WO2016174723A1 - 線量率測定装置 - Google Patents
線量率測定装置 Download PDFInfo
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- WO2016174723A1 WO2016174723A1 PCT/JP2015/062763 JP2015062763W WO2016174723A1 WO 2016174723 A1 WO2016174723 A1 WO 2016174723A1 JP 2015062763 W JP2015062763 W JP 2015062763W WO 2016174723 A1 WO2016174723 A1 WO 2016174723A1
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- dose rate
- compensation
- radiation detector
- radiation
- detector
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01T—MEASUREMENT OF NUCLEAR OR X-RADIATION
- G01T1/00—Measuring X-radiation, gamma radiation, corpuscular radiation, or cosmic radiation
- G01T1/02—Dosimeters
- G01T1/023—Scintillation dose-rate meters
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01T—MEASUREMENT OF NUCLEAR OR X-RADIATION
- G01T1/00—Measuring X-radiation, gamma radiation, corpuscular radiation, or cosmic radiation
- G01T1/16—Measuring radiation intensity
- G01T1/167—Measuring radioactive content of objects, e.g. contamination
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01T—MEASUREMENT OF NUCLEAR OR X-RADIATION
- G01T1/00—Measuring X-radiation, gamma radiation, corpuscular radiation, or cosmic radiation
- G01T1/16—Measuring radiation intensity
- G01T1/20—Measuring radiation intensity with scintillation detectors
Definitions
- the present invention relates to a dose rate measuring apparatus, and more particularly to a dose rate measuring apparatus corresponding to a wide range of dose rates.
- a radiation measuring apparatus in which a low range detector and a high range detector are arranged in one detection unit has been proposed.
- a scintillation detector is used for the low range detector, and a semiconductor detector is used for the high range detector.
- the radiation measuring device switches the measurement range according to the dose rate and outputs it.
- the radiation measuring apparatus estimates the energy of incident radiation by measuring the pulse height spectrum of the output pulse of at least one detector in order to suppress this step. By matching this estimated value with the energy characteristics of either one of the upper and lower dose rate regions including the switching point, a large step generated at the switching point of the measurement range is eliminated.
- JP 2002-22839 A JP 2002-168957 A JP 2000-275347 A Japanese Patent Laid-Open No. 11-160437 JP 2000-65937 A JP 2013-195320 A
- the linearity and energy characteristics of the entire range including the low range dose rate and the high range dose rate are improved even though the occurrence of a step at the switching point can be suppressed. It is not a thing. Further, according to the dose rate measuring apparatus according to Patent Document 2, the total number of semiconductor detectors becomes a shadow on the radiation sensor (scintillator) of the scintillation detector and becomes an obstacle to measurement.
- the present invention has been made to solve the above-described problems, and flattens the energy characteristics of both the low range dose rate and the high range dose rate, and as a result, improves the linearity and energy characteristics of the entire range.
- An object of the present invention is to provide a dose rate measuring apparatus that is improved and capable of measuring with high accuracy over a wide range.
- the dose rate measuring apparatus of the present invention has an inorganic crystal scintillator, has a first radiation detector that outputs a detection signal pulse when radiation enters, and a plastic scintillator, and outputs a detection signal pulse when radiation enters.
- a detector frame having a cylindrical portion and containing the first radiation detector and the second radiation detector, and a detection signal pulse output from the first radiation detector
- the low-range calculation unit for calculating the first compensation dose rate of the incident radiation using the energy compensation coefficient and the G (E) function table, and the detection signal pulse output from the second radiation detector
- a high range calculation unit that calculates a second compensation dose rate of incident radiation using the compensation coefficient, a first compensation dose rate calculated by the low range calculation unit, and a second compensation calculated by the high range calculation unit
- a dose rate switching unit for obtaining a dose rate ratio (second compensation dose rate / first compensation dose rate) from the dose rate and selecting a compensation dose rate to be output according to the magnitude of the obtained dose rate ratio;
- the energy characteristics of both the low range dose rate and the high range dose rate are flattened, and as a result, the linearity and energy characteristics of the entire range are improved, wide range and high accuracy. It is possible to provide a dose rate measuring apparatus capable of measuring the above.
- FIG. 2 is a diagram illustrating a configuration of a first radiation detector according to Embodiment 1.
- FIG. It is a figure which shows the structure of the 2nd radiation detector which concerns on Embodiment 1.
- FIG. 3 is a perspective view showing a configuration of a detection unit according to Embodiment 1.
- FIG. 3 is a cross-sectional view illustrating a main part of a detection unit according to the first embodiment. It is a figure which shows the compensation coefficient table of a low range dose rate. It is a figure which shows the compensation coefficient table of a high range dose rate. It is a figure which shows the energy characteristic of a low range dose rate.
- FIG. 10 is a cross-sectional view illustrating a main part of a detection unit according to Embodiment 3. It is a figure which shows the arithmetic processing flow of the dose rate switching part which concerns on Embodiment 4.
- FIG. 10 is a cross-sectional view illustrating a main part of a detection unit according to Embodiment 3. It is a figure which shows the arithmetic processing flow of the dose rate switching part which concerns on Embodiment 4.
- the same or similar components are denoted by the same reference numerals, and the sizes and scales of the corresponding components are independent.
- the configuration of the dose rate measuring apparatus actually includes a plurality of members, but for the sake of simplicity, only the portions necessary for the description are shown and the other portions are omitted.
- FIG. 1 is a diagram showing a configuration of a dose rate measuring apparatus according to the first embodiment.
- the dose rate measuring apparatus 1 includes a detection unit 2 and a measurement unit 3.
- the detection unit 2 includes a first radiation detector 21 that is in charge of a low range dose rate range, and a second radiation detector 22 that is in charge of a high range dose rate range that follows the low range dose rate range. .
- the first radiation detector 21 outputs discrete detection signal pulses (first detection signal pulses) having a peak value proportional to the absorbed radiation energy at a low range dose rate.
- the second radiation detector 22 outputs discrete detection signal pulses (second detection signal pulses) having a peak value proportional to the absorbed radiation energy at a high range dose rate.
- the first radiation detector 21 includes an inorganic crystal scintillator 211, a photomultiplier tube 212, a preamplifier 213, and a detector case 214.
- the columnar inorganic crystal scintillator 211 emits fluorescence upon incidence of radiation.
- the photomultiplier tube 212 is optically joined to the cylindrical inorganic crystal scintillator 211 to capture fluorescence, and converts and multiplies the fluorescence into a current pulse.
- the preamplifier 213 converts the current pulse generated by the photomultiplier tube 212 into a voltage pulse and outputs it.
- the detector case 214 includes three members (inorganic crystal scintillator 211, photomultiplier tube 212, and preamplifier 213) to shield and electrically shield.
- the second radiation detector 22 includes a PL scintillation fiber 221 (or plastic scintillator), a filter 222, an optical coupler 223, an optical fiber 224, a light shielding tube 225, a light guide 226, a photomultiplier tube 227, and a preamplifier. 228 and a detector case 229.
- the PL scintillation fibers 221a, 221b, and 221c emit fluorescence upon incidence of radiation.
- the filters 222a, 222b, and 222c cover the respective PL scintillation fibers to attenuate incident radiation, and make the count rate response in the measurement unit 3 flat as a whole and shield it from light.
- the optical couplers 223a, 223b, and 223c optically join the PL scintillation fibers 221a to 221c to the optical fiber 224, respectively.
- Optical fibers 224a, 224b, and 224c transmit fluorescence emitted from the PL scintillation fibers 221a to 221c to the light guide 226, respectively.
- the light shielding tubes 225a, 225b, and 225c shield the optical coupler 223 and the optical fiber 224 from light.
- the light guide 226 collects the fluorescence transmitted through the optical fiber 224.
- the photomultiplier tube 227 takes in the condensed fluorescence, converts it into a current pulse, and multiplies it.
- the preamplifier 228 converts the current pulse into a voltage pulse and outputs it.
- the detector case 229 includes a light guide 226, a photomultiplier tube 227, and a preamplifier 228 to shield and electrically shield it.
- the filters 222a, 222b, and 222c can be applied to a metal cylinder having a thickness of about 2 mm that is blocked by blocking one end, but may be a cylinder made of a rubber material containing metal powder. The thickness of the filter 222 is determined by radiation attenuation calculation and a type irradiation test.
- FIG. 4 shows the overall structure of the detection unit 2.
- the detector pedestal 23 accommodates a first radiation detector and a second radiation detector.
- the inorganic crystal scintillator 211 of the first radiation detector is arranged in the center of the detection unit 2 with one end face (upper surface 211a) facing directly above.
- a photomultiplier tube 212 is optically joined to the opposite end surface (bottom surface 211 b) of the inorganic crystal scintillator 211.
- the first radiation detector 21 is supported on a detector mount 23.
- the detector pedestal 23 is provided at a position that does not hinder the measurement space of the inorganic crystal scintillator 211 (or the first radiation detector 21).
- the detection portion mantle 24 encloses the first radiation detector 21, the second radiation detector 22, and the detector mount 23 and shields it electrically.
- the detection unit mantle 24 has a waterproof structure that blocks outside air.
- the stand 25 supports the detection unit mantle 24 and the device contained therein, and holds the first radiation detector 21 at a predetermined height.
- only two PL scintillation fibers 221 are depicted, but another PL scintillation fiber 221 is disposed on the back side.
- Each PL scintillation fiber 221 is wound around a cylindrical portion of the detector mount 23. The number of times of winding one fiber-like PL scintillation fiber is 1/3 round here, but the cylindrical portion may be rounded once.
- FIG. 5 is a cross-sectional view showing the main part of the detection unit 2.
- the detector pedestal 23 has a cylindrical portion 23 a that shares the central axis of the detector (the first radiation detector 21 and the second radiation detector 22) outside the first radiation detector 21. .
- the second radiation detector 22 is accommodated in the cylindrical portion 23 a of the detector mount 23.
- the PL scintillation fibers 221a to 221c are disposed in the scintillation fiber arrangement region of the detector base 23 and along the outer periphery of the cylindrical portion 23a.
- the three PL scintillation fibers 221 constituting the second radiation detector 22 do not overlap each other on the outer surface of the cylindrical portion 23a of the detector mount 23 when viewed from directly above the central axis direction of the detector. It is attached diagonally.
- the PL scintillation fibers 221a, 221b, and 221c are arranged so that the total of the areas viewed from directly above and the total of the areas viewed from right
- the tip of the detector mount 23 does not protrude from the fluorescence incident surface 212a of the photomultiplier 212 to the inorganic crystal scintillator 211 side. Further, the PL scintillation fiber 221 is retracted to the back side (the photomultiplier tube 212 side) from the bottom surface 211b of the inorganic crystal scintillator 211.
- the second radiation detector is arranged so as not to be a shadow of the measurement area around the central axis of the first radiation detector and to share the measurement area with the first radiation detector. .
- the PL scintillation fiber 221 can be obtained a suitable directional characteristic by performing an irradiation experiment as a type test, and finely adjusting an oblique attachment angle to determine a standard arrangement.
- the first radiation detector 21 and the second radiation detector 22 share a dose rate range in which the probability that the pulses are close and overlap in each detection signal pulse train does not affect the measurement.
- the shared areas of the first radiation detector 21 and the second radiation detector 22 are partially overlapped to realize a necessary wide range in total.
- the major difference in detection efficiency is that the inorganic radiation scintillator 211 is used for the first radiation detector 21 and the PL scintillation fibers 221a, 221b, and 221c are used as the scintillator for the second radiation detector 22. This is realized by changing the diameter and length for each type of scintillator.
- the second radiation detector 22 is provided with three PL scintillation fibers. However, one may be used if the range sharing property, the direction characteristic, and the necessary flexibility are satisfied. You may make it comprise with four or more.
- the first radiation detector 21 secures a necessary lower limit range and the upper limit range appropriately overlaps with the second radiation detector 22 and also considers the diameter of the scintillator in consideration of availability. The length is decided. The diameters of the PL scintillation fibers 221a to 221c of the second radiation detector 22 overlap so that the upper limit range is within the measurement accuracy and the lower limit range is equal to or less than the upper limit range of the first radiation detector 21. And dimensions are determined.
- the first radiation detector 21 and the second radiation detector 22 are different in detection efficiency (count rate per unit dose rate at the same energy) by, for example, about five digits. If the detection efficiency of the PL scintillation fibers 221a, 221b, and 221c is too low, the resolution of the dose rate near the lower limit range in the high range to be shared deteriorates, and fluctuations suddenly occur when switching from the low range dose rate to the high range dose rate growing. Considering this, the diameter and length of the PL scintillation fiber are determined.
- the total range of the dose rate measuring apparatus is from the lower limit range of the first radiation detector 21 to the upper limit range of the second radiation detector 22.
- the low range dose rate measurement unit 31 receives the first detection signal pulse from the first radiation detector 21 and performs the first detection thereof.
- the first pulse height spectrum of the signal pulse is measured, each peak value of the first pulse height spectrum is weighted by the dose rate per unit count rate (nGy ⁇ h ⁇ 1 / cpm), and each dose rate is assigned to each wave rate.
- a low range compensation dose rate DL (first compensation dose rate) obtained by energy compensation of the previous low range dose rate D1 with an energy compensation coefficient ⁇ 1 (first energy compensation coefficient) is output.
- the high range dose rate measurement unit 32 receives the second detection signal pulse from the second radiation detector 22 and performs the second detection.
- the second pulse height spectrum of the signal pulse is measured, the count values corresponding to the respective peak values of the second pulse height spectrum are integrated over the measurement energy range, and the moving average is obtained over the measurement time to obtain the count rate.
- the rate is multiplied by a conversion constant (nGy ⁇ h ⁇ 1 / cpm) to obtain a high range dose rate D2 (second dose rate) before energy compensation, and the high range dose rate D2 before energy compensation is calculated as an energy compensation coefficient ⁇ 2 ( A high-range compensation dose rate DH (second compensation dose rate) energy-compensated with the second energy compensation coefficient) is output.
- a conversion constant nGy ⁇ h ⁇ 1 / cpm
- each PL scintillation fiber does not have a physical filter
- the dose rate (nGy / h)
- each peak value of the second peak spectrum is multiplied by the count of the peak value, and the measured energy range is integrated.
- the dose rate is calculated based on the integrated peak value per unit time (equivalent to the amount of luminescence per unit time) obtained by moving and averaging the measured value divided by the fixed period time, the dose rate is It will have good energy characteristics.
- each PL scintillation fiber is provided with a physical filter to attenuate radiation incident on the PL scintillation fiber.
- a filter containing all the PL scintillation fibers may be provided.
- the relationship between the amount of emitted light per unit time with respect to the energy of the radiation (photon) has a good energy characteristic at 100 keV or more, and the energy of less than that is energy. It decreases with the decrease and decreases to about 1 ⁇ 2 at 50 keV. Further, the energy characteristic of the light emission amount is less dependent on the diameter at 50 keV or more. Therefore, the PL scintillation fiber has a filter that flattens the energy characteristics as a whole and compensates for the remaining energy characteristics distortion with the energy compensation coefficient ⁇ 2, thereby improving the low-energy characteristics and improving the overall measurement energy. Energy characteristics are obtained.
- the dose rate switching unit 33 switches from the low range compensation dose rate DL to the high range compensation dose rate DH at the rise switching point where the measurement range is set when the dose rate rises, and when the dose rate falls
- the measurement range is switched from the high range compensation dose rate DH to the low range compensation dose rate DL at the set-up switching point.
- hysteresis is provided so that the switching point when rising is higher than the switching point when falling.
- the display operation unit 34 displays the compensation dose rate (high range compensation dose rate DH or low range compensation dose rate DL) output from the dose rate switching unit 33 and sets the measurement unit on the touch panel.
- the low range dose rate measurement unit 31 includes a pulse amplifier 311, an A / D conversion unit 312 (analog-digital conversion unit), a low range calculation unit 313, and a high voltage power supply 314.
- the pulse amplifier 311 receives and amplifies the first detection signal pulse output from the first radiation detector 21 and removes the superimposed high frequency noise.
- the AD converter 312 measures the peak value of the first detection signal pulse amplified by the pulse amplifier 311 and outputs the peak value Vp1.
- the high-voltage power supply 314 supplies a high voltage to operate the first radiation detector 21 (scintillation detector).
- the low range calculator 313 includes a pulse height spectrum generator 3131, a G (E) function memory 3132, a low range dose rate calculator 3133, and an energy compensation coefficient calculator 3134 (first energy compensation coefficient calculator).
- the pulse height spectrum generation unit 3131 receives the peak value Vp1 output from the AD conversion unit 312 and generates and outputs a first pulse height spectrum.
- the G (E) function memory 3132 divides, for example, the measurement energy range of 50 to 3000 keV into 10 to 600 channels (ch), and each ch (i) corresponding to the wave height and the dose rate Gi (nGy ⁇ h ⁇ 1 / cpm). Is stored in the G (E) function table. Using this G (E) function table, the low range dose rate calculation unit 3133 receives the spectrum data from the wave height spectrum generation unit 3131, and the dose of each ch (i) of 10 to 600 ch for a fixed period for each calculation period.
- the energy compensation coefficient calculation unit 3134 receives the spectrum data from the pulse height spectrum generation unit 3131 and integrates the product of the peak value Hi and the count value Ni of each ch (i) of 10 to 600 ch measured at a fixed period.
- the peak value ⁇ Hi ⁇ Ni is divided by the integrated count value ⁇ Ni to obtain the average peak value of the calculation cycle time.
- the moving average peak value h1 is obtained by moving and averaging the average peak value data string for the measurement time that is updated by taking in the average peak value.
- the moving average peak value h1 is correlated with the representative energy of the radiation incident on the first radiation detector 21. Note that the dose rate obtained based on the G (E) function assuming that all the measured energy range counts are representative energies is equal to the dose rate obtained based on the spectrum and the G (E) function as described above. is there.
- FIG. 6 shows a low range compensation coefficient table (first compensation coefficient table) in which the moving average peak value h1 is associated with the energy compensation coefficient ⁇ 1.
- the energy compensation coefficient calculation unit 3134 stores the low range compensation coefficient table ( ⁇ 1), compares the moving average peak value h1 with the low range compensation coefficient table, and determines and outputs the energy compensation coefficient ⁇ 1.
- the low range dose rate calculation unit 3133 outputs a low range compensation dose rate DL obtained by multiplying the low range dose rate D1 before energy compensation by the energy compensation coefficient ⁇ 1.
- the reference energy is, for example, ⁇ ray 662 keV of Cs-137
- the corresponding energy compensation coefficient ⁇ 1 is 1
- the energy compensation coefficient ⁇ 1 of other energy is shown as a ratio to the reference. .
- the high range dose rate measurement unit 32 includes a pulse amplifier 321, an A / D conversion unit 322 (analog-digital conversion unit), and a high range calculation unit 323.
- the pulse amplifier 321 receives and amplifies the second detection signal pulse output from the second radiation detector 22 and removes the superimposed high frequency noise.
- the AD converter 322 measures the peak value of the second detection signal pulse amplified by the pulse amplifier 321 and outputs the peak value Vp2.
- the high voltage power supply 324 supplies a high voltage to operate the second radiation detector 22.
- the high range calculator 323 includes a pulse height spectrum generator 3231, a high range dose rate calculator 3232, and an energy compensation coefficient calculator 3233 (second energy compensation coefficient calculator).
- the pulse height spectrum generation unit 3231 receives the peak value Vp2 output from the AD conversion unit 322, and generates and outputs a second pulse height spectrum.
- the high range dose rate calculation unit 3232 receives the spectrum data from the pulse height spectrum generation unit 3231, and calculates an integrated count value ⁇ Mi obtained by integrating the count values Mi of each ch (i) of 10 to 600 ch measured at a fixed period. To obtain the count rate of the calculation cycle time. Since the moving average count rate is obtained by moving and averaging the data string for the measurement time whose count rate is updated, the moving average count rate is multiplied by a calibration constant to obtain the high-range dose rate D2 before energy compensation.
- the energy compensation coefficient calculation unit 3233 receives the spectrum data from the pulse height spectrum generation unit 3231, and integrates the product of the peak value Hi and the count value Mi of each ch (i) of 10 to 600 ch measured at a fixed period. Dividing the crest value ⁇ Hi ⁇ Mi by the integrated count value ⁇ Mi to obtain the average crest value for the calculation cycle time, taking the average crest value, and moving average the average crest value data string for the updated measurement time The peak value h2 is obtained. The moving average peak value h2 is correlated with the dominant energy of the dose rate at the measurement time, and the dominant energy increases as the moving average peak value h2 increases.
- FIG. 7 shows a high range compensation coefficient table (second compensation coefficient table) in which the moving average peak value h2 and the energy compensation coefficient ⁇ 2 (second energy compensation coefficient) are associated with each other.
- the energy compensation coefficient calculation unit 3233 stores the high range compensation coefficient table ( ⁇ 2), compares the moving average peak value h2 with the high range compensation coefficient table, and determines and outputs the energy compensation coefficient ⁇ 2.
- the high range dose rate calculation unit 3232 outputs a high range compensation dose rate DH (second compensation dose rate) obtained by multiplying the high range dose rate D2 before energy compensation by the energy compensation coefficient ⁇ 2.
- the reference energy is, for example, ⁇ ray 662 keV of Cs-137, the corresponding energy compensation coefficient ⁇ 2 is 1, and the energy compensation coefficient ⁇ 2 of other energy is shown as a ratio to the reference.
- the high range compensation coefficient table is created in the same manner as the low range compensation coefficient table.
- FIG. 8 illustrates energy characteristics before and after energy compensation for a low range dose rate.
- the energy characteristic a indicates the energy characteristic of the low range dose rate D1 before energy compensation when a NaI (Tl) scintillator is used as the cylindrical inorganic crystal scintillator 211 of the first radiation detector 21.
- the energy characteristic b shows the energy characteristic of the low range compensation dose rate DL as a result of multiplying the low range dose rate D1 before energy compensation by the energy compensation coefficient ⁇ 1. Both show energy characteristics expressed as a ratio of the response of other energy when the response of low range dose rate D1 before energy compensation when Cs (cesium) -137 gamma ray energy 662 keV is incident is there.
- the horizontal axis represents the radiation input energy E (MeV), and the vertical axis represents the response ratio F of the dose rate measuring apparatus 1 with the reference point P as the reference value 1. Since the energy characteristic a is obtained by determining the low-range dose rate D1 before energy compensation using the G (E) function and finely correlating the wave height spectrum to the dose rate, basically a good energy characteristic is obtained. In order to eliminate the influence of noise in the -D conversion unit 312, the detector signal pulse of less than 50 keV is not measured but discarded as noise. Even if the energy of the radiation incident on the first radiation detector 21 is within the measurement energy range, a part of the peak spectrum is distributed below the peak peak value corresponding to the energy of the incident radiation. Since the rate of destruction increases as the energy of the incident radiation approaches the lower limit energy of 50 keV, the influence on the low range dose rate D1 before energy compensation cannot be ignored.
- the incident radiation is 400 keV or less
- the light emission amount per unit energy applied becomes a peak shape with a maximum of about 1.2 times.
- the energy characteristic a becomes a mountain shape at about 100 keV, and falls at an energy of less than that.
- the energy compensation coefficient ⁇ 1 is multiplied by the low range dose rate D1 before energy compensation to obtain the low range compensated dose rate DL after energy compensation. Good characteristics can be obtained.
- FIG. 9 illustrates the energy characteristics before and after energy compensation for a high range dose rate.
- the energy characteristic c indicates the energy characteristic of the high range dose rate D2 before energy compensation.
- the energy characteristic d indicates the energy characteristic of the high range compensation dose rate DH as a result of multiplying the high range dose rate D2 before energy compensation by the energy compensation coefficient ⁇ 2.
- the sensitivity as a count rate per dose rate can be generally flattened by the action of the physical filters 222a, 222b, and 222c provided so as to enclose each of the PL scintillation fibers 221a, 221b, and 221c, the sensitivity is as low as 100 keV or less. It becomes a little mountain shape with energy.
- the energy compensation coefficient ⁇ 2 is multiplied by the high range dose rate D2 before energy compensation to obtain the high range compensation dose rate DH after energy compensation, so that the energy characteristic d Good characteristics can be obtained.
- the first radiation detector 21 and the second radiation detector 22 are affected by the probability of pile-up of the detector pulse signal when the interval between detection signal pulses is shortened when the dose rate is high, and when the dose rate is further increased. Dose rate decreases. At the same dose rate, the number of analog voltage pulses output from the first radiation detector 21 (scintillation detector) per unit time decreases as the energy of the incident radiation increases, and saturation due to pile-up is a high dose. Shift to the rate side. Therefore, physical filters 222a, 222b, and 222c are provided so as to cover the PL scintillation fibers 221a, 221b, and 221c. In the absence of the filter 222, the energy characteristic in which the count rate of the detection signal pulse corresponding to the dose rate increases exponentially as the energy becomes low can be controlled almost flat, and the detection signal pulse pile-up at low energy can be controlled. Can be suppressed.
- FIG. 10 illustrates the switching operation point of the dose rate switching unit 33.
- the horizontal axis represents the input dose rate D (in) of the incident radiation
- the vertical axis represents the low range dose rate calculation unit 3133 and the high range dose rate calculation unit 3232.
- the output dose rate D (out) is shown. Both the horizontal and vertical axes are displayed in log scale.
- the input / output response characteristic a1 conceptually shows the characteristic of the low range dose rate measurement unit 31 with respect to the effective energy 57 keV of Am (Americium) -241.
- the low range compensation dose rate DL increases in proportion to the input dose rate D (in) as indicated by a solid line, and then saturates as indicated by a dotted line.
- the input / output response characteristic a2 conceptually shows the characteristic of the low range dose rate measurement unit 31 with respect to the effective energy 660 keV of Cs (cesium) -137.
- the input / output response characteristic a2 substantially overlaps with the input / output response characteristic a1 and transitions as indicated by a solid line, and saturates as indicated by a dotted line at a dose rate higher than the input / output response characteristic a1.
- the input / output response characteristic b1 conceptually shows the characteristic of the high range dose rate measurement unit 32 with respect to Am-241. In the vicinity of the switching point of fluctuation, the center value substantially overlaps with the input / output response characteristic a1, and the saturation shifts to the high range dose rate side by 4 decades or more from the input / output response characteristic a1 and does not saturate within the measurement range.
- the input / output response characteristic b2 conceptually shows the characteristic of the high range dose rate measurement unit 32 with respect to Cs-137.
- the center value of the fluctuation almost overlaps with the input / output response characteristic a2, and the saturation is shifted by 4 decades or more to the higher dose rate side than the input / output response characteristic a2. It does not saturate within the measurement range, and the input / output response characteristic b1 and the input / output response characteristic b2 substantially overlap within the measurement range.
- the overlap of the solid line of the input / output response characteristic a1 and the input / output response characteristic b1 represents an ideal case where the low range compensation dose rate DL has perfect linearity and the energy characteristic is compensated completely flat. .
- the overlap between the solid line of the input / output response characteristic a2 and the input / output response characteristic b2 shows an ideal case where the high range compensation dose rate DH has perfect linearity and the energy characteristic is compensated completely flat.
- the overlap of the input / output response characteristics a1, a2, b1, b2 near the switching point is ideal because there is no difference in dose rate measurement and the energy characteristics of the low range compensation dose rate DL and the high range compensation dose rate DH are completely overlapped. Shows the case.
- the dose rate switching unit 33 receives the low range compensation dose rate DL output from the low range dose rate calculation unit 3133 and the high range compensation dose rate DH output from the high range dose rate calculation unit 3232, and receives the dose rate.
- the ratio (high range compensation dose rate DH / low range compensation dose rate DL) is determined.
- the dose rate ratio (DH / DL) becomes 1 + k1 or more during the upward switching, the measurement range is switched from the low range compensation dose rate DL to the high range compensation dose rate DH.
- the dose rate ratio (DH / DL) becomes 1 + k2 or less, the measurement range is switched from the high range compensation dose rate DH to the low range compensation dose rate DL.
- the constant k1 and the constant k2 are positive.
- the display operation unit switches the display range from the low range to the high range when the dose rate ratio exceeds 1 + k1, and switches the display range from the high range to the low range when the dose rate ratio decreases to 1 + k2.
- the figure shows an ascending switching point A1 and a descending switching point A2 for Am-241 and an ascending switching point B1 and a descending switching point B2 for Cs-137.
- k1> k2 is set so as to prevent hunting of the switching operation due to fluctuations, and a suitable value obtained by experiments is set so as to minimize the level difference due to switching. Since the constant k1 and the constant k2 are positive numbers and the saturation of the low range compensation dose rate DL is detected and switched to the high range compensation dose rate DH, the switching is surely performed even during a sudden rise response. Can do.
- the low range dose rate measurement unit 31 and the high range dose rate measurement unit 32 measure the pulse height spectrum to obtain the moving average peak value, and based on the moving average peak value, the energy of each low energy region The characteristics are compensated. Suitable energy characteristics can be obtained over the entire measurement energy, and the low-range compensation dose rate DL and the high-range compensation dose rate DH of each share are measured based on the suitable energy characteristics.
- the dose rate switching unit 33 automatically determines a suitable switching point according to the energy of the incident radiation based on the dose rate ratio (DH / DL) to switch between the low range compensation dose rate DL and the high range compensation dose rate DH. Since it did in this way, the highly accurate dose rate measuring apparatus with a favorable energy characteristic and linearity over the whole measurement range can be provided.
- the PL scintillation fibers 221a, 221b, and 221c of the second radiation detector 22 are arranged so that one end face of each PL scintillation fiber released faces obliquely upward around the central axis of the first radiation detector. Therefore, the PL scintillation fibers 221 are arranged at positions that do not obstruct the measurement space of the inorganic crystal scintillator 211 of the first radiation detector. Further, the total effective area viewed from the ceiling direction and the effective area viewed from the straight line direction perpendicular to the central axis of the first radiation detector are arranged to be approximately equal. As a result, the first radiation detector 21 and the second radiation detector 22 do not interfere with each other, and good direction dependency can be obtained with respect to the measurement space.
- the second radiation detector is configured not to be a shadow of the measurement area around the central axis of the first radiation detector and to share the measurement area with the first radiation detector.
- the sensitivity when the radiation is irradiated from the central axis direction of the first radiation detector and the sensitivity when the radiation is irradiated from the direction perpendicular to the central axis are symmetric and equiangular with respect to the central axis.
- the first dose rate measuring means measures the peak value of the first detection signal pulse, generates a first peak spectrum based on the peak value, and the peak value and unit count rate of the first peak spectrum. The first dose rate is obtained based on the relationship of the hit dose rate.
- the second dose rate measuring means measures a peak value of the second detection signal pulse, generates a second peak spectrum based on the peak value, and obtains a count rate based on the second peak spectrum. The second dose rate is obtained by converting the count rate into a dose rate.
- the first energy compensation coefficient calculation means and the second energy compensation coefficient calculation means obtain an average peak value based on the spectrum of the low range dose rate range and the high range dose rate range, respectively, and are specific to the radiation detector based on the average peak value.
- the distortion of the energy characteristics is corrected so that good energy characteristics can be obtained over the entire range.Therefore, when switching between the low dose rate range and the high dose rate range and outputting, the level difference caused by the dose rate switching It is possible to provide a dose rate measuring apparatus that can be suppressed to the minimum and that has good measurement accuracy over the entire dose rate range.
- FIG. FIG. 11 shows the configuration of the PL scintillation fiber in the dose rate measuring apparatus according to the second embodiment.
- the PL scintillation fibers 221a, 221b, and 221c of the second radiation detector 22 are configured by a single plastic scintillation fiber.
- the PL scintillation fiber 221 is configured by a fiber bundle 220 in which a plurality of (for example, three) plastic scintillation fibers are bundled.
- FIG. 12 shows the configuration of the detector mount 23 in the dose rate measuring apparatus according to the third embodiment.
- a shield 26 that shields radiation is disposed in the scintillation fiber coordination region of the detector mount 23.
- the detector mount 23 includes a shield 26 at a position between the inside of the PL scintillation fibers 221a to 221c and the outside of the first radiation detector 21 so as not to obstruct the measurement space of the first radiation detector 21. Yes. Since the radiation in the direction of the back surface of the second radiation detector 22 is shielded by the shield 26, the direction characteristics in the dose rate measurement can be further improved.
- FIG. 13 shows a calculation processing flow in the dose rate measuring apparatus according to the fourth embodiment.
- the diagnosis of the output switching is performed based on the dose rate ratio (DH / DL).
- the process starts at S0, and at S1, as in the first embodiment, the determination result of the necessity of output switching and the dose rate ratio (DH / DL) for the current calculation cycle are read. In S2, it is determined whether or not output switching is necessary. If No, the process returns to S1.
- the key for output switching is Yes, it is determined in S3 whether the current dose rate ratio (DH / DL) is within the set value. If the determination is Yes, the process returns to S1. If the dose rate ratio (DH / DL) is larger than the set value and the determination is No, an output switching abnormality alarm (abnormal alarm) is transmitted to the display operation unit 34 in S4 and then to S1. Return. Since the display operation unit 34 displays an output switching abnormality alarm based on the diagnosis result, it is possible to self-diagnose whether or not normal range switching is performed, and a more reliable dose. A rate measuring device can be provided.
- Dose rate measuring apparatus 2 detection part, 21 1st radiation detector, 211 inorganic crystal scintillator, 212 photomultiplier tube, 213 preamplifier, 214 detector case, 22 2nd radiation detector, 221a, 221b, 221c PL scintillation fiber, 222a, 222b, 222c filter, 223a, 223b, 223c optical coupler, 224a, 224b, 224c optical fiber, 225a, 225b, 225c light shielding tube, 226 light guide, 227 photomultiplier tube, 228 preamplifier, 229 detector Case, 220 Fiber bundle, 23 Detector mount, 24 Detector jacket, 25 Stand, 26 Shield, 3 Measuring unit, 31 Low range dose rate measuring unit, 311 Pulse amplifier, 312 AD converter, 313 Low range calculation Part, 3131 wave height Coulter generator, 3132 G (E) function memory, 3133 low range dose rate calculator, 3
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Abstract
Description
以下、本発明の実施の形態に係る線量率測定装置について図1~13を参照して説明する。図1は、実施の形態1に係る線量率測定装置の構成を示す図である。図に示すように、線量率測定装置1は、検出部2と測定部3を有する。検出部2は低レンジ線量率範囲を担当する第1の放射線検出器21と、低レンジ線量率範囲に続くその上の高レンジ線量率範囲を担当する第2の放射線検出器22を備えている。第1の放射線検出器21は、吸収した放射線のエネルギーに比例する波高値を有する離散的な検出信号パルス(第1の検出信号パルス)を低レンジ線量率において出力する。第2の放射線検出器22は、吸収した放射線のエネルギーに比例する波高値を有する離散的な検出信号パルス(第2の検出信号パルス)を高レンジ線量率において出力する。
実施の形態2に係わる線量率測定装置におけるPLシンチレーションファイバーの構成を図11に示す。実施の形態1では、第2の放射線検出器22のPLシンチレーションファイバー221a、221b、221cは、1本のプラスチックシンチレーションファイバーで構成されている。実施の形態2では、複数の(例えば3本の)プラスチックシンチレーションファイバーを束ねたファイバー束220でPLシンチレーションファイバー221を構成した。ファイバー束を使うことで、レンジ配分においてシンチレータの実質的な径を大きくする必要が生じた場合にもフレキシブルに対応できる効果を奏する。
実施の形態3に係わる線量率測定装置における検出器架台23の構成を図12に示す。検出器架台23のシンチレーションファイバー配位領域に放射線を遮蔽する遮蔽体26を配置している。検出器架台23は、PLシンチレーションファイバー221a~221cの内側と第1の放射線検出器21の外側の間の、第1の放射線検出器21の測定空間の障害にならない位置に遮蔽体26を備えている。遮蔽体26により第2の放射線検出器22の裏面方向の放射線を遮蔽するため、線量率測定における方向特性をより改善できる。
実施の形態4に係る線量率測定装置における演算処理フローを図13に示す。本実施の形態では、線量率切換部33が、今回の演算周期で線量率出力の切換を行う場合に、線量率比(DH/DL)に基づき出力切換の診断を行うようにしている。処理がS0でスタートし、S1で実施の形態1と同様に、今回の演算周期に関する出力切換の要否の判定結果と線量率比(DH/DL)を読み込む。S2で出力切換が要かどうかについて判定し、NoならばS1に戻る。
Claims (7)
- 無機結晶シンチレータを有し、放射線が入射すると検出信号パルスを出力する第1の放射線検出器と、
プラスチックシンチレータを有し、放射線が入射すると検出信号パルスを出力する第2の放射線検出器と、
円筒部を有し、前記第1の放射線検出器および前記第2の放射線検出器を収容する検出器架台と、
前記第1の放射線検出器が出力する検出信号パルスを基に、エネルギー補償係数とG(E)関数テーブルを用いて入射した放射線の第1の補償線量率を算出する低レンジ演算部と、
前記第2の放射線検出器が出力する検出信号パルスを基に、エネルギー補償係数を用いて入射した放射線の第2の補償線量率を算出する高レンジ演算部と、
前記低レンジ演算部が算出した第1の補償線量率と前記高レンジ演算部が算出した第2の補償線量率から、線量率比(第2の補償線量率/第1の補償線量率)を求め、この求められた線量率比の大きさに従って出力する補償線量率を選定する線量率切換部と、
前記線量率切換部が出力した補償線量率を表示する表示操作部と、を備え、
前記第2の放射線検出器が有するプラスチックシンチレータは、前記検出器架台の円筒部に巻き回されていることを特徴とする線量率測定装置。 - 前記第1の放射線検出器および前記第2の放射線検出器は、前記検出器架台の中心軸上に配置されていることを特徴とする請求項1に記載の線量率測定装置。
- 前記プラスチックシンチレータは、前記無機結晶シンチレータの底面よりも奥側に配置されていることを特徴とする請求項1に記載の線量率測定装置。
- 前記線量率切換部は、定数k1>定数k2>0として、線量率比が1+k1を超えると第2の補償線量率を選定して出力し、線量率比が1+k2まで低下すると第1の補償線量率を選定して出力することを特徴とする請求項1に記載の線量率測定装置。
- 前記プラスチックシンチレータは、ファイバー束からなることを特徴とする請求項1に記載の線量率測定装置。
- 前記検出器架台は、円筒部の内側に放射線の遮蔽体が配設されていることを特徴とする請求項1に記載の線量率測定装置。
- 前記線量率切換部は、線量率比が設定値よりも大きい場合、異常警報を発信することを特徴とする請求項1に記載の線量率測定装置。
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