By means of one aspect of the present invention, a radiation detector can be provided that enables an operator to more accurately identify the location of tissues in the body that have absorbed radionuclides. Attached Figure Description

[0016] [ Figure 1 [Illustration 1] is an overall structural diagram of the radiation detector of embodiment 1 of the present invention.

[0017] [ Figure 2 This is an example of the shape of the light-emitting part in implementation form 1. Specifically, Figure 2(a) shows an example of the shape of the light-emitting part that is continuously arranged around the outer peripheral surface of the probe. Figure 2 (b) shows an example of the shape of a light-emitting part that protrudes locally from the outer surface of the probe. Figure 2 (c) shows an example of the shape of the light-emitting part located at multiple positions on the outer surface of the probe.

[0018] [ Figure 3 [ ] is a block diagram of the control functions of the radiation detector implementing form 1.

[0019] [ Figure 4 This is a schematic diagram that includes the emission control flowchart of the radiation detector in Embodiment 1. Specifically, Figure 4 (a) Figure 4 (c) and Figure 4 (e) represents the first, second, and third flowcharts, respectively. Figure 4 (b) Figure 4 (d) and Figure 4 (f) is an example diagram of the radiation detection results and emission timing corresponding to each of these flowchart examples.

[0020] [ Figure 5 [] is a schematic diagram illustrating an example of the use of the radiation detector in Embodiment 1.

[0021] [ Figure 6 [Illustration] is an overall structural diagram of a radiation detector that uses a scintillation detection element.

[0022] [ Figure 7 [ ] is a block diagram of the control functions of a radiation detector that uses a scintillation detection element.

[0023] [ Figure 8 [Illustration 2] is a schematic diagram of the structure of a radiation detector for surgical grasping forceps according to embodiment 2 of the present invention.

[0024] [ Figure 9 This is a schematic diagram that includes the emission control flowchart of the radiation detector in Embodiment 2. Specifically, Figure 9 (a) Figure 9 (c) and Figure 9 (e) represents the fourth, fifth, and sixth flowcharts, respectively. Figure 9 (b) Figure 9 (d) and Figure 9 (f) is an example diagram of the radiation detection results and emission timing corresponding to each of these flowchart examples.

[0025] [ Figure 10 [] is a schematic diagram illustrating an example of the use of the radiation detector in embodiment 2.

[0026] [ Figure 11[This is a schematic diagram of the structure of a radiation detector for surgical grasping forceps, which is an embodiment 3 of the present invention.]

[0027] [ Figure 12 ] Figure 12 (a) Figure 12 (b) Figure 12 (c) is a diagram showing the relationship between the opening angle of the clamping part of the radiation detector in embodiment 3 and the size of the object being measured.

[0028] [ Figure 13 [] is a control flowchart indicating the start and end of radiation measurement by the radiation detector in implementation form 3.

[0029] [ Figure 14 [This is a cross-sectional view of the scintillator of the radiation detector in embodiment 4.]

[0030] [ Figure 15 [ ] is a flowchart representing the measurement method performed by the control unit of the radiation detector in embodiment 5.

[0031] [ Figure 16 [This is a flowchart of the measurement method for implementing a variation of form 5.] Detailed Implementation

[0032] [Implementation Method 1]

[0033] The following description refers to Embodiment 1 of the present invention. Figure 1 This is an overall structural diagram of the medical radiation detector 1 according to Embodiment 1 of the present invention. Figure 2 This is an example of the shape of the light-emitting part in Embodiment 1. Figure 2 It includes a perspective view of a probe equipped with a light-emitting part, and a cross-sectional view taken radially along the probe. Figure 3 This is a functional block diagram of the radiation detector 1 in Embodiment 1. The radiation detector 1 detects the radiation R emitted by radioactive nuclides accumulated in the affected area, and reports it to the operator (practitioner) when the measured value (count) of radiation R meets predetermined conditions.

[0034] (Structure of Radiation Detector 1)

[0035] like Figure 1 As shown, the radiation detector 1 includes a probe 10 that can be inserted into the body and an operation unit 80. The probe 10 has a built-in radiation detection element 20 and a light-emitting unit (notification unit) 30. Operation of the light-emitting unit 30 means that the light-emitting unit 30 emits light. The light-emitting unit 30 is one example of a notification unit. The operation unit 80 includes a control unit 50, an input / output interface (I / O) 62, a setting unit 64, and a counting unit 66. Furthermore, the operation unit 80 includes an input unit 70.

[0036] A radiation detection element 20 is disposed at the front end of the probe 10. The operator can bring the front end of the probe 10 close to the affected area to confirm the detection level of radiation R. The type of radiation detection element 20 is not particularly limited, but small detection elements such as semiconductor detection elements or scintillation detection elements are preferred. CdTe (CZT) semiconductor detection elements, Si semiconductor detection elements, Ge semiconductor detection elements, etc., can be used as semiconductor detection elements. CsI (T1) scintillators, NaI (T1) scintillators, etc., can be used as scintillation detection elements. The radiation detection element 20 converts the energy of radiation R into an electrical signal and outputs it. The structure for converting radiation energy into an electrical signal can use a known structure.

[0037] The method for determining the incident direction of radiation R measured by the radiation detection element 20 can be a collimator method, a Compton camera method, or a simultaneous counting method. The collimator method includes a collimator that restricts the incident direction of radiation R incident on the radiation detection element 20. Then, based on the position of the radiation detection element 20 where radiation R is measured, the incident direction of radiation R incident on the collimator can be determined. In the case of using the Compton camera method, a Compton camera radiation detection element 20 with a scattering section and an absorption section is used. Then, the incident direction of the gamma rays can be determined from the position where the gamma rays are scattered in the scattering section and the position where they are absorbed in the absorption section. In the case of using the simultaneous counting method, two radiation detection elements 20 are arranged facing each other. Then, only when both radiation detection elements 20 are counted simultaneously is the radiation counted, thereby enabling the determination that there is a radiation source between the two radiation detection elements 20. The simultaneous counting method targets nuclides that emit positrons.

[0038] The light-emitting part 30 is disposed at the front end of the probe 10. The light-emitting part 30 is disposed near the radiation detection element 20. When the radiation detection element 20 detects radiation R that meets predetermined conditions, the light-emitting part 30 has the function of notifying the operator. The operator brings the front end of the probe 10 close to the affected area to confirm whether radiation R has been detected. Therefore, the light-emitting part 30 is disposed at the front end of the probe 10 in a manner that allows the operator to identify the light-emitting part 30 emitting light without moving their line of sight when operating the probe 10.

[0039] The light-emitting part 30 is disposed on the outer surface of the probe 10. More specifically, as... Figure 2 As shown in (a), the light-emitting portion 30 is continuously arranged around the outer peripheral surface of the probe 10. However, the shape of the light-emitting portion 30 is not limited to this shape. Figure 2 In the example shown in (a), the light-emitting part 30 surrounds the probe 10 at the same height as its outer peripheral surface. However, as Figure 2 As shown in (b), the structure of the light-emitting part 30 may be such that at least a portion protrudes from the outer surface of the probe 10. Furthermore, as... Figure 2As shown in (c), the light-emitting part 30 can also be disposed at multiple locations on the outer surface of the probe 10. In any configuration, even if the orientation of the probe 10 changes, the operator can reliably identify that the light-emitting part 30 is emitting light.

[0040] The light-emitting part 30 is made of a light-guiding material, for example, capable of guiding light, and can guide and emit the light emitted by the light-emitting element 32 built into it to the outside. The light-emitting element 32, for example, is a light-emitting diode (LED). The number of light-emitting elements 32 can be one or more.

[0041] An input unit 70 is provided on the outer surface of the operation unit 80. The input unit 70, for example, is a device capable of inputting a threshold number of detections of radiation R that causes the light-emitting unit 30 to emit light, such as a touch panel LCD display. The cable 82 is a power cable that supplies power to the radiation detector 1. Furthermore, the cable 82 can also serve as an information communication cable between the radiation detector 1 and the outside. Alternatively, the cable 82 can be omitted by integrating the power supply into the radiation detector 1.

[0042] (Control of Radiation Detector 1)

[0043] Figure 3 This is a functional block diagram related to the control of the radiation detector 1 in Embodiment 1. The control unit 50 can control the entire radiation detector 1. The control unit 50 includes a processor 52 and a memory 54. The memory 54 is composed of, for example, volatile RAM (Random Access Memory) and non-volatile ROM (Read Only Memory), and can store various control programs and data. In addition, the memory 54 can store the threshold value of the radiation measurement value that causes the light-emitting part 30 to emit light and the emission time as set values. The processor 52 is, for example, a CPU (Central Processing Unit) or an MPU (Micro Processing Unit). The processor 52 reads various control programs from the ROM, expands them in the RAM, and executes these programs, thus functioning as a setting unit 64 and a counting unit 66. Alternatively, the processor 52 can also be a dedicated processor such as an ASIC (Application Specific Integrated Circuit) or an FPGA (Field Programmable Gate Array). The radiation detection element 20, the light-emitting element 32, the control unit 50, the I / O 62, the setting unit 64, the counting unit 66, and the input unit 70 are electrically connected via the bus 56.

[0044] The input / output interface (I / O) 62 allows for the transmission and reception of signals and information with external devices. The setting unit 64 acquires the threshold value input by the operator and sets it in the control unit 50. The threshold value corresponds to the radiation detection result used to determine whether to make the light-emitting unit 30 emit light. Specifically, the setting unit 64 acquires information about the threshold value input by the operator from the input unit 70 via, for example, I / O 62. The setting unit 64 sets the threshold value input by the operator in the control unit 50 by storing the acquired information about the threshold value in the memory 54 or a setting register. The counting unit 66 acquires the electrical signal output by the radiation detection element 20, counts the number of radiation measurements, and outputs the result to the control unit 50.

[0045] The control unit 50 causes the light-emitting unit 30 to emit light based on the radiation detection results obtained by the radiation detection element 20. For example, the control unit 50 causes the light-emitting unit 30 to emit light every time the counting unit 66 counts radiation. Alternatively, when the number of radiation measurements obtained from the counting unit 66 exceeds a set threshold, the control unit 50 can control the light-emitting element 3 to emit light for a predetermined time. If the emission time is too long, it will be impossible to distinguish the detection status of each radiation. If the emission time is too short, there is a risk that the emission may not be recognized. Therefore, it is preferable to preset an appropriate emission time. Alternatively, the configuration can be made so that the operator can set the emission time from the input unit 70 according to the measurement conditions.

[0046] Reference Figure 4 The control method for making the light-emitting part 30 emit light will be explained. As an example, such as Figure 4 (a) First flowchart example and Figure 4 As shown in (b), each time the counting unit 66 counts radiation (step S100), the control unit 50 causes the light-emitting element 32 to emit light once at a predetermined time (step S101). This is an example of light emission independent of the radiation count rate. In this case, the operator can observe the emission frequency to determine whether they are approaching a lesion (radiation source) where radioactive nuclides have accumulated. If the emission frequency is high, it can be determined that they are approaching a lesion. The operator can change the position of the probe 10 to confirm the emission frequency and determine that a lesion exists at the location with the high emission frequency.

[0047] Furthermore, the control unit 50 can control the light-emitting unit 30 to emit light when the radiation count rate exceeds a predetermined value. The count rate is expressed, for example, as the average radiation measured in cps (counts per second). Figure 4 (c) Second flowchart and Figure 4As shown in (d), the counting unit 66 accumulates the number of radiation measurements within a predetermined time period (e.g., several seconds to tens of seconds), and then divides this number by the predetermined time duration to calculate the count rate (step S110). Next, the control unit 50 determines whether the count rate calculated by the counting unit 66 is above a predetermined count rate (threshold) (step S111). If the count rate is above the predetermined threshold (step S111: Yes), the control unit 50 instructs the light-emitting unit 30 to emit light for a predetermined time (step S112). If the count rate is not above the predetermined threshold (step S111: No), the control unit 50 does not instruct the light-emitting unit 30 to emit light, but returns to step S111 and determines whether the count rate within a slightly offset predetermined time period is above the predetermined count rate. If there is light emission, the operator can determine that they have approached the affected area.

[0048] As another example, the control unit 50 can control the light-emitting unit 30 to change the light emission pattern according to the radiation count or count rate. Figure 4 (e) Third flowchart example and Figure 4 As shown in (f), the counting unit 66 counts the measured radiation number within a predetermined time period (e.g., several seconds to tens of seconds) (step S120) and calculates the count rate (step S121). Next, the control unit 50 causes the light-emitting unit 30 to emit light in a predetermined manner according to the count rate (step S122). For example, if the radiation level is below a first threshold, the control unit 50 does not cause the light-emitting element 32 to emit light; if the radiation level is above the first threshold but below a second threshold, the light-emitting element 32 emits blue light; if the radiation level is above the second threshold, the light-emitting element 32 emits red light. If red light is emitted, the operator can determine that the radiation is very close to the affected area or that the amount of radioactive nuclide accumulated in the affected area is large. Furthermore, the control unit 50 can control the light-emitting unit 30 to change its luminescence intensity (brightness) according to the count rate. The stronger (brighter) the emitted light, the closer the radiation is to the affected area or the greater the amount of radioactive nuclide accumulated in the affected area. Additionally, the control unit 50 can control the light-emitting unit 30 according to the count rate to change its luminescence mode or luminescence time.

[0049] The above threshold is preferably set appropriately by the operator based on factors such as the type of radionuclide, the dose of the radionuclide administered, the amount of radionuclide accumulation (size of the affected area), and the elapsed time from administration to measurement.

[0050] (Example of the use of radiation detector 1)

[0051] like Figure 5As shown, the radiation detector 1 can be used in endoscopic or robot-assisted surgery by being inserted into the patient through a puncture cannula. While observing the image from the optical camera 200, the operator brings the radiation detection element 20 of the probe 10 close to the tissue (e.g., a lymph node) S and measures the radiation to detect whether a drug containing a radionuclide has accumulated therein. Whether a specific radiation has been measured can be confirmed by observing the luminous state, flicker, and hue of the light-emitting part 30 in the field of view of the optical camera 200. Therefore, the operator can obtain the radiation measurement results in real time through the optical camera 200.

[0052] As described above, the radiation detector 1 of Embodiment 1 uses the radiation detection element 20 of the probe 10 to measure the radiation emitted by radionuclides absorbed by the body tissue (affected area), and appropriately causes the light-emitting part 30 located at the tip of the probe 10 to emit light. The operator can easily identify the light-emitting part 30 at the tip of the probe 10 emitting light without changing their line of sight from the probe 10. In other words, in addition to the display screen showing the image near the tip of the probe 10 (around the affected area), the operator can more accurately identify the location of the body tissue without having to look at other display screens, such as those showing radiation energy values.

[0053] (Modified Example)

[0054] In Embodiment 1 described above, a light-emitting part 30 is used to notify the operator that radiation has been measured. However, the notification means is not limited to the light-emitting part 30. For example, a loudspeaker that emits a detection tone can be used instead of the light-emitting part 30. When using a loudspeaker, its placement can be inside the probe 10 rather than on its outer surface. However, from the operator's point of view, it is preferable to place it near the front end of the probe 10. The detection tone can be emitted every time radiation is measured. Furthermore, the magnitude of the count rate can also be notified to the operator by changing aspects of the detection tone (frequency, pitch, etc.) according to the count rate.

[0055] Radiation detection element 20 may use a scintillation detection element. For example... Figure 6 , Figure 7 As shown, the radiation detector 1A includes a radiation detection element 20, which is a scintillation detection element, and a light-receiving section (enhancing section) 40. The light-receiving section 40 is connected to the radiation detection element 20 via an optical fiber 22. The optical fiber 22 guides the scintillation light emitted by the radiation detection element 20 to the light-receiving section 40. The light-receiving section 40 enhances the scintillation light delivered from the radiation detection element 20 via the optical fiber 22 and outputs it as an electrical signal to the counting section 66. The light-receiving section 40 is, for example, a silicon photomultiplier tube. The light-receiving section 40 requires a relatively high voltage, for example, about 70 volts. Therefore, for safety reasons, it is preferable to place the light-receiving section 40 inside the operating section 80, rather than inside the probe 10 to be inserted into the body.

[0056] Furthermore, in Embodiment 1 and its variations described above, the light-emitting portion 30 includes a light-emitting element 32 inside. However, its arrangement is not limited to this; the light-emitting portion 30 and the light-emitting element 32 can also be arranged separately (see below). Figure 8 In this case, the light-emitting part 30 and the light-emitting element 32 can be connected via an optical fiber. This allows the probe 10 to be further miniaturized.

[0057] In Embodiment 1 described above, the control unit 50 is built into the operation unit 80 of the radiation detector 1. However, the control unit 50 may also be located in a housing other than the housing containing the probe 10 or the operation unit 80 of the radiation detector 1. Furthermore, in this case, the control unit 50 may be, for example... Figure 3 As illustrated, it is installed in the aforementioned other housings in a state where it is electrically connected to I / O 62, setting unit 64, counting unit 66, radiation detection element 20, light-emitting element 32 and input unit 70 via bus 56.

[0058] [Implementation Method 2]

[0059] The following description pertains to Embodiment 2, with reference to the accompanying drawings. Furthermore, components having the same structure or function as those in Embodiment 1 are labeled with the same reference numerals, and their descriptions are omitted. Figure 8 This is a schematic diagram of the radiation detector as an embodiment 2 of surgical grasping forceps. The grasping forceps are surgical instruments used to grip and grasp internal tissues with two scissor-shaped clamping parts. The radiation detector 2 has a pair of radiation detection elements built into the two clamping parts (probes), and measures the radiation energy of the object by clamping the object between the radiation detection elements.

[0060] (Structure of Radiation Detector 2)

[0061] like Figure 8 As shown, the radiation detector 2 has a main body 110, an operation unit 105 disposed at one end of the main body 110, and a clamping unit 140 disposed at the other end of the main body 110. The main body 110 houses a first light-receiving element (enhancing unit) 120, a second light-receiving element (enhancing unit) 121, a light-emitting element 132, a simultaneous counting circuit 136, and a control unit 50. The first light-receiving element 120 and the second light-receiving element 121 are, for example, silicon photomultiplier tubes, requiring a relatively high voltage of approximately 70 volts. Therefore, for safety reasons, it is preferable to position the first light-receiving element 120 and the second light-receiving element 121 as far away from the clamping unit 140 as possible, and closer to the operation unit 105. Furthermore, the radiation detector 2 may include an input unit and a setting unit (not shown in the figures). For example, the input unit and setting unit in the radiation detector 2 have the same functions as the input unit 70 and setting unit 64 described in Embodiment 1.

[0062] The operating section 105 is a mechanism for opening and closing the clamping section 140. For example, it has a first operating section 103 for placing fingers other than the thumb, and a second operating section 104 for placing the thumb. The first operating section 103 and the second operating section 104 can be opened and closed with one hand.

[0063] The clamping portion 140 has a first clamping portion 142 and a second clamping portion 143. The first clamping portion 142 and the second clamping portion 143 respectively correspond to the probe 10 in Embodiment 1. A first scintillator (radiation detection element) 144 is disposed in the first clamping portion 142. A second scintillator (radiation detection element) 145 is disposed in the second clamping portion 143. The first scintillator 144 and the first light-receiving element 120 are optically connected through a first optical fiber 122. The second scintillator 145 and the second light-receiving element 121 are optically connected through a second optical fiber 123.

[0064] The first clamping part 142 and the second clamping part 143 swing in opposite directions around the opening and closing shaft 160 located at the other end of the main body 110 to perform opening and closing actions. The opening and closing actions of the first operating part 103 and the second operating part 104 are transmitted through a transmission mechanism inside the main body 110 (not shown in the figure) and are converted into the opening and closing actions of the first clamping part 142 and the second clamping part 143.

[0065] A light-emitting portion 130 is provided near the opening / closing axis 160 of the main body 110. The light-emitting portion 130 receives light from the light-emitting element 132 and emits light. The light-emitting portion 130 and the light-emitting element 132 are separately configured, and the light-emitting portion 130 and the light-emitting element 132 are optically connected via an optical fiber 134. The light-emitting portion 130 is constructed of, for example, a light-diffusing member. In this embodiment, in order to provide the light-emitting portion 130 near the opening / closing axis 160, it is preferable to provide it as close as possible to the clamping portion 140 of the main body 110. Furthermore, the light-emitting portion 130 is preferably provided on at least one of the first clamping portion 142 and the second clamping portion 143 of the clamping portion 140.

[0066] (The operation of radiation detector 2)

[0067] The operator clamps the affected tissue between the first clamping part 142 and the second clamping part 143 of the radiation detector 2 to measure radiation. The operator administers F-18-labeled FDG (fluorodeoxyglucose) to the patient beforehand. F-18-labeled FDG is easily absorbed and accumulates in cancerous tissue. F-18 emits two annihilation gamma rays due to the annihilation of positrons and electrons. Since both annihilation gamma rays have the same energy of 511 keV and occur simultaneously at 180-degree angles, they are simultaneously detected by the opposing first scintillator 144 and second scintillator 145. Radiation not simultaneously detected is not annihilation gamma rays, or even if it is, it originates outside the field of view and can be excluded as background radiation. Therefore, the radiation detector 2 can be constructed with a simple structure without considering shielding materials.

[0068] The scintillation light generated by the 511 (KeV) radiation from the first scintillator 144 is transmitted to the first light-receiving element 120 via the first optical fiber 122. The first light-receiving element 120 converts the scintillation light into an electrical signal and outputs it to the simultaneous counting circuit 136. The scintillation light generated by the 511 (KeV) radiation from the second scintillator 145 is transmitted to the second light-receiving element 121 via the second optical fiber 123. The second light-receiving element 121 converts the scintillation light into an electrical signal and outputs it to the simultaneous counting circuit 136. When the electrical signals from the first scintillator 144 and the second scintillator 145 are both generated by 511 (KeV) radiation and are simultaneously measured, the simultaneous counting circuit 136 determines that annihilation gamma rays have been detected and outputs the detection signal to the control unit 50. Here, "simultaneous" refers to a time difference of arrival of less than a few nanoseconds or less than tens of nanoseconds. When the detection signal from the simultaneous counting circuit 136 meets the predetermined conditions, the control unit 50 causes the light-emitting unit 130 to emit light.

[0069] The control method for the control unit 50 to make the light-emitting unit 130 emit light will be explained. First, the control method is to make it emit light whenever annihilation gamma rays are detected. For example... Figure 9 (a) Fourth flowchart example and Figure 9As shown in (b), the simultaneous counting circuit 136 receives electrical signals (detection signals) of radiation measured by the first scintillator 144 and the second scintillator 145 via the first light-receiving element 120 and the second light-receiving element 121 respectively (step S160). Next, the simultaneous counting circuit 136 determines whether it has simultaneously received detection signals from the first scintillator 144 and the second scintillator 145 (step S161). In step S161, if two detection signals are received simultaneously (step S161: Yes), it can be determined that annihilated gamma rays have been measured, and the simultaneous counting circuit 136 outputs a signal indicating that radiation has been measured to the control unit 50. If two detection signals are not received simultaneously (step S161: No), the processing performed by the control unit 50 returns to the previous stage of step S161. Then, when the control unit 50 receives a signal indicating that radiation has been measured from the simultaneous counting circuit 136, it causes the light-emitting element 132 to emit light (step S162). The light emitted by the light-emitting element 132 causes the light-emitting part 130 to emit light via the optical fiber 134.

[0070] Alternatively, it could be a control method that causes luminescence when the count rate of annihilated gamma rays exceeds a predetermined threshold. The count rate is the same as described in Embodiment 1. Figure 9 (c) and the fifth flowchart example and Figure 9 As shown in (d), the simultaneous counting circuit 136 receives the radiation detection signals measured by the first scintillator 144 and the second scintillator 145 (step S170). Next, the simultaneous counting circuit 136 determines whether the two detection signals are received simultaneously (step S171). In step S171, when the two detection signals are received simultaneously (step S171: Yes), the simultaneous counting circuit 136 outputs a signal indicating that radiation has been measured to the control unit 50. Next, the control unit 50 determines whether the reception frequency (count rate) of the signal indicating that radiation has been measured from the simultaneous counting circuit 136 is above a threshold (step S172). In step S172, when the count rate is above the threshold (step S172: Yes), the control unit 50 causes the light-emitting element 132 to emit light (step S173). Furthermore, when the two detection signals are not received simultaneously (step S171: No), or when the count rate is not above the threshold (step S172: No), the processing of the control unit 50 returns to the previous stage of step S171. The light emitted by the light-emitting element 132 is transmitted through the optical fiber 134 to make the light-emitting part 130 emit light.

[0071] Furthermore, the control unit 50 can control the change of the luminescent sample according to the count rate of annihilated gamma rays. For example... Figure 9 (e) Sixth flowchart example and Figure 9As shown in (f), the simultaneous counting circuit 136 receives the radiation detection signals measured by the first scintillator 144 and the second scintillator 145 (step S180). Next, the simultaneous counting circuit 136 determines whether the two detection signals are received simultaneously (step S181). In step S181, when the two detection signals are received simultaneously (step S181: Yes), the simultaneous counting circuit 136 outputs a signal indicating that radiation has been measured to the control unit 50. Next, the control unit 50 determines whether the reception frequency (count rate) of the signal indicating that radiation has been measured from the simultaneous counting circuit 136 is above a threshold (step S182). In step S182, when the count rate is above the threshold (step S182: Yes), the control unit 50 causes the light-emitting element 132 to emit light of a specific color corresponding to the count rate (step S183). Furthermore, when the two detection signals are not received simultaneously (step S181: No), or when the count rate is not above a threshold (step S182: No), the processing of the control unit 50 returns to the previous stage of step S181. For example, the control unit 50 does not emit light when the count rate is below a first threshold, emits blue light when the count rate is above the first threshold and below a second threshold, and emits red light when the count rate is above the second threshold. Alternatively, the control unit 50 can control the frequency of light emission, such as flashing, according to the count rate. The method for setting the threshold is the same as described in Embodiment 1.

[0072] (Example of using radiation detector 2)

[0073] like Figure 10 As shown, the radiation detector 2 can be used in endoscopic surgery and robot-assisted surgery. While observing the image from the optical camera 200, the operator uses the two scintillators 144 and 145 of the clamping part 140 to hold the object and measure its radiation energy to detect whether F-18 labeled FDG has accumulated in tissue (e.g., lymph nodes) S. Because the presence or absence of annihilated gamma rays can be confirmed by observing the emission, scintillation, and hue of the luminescent part 130 in the field of view of the optical camera 200, the operator can obtain the radiation measurement results in real time through the optical camera 200.

[0074] As described above, by checking whether the light-emitting part 130 emits light, the operator can confirm whether F-18 labeled FDG has accumulated in the tissue held by the first clamping part 142 and the second clamping part 143.

[0075] Since the radiation detector 2 of Embodiment 2 only detects annihilation gamma rays emitted by the tissue held by the clamping part 140, it is not affected by other radiation. Then, the operator can easily identify the light-emitting part 130, located near or on the clamping part 140, emitting light without changing their line of sight. In other words, the operator can more accurately identify the presence of radioactive nuclides in the tissue held by the clamping part 140 without needing to look at other displays.

[0076] [Implementation Method 3]

[0077] Next, Embodiment 3 will be described with reference to the accompanying drawings. Furthermore, components having the same structure or function as those in Embodiment 2 will be labeled with the same reference numerals and their descriptions will be omitted. Figure 11 This is a schematic diagram of the structure of a radiation detector configured as a surgical grasping forceps in Embodiment 3. Figure 12 This is a diagram showing the relationship between the opening angle of the clamping part 140 and the size of the object being measured.

[0078] (Structure of radiation detector 3)

[0079] The structure of radiation detector 3 is almost identical to that of radiation detector 2. Specifically, radiation detector 3 has a main body 110, an operation unit 105, and a clamping unit 140. In the main body 110, a light-emitting unit 130 is arranged near the opening / closing shaft 160, and a light-emitting element 132 (not shown) is arranged inside the light-emitting unit 130. Furthermore, the main body 110 houses a first light-receiving element 120, a second light-receiving element 121, a simultaneous counting circuit 136, a correction unit 137, an encoder 138, and a control unit 50. Although not shown in the figures, radiation detector 3 may also include an input unit and a setting unit.

[0080] Radiation detector 3 differs from radiation detector 2 in that it includes a corrector 137 and an encoder 138. The encoder 138 is an angle encoder that outputs the opening angle θ1 of the operating unit 105, which is the angle θ1 formed by the first operating unit 103 and the second operating unit 104. The opening angle of the operating unit 105 is linked to the opening angle θ2 of the clamping unit 140 (first clamping unit 142 and second clamping unit 143). Therefore, by detecting the opening angle θ1 of the operating unit 105 with the encoder 138, the opening angle θ2 of the clamping unit 140 can be obtained. Furthermore, when the opening and closing motion of the operating unit 105 is converted into linear motion of the shaft within the main body 110, and transmitted as the opening and closing motion of the clamping unit 140, a linear encoder can also be used as the encoder 138. In this case, the opening angle θ2 of the clamping unit 140 can be calculated from the amount of shaft movement output by the linear encoder. Alternatively, the distance between the first clamping part 142 and the second clamping part 143 can be calculated to replace the opening angle θ2 of the clamping part 140.

[0081] The correction unit 137 can correct the detection efficiency (detection sensitivity) of the simultaneous counting of annihilated gamma rays by the first scintillator 144 and the second scintillator 145 based on the opening angle of the clamping unit 140 or the distance between the first clamping unit 142 and the second clamping unit 143. The configuration relationship of the two scintillators 144, 145 varies depending on the opening angle of the clamping unit 140. The correction unit 137 can correct the detection efficiency of the simultaneous counting based on the positional relationship between the two scintillators 144, 145, thereby ensuring that the measured radiation energy does not change even when the opening angle of the clamping unit 140 changes.

[0082] like Figure 12 As shown in (a), when the opening angle of the operating part 105 is at its maximum, the opening angle of the clamping part 140 also reaches its maximum. As the opening angle of the operating part 105 decreases, the opening angle of the clamping part 140 also decreases. For example, when detecting annihilated gamma rays by clamping a lymph node S with the clamping part 140, if the lymph node S is large, such as... Figure 12 As shown in (b), the opening angle of the clamping part 140 increases; if the lymph node S is small, such as Figure 12 As shown in (c), the opening angle of the clamping part 140 becomes smaller. Thus, if the clamping part 140 just clamps the lymph node S, the size of the lymph node S can be measured based on the opening angle of the clamping part 140 or the distance between the first clamping part 142 and the second clamping part 143 while detecting the annihilation of gamma rays.

[0083] For example, assuming lymph node S is a sphere, its diameter and volume (ml) can be determined based on the opening angle of clamping part 140 or the distance between the first clamping part 142 and the second clamping part 143. On the other hand, the simultaneous count values ​​(cps) measured by the two scintillators 144 and 145 can be corrected by correction part 137 and converted into the radiation energy (becquerels) of lymph node S. Based on these results, the radiation energy density (becquerels / ml) of lymph node S can be calculated. Since the radiation energy density of lymph node S is proportional to the accumulation density of radionuclides, it can be used to estimate the number of cancer cells in lymph node S.

[0084] As described above, the opening angle of the clamping portion 140 can be calculated using the encoder 138. Then, by correcting the detection efficiency of the two scintillators 144 and 145 provided on the clamping portion 140 based on the opening angle of the clamping portion 140, a more accurate calculation of the radiated energy of the object being measured can be obtained. Furthermore, the size of the object being measured can be determined based on the opening angle of the clamping portion 140. Finally, the radiated energy density of the object being measured can be calculated based on its radiated energy and size.

[0085] Next, one example of the method of using the radiation detector 3 will be described. The control unit 50 can control the start and / or end of the operation of the aforementioned radiation detector 3 based on changes in the opening angle of the clamping part 140 and changes in the distance between the first clamping part 142 and the second clamping part 143. For example, radiation measurement can begin when the opening angle of the initially closed clamping part 140 (i.e., the opening angle of the operating part 105) reaches its maximum. In other words, the control unit 50 can begin radiation measurement when the opening angle of the clamping part 140 reaches its maximum angle from a state that is not at its maximum angle.

[0086] Alternatively, the control unit 50 can terminate the radiation measurement when predetermined conditions are met. For example, the control unit 50 can terminate the measurement at a predetermined time after the measurement begins. Alternatively, the measurement can terminate when the opening angle of the clamping part 140 changes again after the size of the lymph node has changed. This is because the clamping part is released only after the lymph node measurement is completed. Alternatively, the measurement can terminate when the opening angle of the clamping part 140 reaches its minimum (closed) state. This is because the measurement operation has already ended at this point. Furthermore, even after the measurement has terminated, it can be restarted by maximizing the opening angle of the clamping part 140 again.

[0087] As described above, since the radiation detector 3 can autonomously start and end radiation measurements based on specific conditions, the operator no longer needs to operate the measurement start / end button, thus enabling the surgery to proceed smoothly.

[0088] Next, regarding an example of controlling the start and end of radiation measurement by radiation detector 3, refer to... Figure 13 Please provide an explanation. For example... Figure 13 As shown, firstly, the control unit 50 uses the encoder 138 to measure the opening angle of the clamping part 140 (step S201). Next, the control unit 50 determines whether the opening angle of the clamping part 140 is the maximum angle (step S202). When the opening angle of the clamping part 140 is the maximum angle (step S202: Yes), the control unit 50 starts measuring radiation (step S203). If the opening angle of the clamping part 140 is not the maximum angle (step S202: No), the control flow returns to step S201. Next, in step S204, the control unit 50 continues to measure the opening angle of the clamping part 140 after starting to measure radiation. Then, the control unit 50 corrects the detection efficiency of the two scintillators 144 and 145 based on the measured opening angle of the clamping part 140 (step S205) and calculates the radiation energy value (step S207). Furthermore, the control unit 50 calculates the diameter of the object being measured in parallel with steps S205 and S207 (step S206). Next, the control unit 50 determines whether the termination condition for the radiation measurement is met (step S209). If the termination condition is not met in step S209 (step S209: No), the control flow returns to step S204. In step S209, if the termination condition is met (step S209: Yes), the control unit 50 records the measured maximum radiation energy value and the diameter of the object being measured (step S210), and ends the radiation measurement. Afterwards, it can return to step S201 again.

[0089] The termination condition for step S209, as described above, can be appropriately set as follows: when a predetermined time has elapsed since the start of the measurement; when the opening angle of the clamping part 140 changes again after a change in the opening angle; or when the opening angle of the clamping part 140 reaches its minimum, etc. Furthermore, in the aforementioned embodiments 2 and 3, although F-18-labeled FDG is exemplified as the agent containing a radionuclide, the agent is not limited to this. Additionally, in embodiments 1 to 3, although lymph nodes are exemplified as the in vivo tissue used to detect whether an agent containing a radionuclide has accumulated, the tissue is not limited to this.

[0090] [Implementation Method 4]

[0091] (Flasher shape)

[0092] Next, a radiation detector configured as a surgical grasping forceps in Embodiment 4 of the present invention will be described with reference to the accompanying drawings. The structure of the radiation detector in Embodiment 4 is substantially the same as that of the radiation detector 3 in Embodiment 3; the differences are described below. Furthermore, elements having the same configuration as those described in the aforementioned embodiments are indicated by the same reference numerals, and their descriptions and illustrations are omitted.

[0093] The radiation detector of embodiment 4 can be inserted into the body, for example, through a puncture cannula. A puncture cannula is a medical device used for intrathoracic drainage, etc. Using a puncture cannula provides a less invasive treatment method. However, the diameter of the puncture cannula is, for example, 5 mm to a few millimeters, which is not large. Therefore, from the viewpoint of radiation detection efficiency, the group of scintillators 144, 145 preferably has a shape that can be housed inside an existing puncture cannula, and a shape with the largest possible cross-sectional area perpendicular to the insertion direction. Since the cross-section of the puncture cannula is circular, the cross-section of the group of scintillators 144, 145 is also preferably circular to maximize the cross-sectional area. With this configuration, the volume of the scintillator capable of detecting radiation can be increased, and the radiation detection efficiency can be improved.

[0094] Figure 14 This is a cross-sectional view of the first scintillator 144 and the second scintillator 145, which are respectively built into the first clamping part 142 and the second clamping part 143 of the radiation detector in Embodiment 4, in a direction perpendicular to the long axis. Figure 14 As shown, the cross-sectional shapes of the first scintillator 144 and the second scintillator 145 are semi-circular, and they are arranged in such a way that the cross-sections of the two scintillators 144 and 145 facing each other form a circle.

[0095] The clamping part 140 of the radiation detector in Embodiment 4 is also configured such that the first clamping part 142 and the second clamping part 143 are semicircular, and the two are closed to form a circle.

[0096] In this case, the dimensions of the scintillators 144 and 145, and the overall size (diameter) of the radiation detector in Embodiment 4, are set to a size that allows insertion into the body through an readily available puncture cannula. That is, the radiation detector with the scintillators 144 and 145 built-in is set to a size that allows it to pass through the puncture cannula. With the above structure, a radiation detector capable of low-invasive diagnosis and treatment using readily available puncture cannulas can be provided.

[0097] [Implementation Method 5]

[0098] (Preset counting method)

[0099] Next, the radiation counting method of the radiation detector according to Embodiment 5 of the present invention will be described with reference to the accompanying drawings. The structure of the radiation detector of Embodiment 5, which is configured as a surgical grasping forceps, is basically the same as that of the radiation detector 3 of Embodiment 3. The differences are described below. In addition, elements having the same configuration as those described in the foregoing embodiments are indicated by the same reference numerals, and their descriptions and illustrations are omitted.

[0100] When a user (operator) uses a radiation detector to measure radiation energy in the affected area during surgery, there are sometimes many objects to be measured. For example, when measuring cancerous lymph nodes, it is still necessary to clamp a large number of lymph nodes one by one with the clamping part 140. In this case, a preset counting method can be used for measurement. Using the preset counting method can shorten the measurement time when the radiation energy in the affected area is high. The preset counting method is very effective when measuring a large number of lymph nodes and can control the increase in surgical time caused by radiation measurement during surgery.

[0101] The preset count is performed as follows. Figure 15 This is a flowchart of the measurement method performed by the control unit 50 of the radiation detector in Embodiment 5. Figure 15 As shown, after the measurement begins, in step S300, the control unit 50 adds up the total value. The count value is the number of radiation measurements. Next, in step S301, the control unit 50 determines whether the total count value is above a preset set value. If it is determined in step S301 that the total value is above the set value (step S301: Yes), the process proceeds to step S303. In step S303, the control unit 50 notifies the user that the count value is above the reference value and ends the measurement. Here, "the control unit 50 notifies the user that the count value is above the reference value" means that the control unit 50 causes the light-emitting unit 130 to emit light in a specific manner.

[0102] On the other hand, if it is determined in step S301 that the summation value is not above the set value (step S301: No), the process proceeds to step S302. In step S302, the control unit 50 determines whether the predetermined measurement time has elapsed. If it is determined in step S302 that the predetermined measurement time has not elapsed (step S302: No), the process returns to step S300. On the other hand, if it is determined in step S302 that the predetermined measurement time has elapsed (step S302: Yes), the process proceeds to step S304. In step S304, the control unit 50 notifies the user that the count value is less than the reference value and ends the measurement.

[0103] The so-called baseline value is a benchmark value set based on the user's preset index of the severity of the affected area. In other words, the control unit 50 notifies the comparison result between the radiation measurement value and the index of the severity of the affected area.

[0104] Specifically, the baseline value is, for example, a count value representing the likelihood of cancer metastasizing from the affected area. The inventors discovered a correlation between the radiation energy in lymph nodes and the likelihood of metastasis; that is, if the radiation energy of a lymph node is above a first value, the likelihood of metastasis is high. Specifically, the inventors found that if the radiation energy of a lymph node is 10,000 (Bq) or higher, the likelihood of metastasis is high. Users can convert this radiation energy into a sum of counts measured over a predetermined time using predetermined scintillators 144 and 145 of a radiation detector, and set this as the baseline value.

[0105] Alternatively, the baseline value can be set as a count value indicating a low probability of cancer metastasis. The inventors discovered that if the radiation energy in a lymph node is below the second value, the probability of metastasis is low. Specifically, the inventors discovered that if the radiation energy of a lymph node is below 600 (Bq), the probability of metastasis is low. Users can convert this radiation energy into a total count over a predetermined time period and set it as the baseline value.

[0106] For example, while also considering the size and shape of the scintillators 144 and 145 and the structure of the clamping part 140, when administering 185 MBq of FDG to a cancer patient and measuring the accumulated radiation energy 6 hours after administration, the radiation energy of lymph nodes considered to have a low probability of metastasis (600 Bq per lymph node) is generally expected to be measured 100 times within 30 seconds. On the other hand, the radiation energy of lymph nodes considered to have a high probability of metastasis (10,000 Bq per lymph node) is generally expected to be measured 100 times within 1.8 seconds.

[0107] For example, the baseline value for radiation energy is set at 600 Bq, the measurement value is set at 100 counts, and the predetermined measurement time is 30 seconds. If the measured value does not reach the set value after 30 seconds, the radiation energy of the lymph node is judged to be below 600 Bq, and the possibility of metastasis is low. Conversely, if the measured value reaches or exceeds the set value within 1.8 seconds, the possibility of metastasis of the lymph node is judged to be high.

[0108] Because this method of measuring radiation energy allows for the notification of lymph nodes with high radiation energy and the termination of the measurement within a short time, it can shorten the measurement time when measuring a large number of lymph nodes. Furthermore, by sending a notification promptly after the measurement is completed, or by keeping the time between the end of the measurement and the sending of the notification relatively constant, the user can roughly determine the radiation energy based on the time elapsed between the start of the measurement and the sending of the notification. Additionally, the reference values ​​for the measurement time and the sum of the counts can be appropriately set based on the expected amount of radionuclides that will accumulate in the affected area and the detection efficiency of the scintillators 144 and 145 of the radiation detector.

[0109] The control unit 50 preferably alternates between notifying the user when a reference value is reached or exceeded, and notifying the user when the value is less than the reference value. For example, by maintaining the light on when the value is less than the reference value, and then switching the light from on to flashing when the value is reached or exceeded, the user can be notified that the value has been reached or exceeded. The flashing time can be fixed. If the light remains on after the measurement is completed, it means the value is less than the reference value. If the light quickly switches to flashing, it means the radiated energy is higher. Furthermore, the notification method can be sound or a combination of sound and light.

[0110] (Modified Example)

[0111] Alternatively, the following measurement methods can also be used. Figure 16 This is a flowchart of the measurement method of a variation of embodiment 5. Figure 16 The flowchart shown is a flowchart for calculating the radiant energy accumulated in lymph nodes and informing the user. For example... Figure 16 As shown, after the measurement begins, in step S310, the control unit 50 first sums up the counts. Then, in step S311, the control unit 50 determines whether the sum of the counts is above a preset value.

[0112] If it is determined in step S311 that the summation value is above the set value (step S311: Yes), proceed to step S314. In step S314, the control unit 50 stops the timer. Next, in step S315, the controller 50 calculates the radiation energy of the lymph node based on the count value. The radiation energy of the lymph node is obtained by converting the count value based on the shape of the scintillators 144 and 145, the opening angle of the radiation detector, the size of the affected area, etc. Next, in step S316, the control unit 50 notifies the user of the radiation energy and ends the measurement.

[0113] On the other hand, if it is determined in step S311 that the summation value is not above the set value (step S311: No), the process proceeds to step S312. In step S312, the control unit 50 determines whether the predetermined measurement time has elapsed. If it is determined in step S312 that the predetermined measurement time has not elapsed (step S312: No), the process returns to step S310. On the other hand, if it is determined in step S312 that the predetermined measurement time has elapsed (step S312: Yes), the process proceeds to step S313. In step S313, the control unit 50 notifies the user of the result that is less than the reference value and ends the measurement.

[0114] By measuring radiation energy in this way, lymph nodes with high radiation energy can be notified and the measurement can be terminated in a short time, thus shortening the measurement time when measuring a large number of lymph nodes.

[0115] The method of notifying the user can be the same as in the previous example. Additionally, the flashing frequency can be changed. For example, the flashing frequency can be increased when the lymph node radiation energy is high, and decreased when the radiation energy is low.

[0116] Furthermore, there are many possible methods for instructing the start of radiant energy measurement. For example, measurement can begin with the movement of the radiation detector. For instance, a sensor capable of detecting the degree of opening of the clamping part 140 of the radiation detector can be installed, and measurement can begin when the clamping part 140 changes from a fully closed state to an open state. Alternatively, a contact sensor can be provided at the front end of the clamping part 140, etc., and measurement can begin when contact between the contact sensor and the lymph node (the object of measurement) is detected. Furthermore, a voice recognition system capable of detecting the user's voice can be installed, and measurement can begin when a specific voice of the user (e.g., the voice of "start") is recognized.

[0117] Furthermore, for example, by displaying the opening degree of the clamping part 140 on the clamping part 140, the user can fully grasp the timing of starting the measurement. When displaying the opening degree of the clamping part 140, it is preferable to arrange the display of the opening degree in a position that the user can see during normal operation. This is so that the user does not need to change the orientation of the radiation detector when confirming the opening degree.

[0118] As mentioned above, by autonomously initiating measurements under specific conditions and operating the switch relative to the user, the burden on the user can be reduced, and measurements can be initiated in a shorter time.

[0119] [Summarize]

[0120] The radiation detector of aspect 1 of the present invention comprises: a probe having a built-in radiation detection element and being insertable into a body; a notification unit disposed on the probe; and a control unit that activates the notification unit based on the radiation detection result measured by the radiation detection element.

[0121] Using the above method, the operator can more accurately identify the location of tissues within the body that have absorbed radioactive nuclides. Specifically, the operator (practitioner) can confirm the location of the radiation source (affected area) where radioactive nuclides have accumulated by manipulating the probe and receiving information from the reporting unit. Furthermore, since the reporting unit is located on the probe, which has a built-in radiation detection element, the operator can confirm the location of the affected area without changing their facial orientation or line of sight.

[0122] Alternatively, the present invention may also provide a radiation detection method having, for example, the following steps: detecting radiation based on a radiation detection element provided by a probe inserted into the body; and activating a notification unit further provided by the probe based on the radiation detection result.

[0123] In the radiation detector of aspect 2 of the present invention, a setting unit may be further provided, which sets a threshold for the control unit corresponding to the detection result used to determine whether to activate the notification unit.

[0124] Using the above method, the measured radiation energy will vary depending on the type of radionuclide used, the amount administered, or the amount of radionuclide accumulated. By adjusting the threshold for activating the reporting unit according to these conditions, various clinical situations can be addressed.

[0125] In the radiation detector of aspect 3 of the present invention, the aforementioned notification part may be a light-emitting part provided on the outer surface of the aforementioned probe.

[0126] By using the above solution, the location of the affected area can be visually identified by using the light-emitting part as the reporting part.

[0127] In the radiation detector of aspect 4 of the present invention, the aforementioned control unit can control the aforementioned light-emitting unit to change at least one of the following: light emission intensity, light emission mode, light emission color, and light emission time, based on the radiation count or count rate obtained as the aforementioned detection result.

[0128] Using the above method, the operator can visually determine the radiation energy based on the luminescence pattern of the luminescent part, thus easily identifying the accumulation location and diffusion range of radionuclides, that is, the location and diffusion range of the affected area.

[0129] In the radiation detector of aspect 5 of the present invention, the aforementioned light-emitting part and the light-emitting element that makes the aforementioned light-emitting part emit light can be separately configured, and the aforementioned light-emitting element and the aforementioned light-emitting part can be optically connected via optical fiber.

[0130] By using the above method, the probe can be miniaturized by placing the light-emitting element in a position separate from the probe.

[0131] In the radiation detector of aspect 6 of the present invention, the aforementioned light-emitting portion may be continuously disposed around the outer peripheral surface of the aforementioned probe, or may protrude at least partially from the outer surface of the aforementioned probe, or may be disposed at multiple positions on the outer surface of the aforementioned probe.

[0132] With the above solution, the light-emitting part can emit light from a wide three-dimensional angle, or the light-emitting part can emit light from multiple positions. Therefore, even if the orientation and position of the probe are changed, the operator can easily know whether there is light emission.

[0133] In the radiation detector of aspect 7 of the present invention, a collimator may be provided, which restricts the incident direction of radiation incident on the aforementioned radiation detection element.

[0134] Using the above method, the collimator can suppress radiation from the surrounding environment from entering the radiation detection element, thus enabling efficient detection of radiation from the affected area and efficient determination of the location of the affected area.

[0135] In the radiation detector of aspect 8 of the present invention, the radiation detection element may be a detection element for a Compton camera.

[0136] Using the above method, the Compton camera can efficiently detect radiation from the affected area without the need for a collimator or shielding, and thus efficiently determine the location of the affected area.

[0137] In the radiation detector of aspect 9 of the present invention, the aforementioned radiation detection element may be a radiation detection element in a simultaneous counting manner.

[0138] Using the above method, when using radioactive nuclides that emit gamma rays due to annihilation, the location of the affected area can be detected efficiently by employing radiation detection elements that use a simultaneous counting method.

[0139] In the radiation detector of aspect 10 of the present invention, the aforementioned probes may be configured as two, and each of the aforementioned probes has the aforementioned radiation detection element built into it.

[0140] By using the above scheme, by setting up two probes and equipping each of them with a radiation detection element, the characteristics of simultaneous radiation counting can be utilized.

[0141] The radiation detector of aspect 11 of the present invention can be configured as a surgical grasping forceps, and each of the two front ends of the grasping forceps can function as a probe having the aforementioned radiation detection element.

[0142] By using the above-described scheme, which is configured as a surgical grasping forceps, the location of the affected area can be easily positioned during surgery.

[0143] The radiation detector of aspect 12 of the present invention is configured as a surgical grasping forceps that can be inserted into the body. The two front ends of the grasping forceps are configured as two probes, each with a built-in radiation detection element. The radiation detector includes: a notification unit disposed in the grasping forceps; and a control unit that activates the notification unit based on the detection result of annihilated gamma rays, wherein the detection result is obtained by simultaneous counting by the radiation detection elements each built into the two probes.

[0144] Using the above method, the operator can more accurately determine whether radioactive nuclides have accumulated in the body tissue by using gripping forceps to grasp the tissue and measuring the radiation emitted by the radioactive nuclides absorbed by the tissue. The operator does not need to look at a specific display screen that shows isotope distribution images or radiation energy values.

[0145] Alternatively, the present invention can also be a radiation detection method using a radiation detector, wherein the radiation detector is configured, for example, as a surgical grasping forceps that can be inserted into the body, and the radiation detection method includes the following steps: detecting annihilation gamma rays by means of radiation detection elements provided by two probes formed by the front ends of the aforementioned grasping forceps inserted into the body in a simultaneous counting manner; and activating a notification unit provided by the aforementioned grasping forceps based on the detection results of the aforementioned annihilation gamma rays.

[0146] In the radiation detector of aspect 13 of the present invention, the aforementioned control unit can adjust the detection sensitivity of simultaneous counting based on the opening angle of the two probes or the distance between the two probes.

[0147] The above method can accurately measure the radiation energy of the affected area.

[0148] In the radiation detector of aspect 14 of the present invention, the aforementioned control unit can measure the size of the object to be measured based on the opening angle of the two probes or the distance between the two probes.

[0149] The above method can detect not only the location of the affected area, but also its size.

[0150] In the radiation detector of aspect 15 of the present invention, the aforementioned control unit can calculate the volume of the object to be measured and the radiation energy per unit volume based on the opening angle of the two probes or the distance between the two probes.

[0151] The above method can not only detect the location of the affected area, but also the density of radioactive nuclides, that is, the degree of dispersion of the affected area.

[0152] In the radiation detector of aspect 16 of the present invention, the aforementioned control unit can control the start and / or end of the operation of the aforementioned radiation detector based on the change in the opening angle of the aforementioned two probes or the change in the distance between the aforementioned two probes.

[0153] With the above method, the operator does not need to operate the radiation detector to start and stop it, thus improving the efficiency of diagnosis or treatment.

[0154] In the radiation detector of aspect 17 of the present invention, the aforementioned notification unit may be a light-emitting unit and may be disposed in at least one of the aforementioned two probes or disposed in the main body of the aforementioned gripping clamp.

[0155] With the above method, the operator can more accurately determine whether radionuclides have accumulated in the body tissue without having to watch the probe of the gripping forceps and another display at the same time.

[0156] In the radiation detector of aspect 18 of the present invention, the cross-sectional shape of the radiation detection element, which is built into each of the two probes, can be semi-circular.

[0157] The above approach can increase the size of the radiation detection element and improve detection efficiency.

[0158] In the radiation detector of aspect 19 of the present invention, the aforementioned reporting unit can report the comparison result between the detection result of the aforementioned annihilated gamma rays and the index of the malignancy of the affected area.

[0159] Using the above method, users can easily determine the severity of the disease by observing the status of the notification.

[0160] In the radiation detector of aspect 20 of the present invention, the aforementioned control unit may be disposed in a housing that is different from the main body of the aforementioned radiation detector.

[0161] By using the above solution, even if the processing capacity of the control unit is large and it is necessary to increase the size of the control unit, the decrease in operability when operating the radiation detector by hand can be suppressed.

[0162] This invention is not limited to the embodiments described above. Various modifications can be made within the scope of the claimed invention. Embodiments obtained by appropriately combining the technical means disclosed in different embodiments are also included within the technical scope of this invention.

[0163] <Explanation of Figure Markers>

[0164] 1, 1A, 2, 3 Radiation Detectors

[0165] 10 probes

[0166] 20 Radiation Detection Elements

[0167] 22,134 fiber optic cables

[0168] 30, 130 Light-emitting section (notification section)

[0169] 32,132 Light-emitting elements

[0170] 40 Light-receiving section (enhancing section)

[0171] 50 Control Department

[0172] 52 processor

[0173] 54 Memory

[0174] 56 bus

[0175] 62 Input / Output Interfaces (I / O)

[0176] 64 Setting Department

[0177] 66 Counting Department

[0178] 70 Input Section

[0179] 80, 105 Operations Department

[0180] 82 cable

[0181] 103 First Operations Department

[0182] 104 Second Operations Department

[0183] 110 Main Body

[0184] 120 First light-receiving element (enhancing section)

[0185] 121 Second light-receiving element (enhancing section)

[0186] 122 First Fiber Optic

[0187] 123 Second Fiber Optic

[0188] 136 Simultaneous Counting Circuit

[0189] 137 Revision Department

[0190] 138 encoder

[0191] 140 Clamping Part (Probe)

[0192] 142 First clamping part

[0193] 143 Second clamping part

[0194] 144 First Scintillator (Radiation Detection Element)

[0195] 145 Second Scintillator (Radiation Detection Element)

[0196] 160 opening and closing shaft

[0197] 200 optical camera

Claims

1. A radiation detector, characterized in that, have: The probe has a built-in radiation detection element and can be inserted into the body; The notification unit is located at the aforementioned probe; and The control unit, based on the radiation detection results obtained by the aforementioned radiation detection element, causes the aforementioned notification unit to operate. The aforementioned radiation detection element is a radiation detection element using a simultaneous counting method. The aforementioned probes are configured in pairs, each containing the aforementioned radiation detection element. The aforementioned control unit adjusts the detection sensitivity of simultaneous counting based on the opening angle of the two probes or the distance between the two probes.

2. The radiation detector according to claim 1, characterized in that, It further includes a setting unit that sets a threshold for the control unit that corresponds to the detection result used to determine whether to activate the notification unit.

3. The radiation detector according to claim 1 or 2, characterized in that, The aforementioned notification part is a light-emitting part located on the outer surface of the aforementioned probe.

4. The radiation detector according to claim 3, characterized in that, The aforementioned control unit controls the aforementioned light-emitting unit to change at least one of the following: light emission intensity, light emission mode, light emission color, and light emission time, based on the radiation count or count rate obtained as the aforementioned detection result.

5. The radiation detector according to claim 3, characterized in that, The aforementioned light-emitting part and the light-emitting element that makes the aforementioned light-emitting part emit light are separately configured, and the aforementioned light-emitting element and the aforementioned light-emitting part are optically connected via optical fiber.

6. The radiation detector according to claim 3, characterized in that, The aforementioned light-emitting part is continuously disposed around the outer peripheral surface of the aforementioned probe, or at least partially protrudes from the outer surface of the aforementioned probe, or is disposed at multiple positions on the outer surface of the aforementioned probe.

7. The radiation detector according to claim 1 or 2, characterized in that, It is equipped with a collimator, which limits the incident direction of radiation incident on the aforementioned radiation detection element.

8. The radiation detector according to claim 1 or 2, characterized in that, The radiation detection element is a detection element used in Compton cameras.

9. The radiation detector according to claim 1, characterized in that, The radiation detector is configured as a surgical gripper, with each of the two front ends of the gripper functioning as a probe equipped with the aforementioned radiation detection element.

10. A radiation detector, wherein, The radiation detector is configured as a surgical grasping forceps that can be inserted into the body. The radiation detector is characterized by... The two front ends of the aforementioned gripper are configured as two probes, each containing a built-in radiation detection element. This radiation detector has the following features: The notification unit is located in the aforementioned gripper; and The control unit activates the aforementioned notification unit based on the detection results of annihilated gamma rays, wherein the detection results are obtained by simultaneous counting by the radiation detection elements each built into the aforementioned two probes. The aforementioned control unit adjusts the detection sensitivity of simultaneous counting based on the opening angle of the two probes or the distance between the two probes.

11. The radiation detector according to claim 10, characterized in that, The aforementioned control unit measures the size of the object being measured based on the opening angle of the two probes or the distance between the two probes.

12. The radiation detector according to claim 10 or 11, characterized in that, The aforementioned control unit calculates the volume of the object being measured based on the opening angle of the two probes or the distance between the two probes, and calculates the radiant energy per unit volume.

13. The radiation detector according to claim 10 or 11, characterized in that, The aforementioned control unit controls the start and / or end of the operation of the aforementioned radiation detector based on the change in the opening angle of the aforementioned two probes or the change in the distance between the aforementioned two probes.

14. The radiation detector according to claim 10 or 11, characterized in that, The aforementioned notification part is a light-emitting part, and is disposed in at least one of the aforementioned two probes or in the main body of the aforementioned gripping clamp.

15. The radiation detector according to claim 10 or 11, characterized in that, The cross-sectional shape of the radiation detection element embedded in each of the two probes is semi-circular.

16. The radiation detector according to claim 10 or 11, characterized in that, The aforementioned notification department reports the comparison results between the detection results of the aforementioned annihilated gamma rays and the indicators of the malignancy of the affected area.

17. The radiation detector according to claim 1, 2, 10 or 11, characterized in that, The aforementioned control unit is housed in a casing that is different from the main body of the aforementioned radiation detector.

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