Electronic personal dosimeter applied to medical intervention pulse radiation field

Abstract

The invention discloses an electronic personal dosimeter applied to a medical intervention pulse radiation field, and relates to the field of medical radiation monitoring, and the electronic personal dosimeter comprises an instantaneous-accumulation dual-channel detector, an ADC, a main controller and a segment code screen; the detector is arranged in the medical intervention pulse radiation field, is connected with the ADC and is used for simultaneously collecting transient response current and accumulated integral charge of the medical intervention pulse radiation field; the ADC is connected with the SPI end of the main controller; the LCD end of the main controller is connected with the segment code screen; the transient response current and the accumulated integral charge of the radiation field are synchronously collected through the detector and are converted into digital signals through the ADC, and after the radiation dose rate and the radiation accumulated dose are calculated by the main controller, the radiation dose rate and the radiation accumulated dose are displayed in real time through the segment code screen. The radiation dose rate and the radiation accumulated dose of the detector can be synchronously monitored in real time in a small size by adopting a dual-channel combination mode, the power consumption is reduced, and the portability and the environmental adaptability of the dosimeter are improved.

Description

Technical Field

[0001] This application relates to the field of medical radiation monitoring, and in particular to an electronic personal dosimeter for use in medical interventional pulsed radiation fields. Background Technology

[0002] Pulsed X-ray radiation fields refer to the instantaneous pulsed radiation fields generated by some medical diagnostic X-ray devices (such as radiographic X-ray machines). Unlike continuous and stable radiation fields, their radiation appears in the form of short-duration, high-intensity pulses. In pulsed fields, traditional online measurement methods for continuous radiation fields are insufficient to cope with the challenges posed by high instantaneous dose rates and short pulse durations. Detectors may experience problems such as pulse saturation, ion recombination, and signal accumulation, leading to inaccurate measurements. The core of online radiation field measurement lies in the probe composed of a detector and readout circuitry. Detectors can generally be classified by material into gas, semiconductor, and scintillator types, and by signal readout type into pulsed and cumulative types (usually manifested as current). Pulsed detectors are generally designed to distinguish the interaction between each ray and the detector, typically statistically expressed as count rate, pulse amplitude spectrum (energy spectrum), and time spectrum. They have a fast response but are prone to saturation, and are generally suitable for environmental and site monitoring. In pulsed radiation fields, due to the simultaneous action of a large number of short-sighted rays, saturation is easily encountered. Pulsed detectors, on the other hand, involve continuous interaction between the radiation and the detector during the collection period, resulting in a continuous output charge. Their response time depends on the detector signal transport time and the time constant of the readout circuit, making them less prone to saturation but relatively slow. For measuring pulsed field radiation, using a Farmer ionization chamber is a relatively mature method, commonly used in QA instruments such as Raysafe. However, these chambers are bulky, consume a lot of power, and their gas detectors are easily affected by environmental changes, while the electrometers are highly sensitive to humidity, presenting certain limitations. Furthermore, these devices lack cumulative dose measurement capabilities, making it impossible to continuously monitor the cumulative dose received by personnel during equipment use.

[0003] In summary, existing dosimeters struggle to simultaneously measure both instantaneous response current and accumulated integrated charge, and their large size, inconvenient wear, and high power consumption limit their application scope. Summary of the Invention

[0004] The purpose of this application is to provide an electronic personal dosimeter for use in medical interventional pulsed radiation fields, which can realize real-time synchronous monitoring of radiation dose rate and cumulative radiation dose in medical interventional pulsed radiation fields, reduce power consumption, and improve the portability and environmental adaptability of the dosimeter.

[0005] To achieve the above objectives, this application provides the following solution: This application provides an electronic personal dosimeter for use in medical interventional pulsed radiation fields. The electronic personal dosimeter includes: an instantaneous-cumulative dual-channel detector, an ADC, a main controller, and a segment display. The instantaneous-cumulative dual-channel detector is disposed within the medical interventional pulsed radiation field, and its output is connected to the analog input of the ADC. The instantaneous-cumulative dual-channel detector is used to simultaneously acquire the instantaneous response current and accumulated integrated charge of the medical interventional pulsed radiation field. The digital output of the ADC is connected to the SPI terminal of the main controller. The ADC is used to convert the analog instantaneous response current and accumulated integrated charge into digital quantities. The main controller is an STM32L476 ultra-low power microcontroller. The LCD terminal of the main controller is connected to the segment display. The main controller is used to obtain the radiation dose rate and cumulative radiation dose based on the displayed instantaneous response current and accumulated integrated charge through scale conversion, and transmit them to the segment display for real-time display.

[0006] According to the specific embodiments provided in this application, the following technical effects are disclosed: This application employs a dual-channel structure combining a real-time instantaneous response current measurement channel and a cumulative charge measurement channel. The real-time measurement channel, through rapid current conversion, is specifically designed for rapid measurement in high-dose, short-duration pulsed radiation fields, solving the problem of dose underestimation or alarm failure caused by the saturation of traditional electronic personal dosimeters under pulsed fields. The cumulative charge measurement channel can measure cumulative charge over a wide dose rate range, including the background, ensuring accurate and effective measurement of cumulative dose in low-dose environments. This dual-channel design achieves both rapid dose rate alarm and high-precision cumulative dose measurement within a compact size. The dual-channel design, combined with the STM32L476 microcontroller, further reduces the overall power consumption of the dosimeter, improves its portability and environmental adaptability in medical interventional pulsed radiation fields, and reduces the production cost of the dosimeter. Attached Figure Description

[0007] To more clearly illustrate the technical solutions in the embodiments of this application or related technologies, the drawings used in the embodiments will be briefly introduced below. Obviously, the drawings described below are only some embodiments of this application. For those skilled in the art, other drawings can be obtained based on these drawings without creative effort.

[0008] Figure 1 A flowchart illustrating an electronic personal dosimeter applied to a medical interventional pulsed radiation field, provided as an embodiment of this application. Figure 1 .

[0009] Figure 2A flowchart illustrating an electronic personal dosimeter applied to a medical interventional pulsed radiation field, provided as an embodiment of this application. Figure 2 .

[0010] Figure 3 A three-dimensional view of the instantaneous-cumulative dual-channel detector provided in an embodiment of this application.

[0011] Figure 4 A cross-section of the instantaneous-accumulation dual-channel detector provided in the embodiments of this application. Figure 1 .

[0012] Figure 5 A cross-section of the instantaneous-accumulation dual-channel detector provided in the embodiments of this application. Figure 2 .

[0013] Figure 6 A side view of the instantaneous-cumulative dual-channel detector provided in an embodiment of this application.

[0014] Figure 7 A circuit diagram of a fast response current measurement circuit provided in an embodiment of this application.

[0015] Figure 8 A circuit diagram of the integrated charge measurement circuit provided in an embodiment of this application.

[0016] Figure 9 This is a schematic diagram illustrating the characteristics of the STM32L476 ultra-low power microcontroller provided in the embodiments of this application.

[0017] Figure 10 The circuit diagram of the ADC provided in the embodiments of this application.

[0018] Figure 11 A circuit diagram of a high-voltage regulation circuit provided in an embodiment of this application.

[0019] Figure 12 A low-power design circuit diagram for an instantaneous-cumulative dual-channel detector provided in an embodiment of this application.

[0020] Figure label: 1. Instantaneous-cumulative dual-channel detector; 2. ADC; 3. Main controller; 4. Segment display; 5. Alarm module; 6. Temperature measurement circuit. Detailed Implementation

[0021] The technical solutions of the embodiments of this application will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some embodiments of this application, and not all embodiments. Based on the embodiments of this application, all other embodiments obtained by those skilled in the art without creative effort are within the scope of protection of this application.

[0022] To make the above-mentioned objectives, features and advantages of this application more apparent and understandable, the application will be further described in detail below with reference to the accompanying drawings and specific embodiments.

[0023] Example 1, as Figures 1-2 As shown, this embodiment provides an electronic personal dosimeter for use in medical interventional pulsed radiation fields. The electronic personal dosimeter for use in medical interventional pulsed radiation fields includes: an instantaneous-cumulative dual-channel detector 1, an ADC 2, a main controller 3, and a segment code screen 4.

[0024] The instantaneous-cumulative dual-channel detector 1 is set in the medical interventional pulse radiation field, and the output terminal of the instantaneous-cumulative dual-channel detector 1 is connected to the analog input terminal of the ADC2; the instantaneous-cumulative dual-channel detector 1 is used to simultaneously collect the instantaneous response current and the accumulated integrated charge of the medical interventional pulse radiation field.

[0025] The digital output terminal of the ADC2 is connected to the SPI terminal of the main controller 3; the ADC2 is used to convert the instantaneous response current and accumulated integrated charge of the analog quantity into digital quantity; the main controller 3 is an STM32L476 ultra-low power microcontroller.

[0026] The LCD terminal of the main controller 3 is connected to the segment code screen 4; the main controller 3 is used to control the segment code screen 4 to display the instantaneous response current and accumulated integrated charge in real time.

[0027] Furthermore, the detector is a silicon PIN detector.

[0028] Furthermore, such as Figures 3-6 As shown, the detector is packaged in a ceramic housing LCC10 package.

[0029] In practical applications, the instantaneous-cumulative dual-channel detector 1 is powered by a low-noise power supply. The signal processing circuit is divided into two measurement channels: dose rate and cumulative dose. The dose rate measurement channel uses a low-noise logarithmic current-type preamplifier, which can rapidly amplify and acquire the weak current output by the detector over a considerable dynamic range to obtain the real-time dose rate, avoiding the excessively long measurement time caused by frequent range switching in commonly used transimpedance amplifier methods. However, the current readout method is limited by the minimum measurable current. The measurement of the extremely weak current (pA~fA) output by the detector and the bandwidth (kHz~MHz) near the background cannot be simultaneously satisfied, resulting in a high detection lower limit for the fast measurement channel. Direct integration would lead to insufficient response to the cumulative effect. In this case, the cumulative dose during QA measurement is related to the protective requirements of the personnel and must be accurately measured. Therefore, a separate cumulative dose measurement channel is set up. This channel uses a gated charge integration circuit to accumulate and collect the positive and negative electron pairs generated by the ionization of radiation in the detector, thereby accurately obtaining the cumulative dose over a period of time. The function of the PIN is to convert the radiation signal into an electrical signal and output the signal to the fast measurement channel and the cumulative measurement channel.

[0030] Existing detectors generally fall into three categories: ionization chambers, scintillators, and semiconductors. An ionization chamber is a gas ionization detector that measures charge by collecting ion pairs generated by radiation ionization between electrodes; its charge is proportional to the absorbed dose. Its inherent response time is determined by ion drift and is typically on the order of milliseconds, much slower than the typical pulse duration (µs). Therefore, ionization chambers cannot resolve the instantaneous waveform of a single µs pulse and can only measure the accumulated charge of multiple pulses. The shorter the pulse, the higher the instantaneous ion density, making ion recombination more likely and reducing collection efficiency. Therefore, the linearity of ionization chambers under extremely short pulses is affected by ion recombination. Scintillators (such as organic plastics and inorganic crystals) emit photons instantaneously after absorbing radiation. The light pulse is converted into an electrical signal by a photomultiplier tube (PMT) or silicon photomultiplier (SiPM). These detectors have extremely fast responses; the fluorescence lifetime of a typical plastic scintillator is only a few nanoseconds, while some inorganic scintillators, such as LYSO, are about 40 ns. Therefore, they can finely resolve pulses on the order of µs or even nanoseconds. High-speed data acquisition systems can acquire pulse waveforms at sampling rates of kHz or even higher, enabling pulse-by-pulse dose measurement. Scintillation detectors are well-suited for time-resolved dose measurements of short-pulse beams; however, scintillator detection systems may exhibit optical output saturation and readout device nonlinearity under high-dose pulses. Small-volume plastic scintillators maintain linear output in the range of ~Gy per pulse, but saturation tendencies begin to be observed when the single-pulse dose reaches several Gy or higher. Semiconductor detectors utilize electron-hole pairs generated by radiation in solid materials, collecting them through a built-in electric field to form current pulses. Typical examples are silicon PN junction diodes and artificial single-crystal diamond detectors. They possess extremely fast charge collection speeds (high carrier mobility, collection completed in several nanoseconds to hundreds of nanoseconds) and high ionization energy conversion efficiency, making them ideal for instantaneous dose measurements of short-pulse radiation. Silicon diodes can output clear current pulses under 6MV pulses from linear accelerators, with rise times < tens of nanoseconds. SiC exhibits higher carrier saturation drift velocity, higher breakdown field strength, and stronger radiation resistance. SiC detectors show no obvious signs of saturation even at doses as high as 21 Gy / pulse or even 25 Gy / pulse, and their signal response demonstrates good independence from both the DPP and pulsed dose rate. Diamond detectors, due to their large bandgap and fast saturation electric velocity, have been proven to measure nanosecond X-ray pulses without significant time lag. Experiments show that single-crystal diamond responds well to nanosecond pulsed X-ray fields. Therefore, semiconductor detectors have significant advantages in time resolution and high-speed measurement.

[0031] This application selects semiconductor detectors, preferentially using PIN-type silicon detectors as the detection device. However, compatible packaged diamond and SiC detectors can also be used as needed to achieve excellent linearity over a wide dose rate range. Furthermore, such as Figures 3-6As shown, this application adopts a ceramic-cased LCC10 package, which has advantages such as reliable structure, small size, high signal-to-noise ratio, good sensitivity, and stable performance. This package is also suitable for other semiconductor detectors made of materials such as SiC and diamond, and is compatible with shapes not exceeding [a certain size]. Other detector sizes are also discussed. Unlike traditional Farmer ionization chambers (large size, millisecond response, and susceptible to humidity), this application's semiconductor-compatible framework achieves "material self-adaptation + interface standardization," maintaining microsecond-level response across a wide dose rate range (fA~mA), filling the gap in the market for cumulative monitoring of personal protective equipment in QA instruments (such as RaySafe). Literature shows that similar SiC / diamond integration is rare in pulsed field measurements; the packaging compatibility of this application can reduce upgrade costs by more than 30%.

[0032] like Figure 9 As shown, STMicroelectronics' STM32L476 ultra-low-power microcontroller is based on a high-performance Arm® Cortex®-M4 32-bit RISC core operating at frequencies up to 80MHz. The Cortex-M4 core features a single-precision floating-point unit (FPU) that supports all Arm® single-precision data processing instructions and data types. It also includes a complete set of DSP instructions and a memory protection unit (MPU) for enhanced application security. Its features are as follows: Power supply range from 1.71V to 3.6V.

[0033] Temperature range: -40°C to 125°C.

[0034] Low power consumption: 300nA, VBAT mode: powers the RTC and 32x32-bit backup registers; 30nA, shutdown mode (5 wake-up pins); 420nA, standby mode (using RTC); 39μA / MHz in run mode (@3.3VSMPS mode).

[0035] The wake-up time from stop mode is 4μs.

[0036] 4MHz to 48MHz crystal oscillator; 32kHz crystal oscillator for RTC (LSE); 16 timers.

[0037] Up to 114 high-speed I / Os with a maximum withstand voltage of 5V; up to 14 I / Os with independent power supplies and a minimum voltage of 1.08V.

[0038] RTC with hardware calendar, alarms, and calibration.

[0039] 8×40 or 4×44 LCD with boost converter.

[0040] Data storage: Up to 1MB of Flash memory, supporting simultaneous read and write of two memory areas and proprietary code read protection; up to 128KB of SRAM, of which 32KB supports hardware parity checking.

[0041] Analog peripherals: 3 x 12-bit ADC2 (5Msps), up to 16-bit ADC2 (supports hardware oversampling), 200μA / Msps; 2 x 12-bit DAC output channels, low-power sample and hold circuitry.

[0042] Communication peripherals: 3 I2CFM+ (1Mb / s); 5 USARTs; 1 LPUART; 3 SPIs.

[0043] Development support: Serial wire debugging (SWD), JTAG.

[0044] Optionally, after the main controller 3 acquires the instantaneous response current and accumulated integrated charge, it first determines whether the range of the accumulated charge channel (integrated charge measurement circuit) is saturated. If the range is saturated, it switches the range to the optimal range based on the rapid measurement data. If the accumulated charge channel is not saturated, it determines whether the measured value is within the appropriate range. If the measured value is less than 20% or greater than 50% of the range, it switches the range to make the measured value within 50% of the range. Finally, it compares the measurement data of the rapid current channel (response current rapid measurement circuit) and the accumulated charge channel to determine whether the data is valid. If the data is valid, it outputs the measurement result; if the data is invalid, it outputs a fault message and re-measures.

[0045] Furthermore, the instantaneous-cumulative dual-channel detector 1 specifically includes: a response current fast measurement circuit and an integral charge measurement circuit.

[0046] The rapid response current measurement circuit is used to measure the instantaneous response current of a medical interventional pulsed radiation field.

[0047] Furthermore, the fast response current measurement circuit includes at least a single-chip logarithmic detector; the single-chip logarithmic detector is model ADL5303.

[0048] The integrated charge measurement circuit is used to measure the cumulative integrated charge of the medical interventional pulsed radiation field.

[0049] Furthermore, such as Figure 8 As shown, the integrated charge measurement circuit includes at least: a switched integrating transimpedance amplifier; the switched integrating transimpedance amplifier is model IVC102.

[0050] In practical applications, such as Figure 7As shown, the fast current measurement circuit is compatible with both scintillator-coupled SiPM outputs and PIN detector outputs, using the ADL5303 as the core device. The ADL5303 is a monolithic logarithmic detector offering a wide dynamic range and a flexible, easy-to-use form factor. Its proprietary design and precise laser trimming enable a wide measurement range and high accuracy. The input pin INPT is surrounded by a VSUM protection pin that tracks the summing node voltage. Connecting the device's exposed pads to the VSUM pin provides continuous protection to minimize leakage current at the INPT pin. The default logarithmic slope of the VLOG output is set by an internal 5kΩ resistor. The logarithmic slope can be reduced by using an external parallel resistor, or increased by using a buffer and a pair of external feedback resistors; the choice of slope and intercept depends on the specific application.

[0051] The versatility of the ADL5303 allows for optimal selection in two common scenarios. First, the ADL5303 allows for an input current range less than the full 160dB to fully utilize the available voltage range at the output. Second, it allows for defining the output voltage range to accommodate the input capacity of a subsequent ADC2. In specific applications, very high slopes (such as 1V / 10x range) enable high sensitivity coverage of a small IPD range. The slope can be reduced without limitation by adding a parallel resistor RS between VLOG and ground. Since the resistance at this pin is trimmed to 5kΩ, the accuracy of the modified slope depends on the external resistor. The modified slope is calculated using the following formula: At IPD=1nA, the bandwidth of the ADL5303 is approximately 2kHz, and increases proportionally with IPD, reaching a maximum of 10MHz, enabling effective measurement of pulsed radiation fields as short as 1µs, fully meeting the requirements for rapid current measurement over a wide dynamic range.

[0052] Adaptive bias circuit integration: Borrowing from the ADL5303's adaptive bias (reverse bias from 0.1V to 2V), it is extended into a dedicated module for the detector. It minimizes dark current (<1pA) under low light (low dose) conditions and linearly increases the bias to above 5V under high dose conditions to prevent saturation. A temperature-compensated sensor (NTC thermistor) is added to compensate for environmental changes (-20°C to 60°C), ensuring linearity deviation <1%.

[0053] The integrated charge measurement circuit includes a high-precision switched-integrating transimpedance amplifier, IVC102. A microcontroller's embedded timer generates digital control signals to control the IVC102. The IVC102 is a precision integrating amplifier that integrates a FET operational amplifier, an integrating capacitor, and a low-leakage-current FET switch. The IVC102 integrates a low-level input current within a user-defined time, storing the resulting voltage on the integrating capacitor. The output voltage remains stable for accurate measurement. Compared to traditional transimpedance operational amplifier circuits that require extremely high feedback resistors, the IVC102 provides a more precise, lower-noise alternative.

[0054] The IVC102 is ideal for amplifying low-level sensor currents from sources such as photodiodes and ionization chambers. The input signal current can be positive or negative. TTL / CMOS compatible timing inputs control the integration period, hold, and reset functions to set the effective transimpedance gain and reset (discharge) the integrating capacitor. Baseline correction is achieved by calculating the average voltage over the pulse interval (e.g., −600ns to 0ns) and subtracting it from the signal integral.

[0055] Furthermore, such as Figure 12 As shown, the electronic personal dosimeter applied to the medical intervention pulsed radiation field further includes: a first comparator and a second comparator.

[0056] The non-inverting input of the first comparator is connected to the output of the fast response current measurement circuit, the inverting input of the first comparator is connected to the DAC output port of the main controller 3, and the output of the first comparator is connected to the analog input of the ADC2. The first comparator is used to trigger an interrupt in the main controller 3 when the voltage of the instantaneous response current is greater than a first voltage threshold. The main controller 3 then starts the ADC2 to measure the instantaneous response current.

[0057] The non-inverting input of the second comparator is connected to the output of the integrated charge measurement circuit, the inverting input of the second comparator is connected to the DAC output port of the main controller 3, and the output of the second comparator is connected to the analog input of the ADC2. The second comparator is used to trigger an interrupt in the main controller 3 when the voltage of the accumulated integrated charge is greater than a second voltage threshold. The main controller 3 then starts the ADC2 to measure the accumulated integrated charge.

[0058] In practical applications, the fast current measurement channel (response current fast measurement circuit) can be turned off to save power and reduce the sampling rate of the accumulated charge measurement channel (integrating charge measurement circuit). However, the device cannot respond in time when the measurement environment changes rapidly. Therefore, this application adds a comparator to both the fast current measurement channel and the accumulated charge measurement channel.

[0059] Specifically, a comparator is added to the fast current channel. When the ambient dose changes and the voltage change of the fast current output channel exceeds a threshold, the comparator triggers an interrupt in the main controller 3, which then activates ADC2 and performs measurement. Similarly, the cumulative dose channel, in most cases, only needs to be activated periodically for measurement and then deactivated. When there is an ambient dose change, measurement can be activated quickly. The addition of the first and second comparators can coordinate the operating states of the fast current measurement channel (response current fast measurement circuit) and the cumulative charge measurement channel (integrating charge measurement circuit), greatly reducing overall power consumption.

[0060] Furthermore, the electronic personal dosimeter applied to the medical interventional pulsed radiation field also includes: an alarm module 5.

[0061] The alarm module 5 is connected to the GPIO terminal of the main controller 3; the alarm module 5 is used to trigger an alarm when the instantaneous response current or accumulated integrated charge exceeds the limit; the alarm forms include at least: sound, light and vibration.

[0062] Furthermore, the electronic personal dosimeter applied to the medical interventional pulsed radiation field also includes: a temperature measurement circuit 6; the temperature measurement circuit 6 is disposed within the medical interventional pulsed radiation field.

[0063] The temperature measurement circuit 6 is connected to the I2C terminal of the main controller 3; the temperature measurement circuit 6 is used to monitor the ambient temperature of the medical interventional pulse radiation field and transmit the ambient temperature to the main controller 3, and the main controller 3 adjusts the high voltage output to perform temperature compensation on the instantaneous-cumulative dual-channel detector 1.

[0064] Furthermore, the model number of the ADC2 is ADS131M02.

[0065] In practical applications, such as Figure 10 As shown, the ADS131M02 is a dual-channel, synchronous sampling, 24-bit, 64kSPS sampling rate, Δ-Σ analog-to-digital converter (ADC2) with wide dynamic range and low power consumption. It operates from 2.7V to 3.6V, and consumes only 2.3mW under 3VA VDD and DVDD conditions. It is packaged in a 20-pin WQFN package with a package size of 3... 3mm, temperature range 40°C to +125°C.

[0066] In practical applications, the dosimeter also includes the following components: 1) High-voltage regulation circuit: such as Figure 11 As shown, the main controller 3 regulates the high voltage via a DAC. The boost voltage to the detector bias power supply is a TPS61040DRVR chip. This chip has an input voltage range of 1.8~6V, a maximum output of 28V, a voltage doubler output of 56V, a quiescent current of 28uA, and is packaged in a WSON package with a package size of 2. 2mm.

[0067] The high-voltage circuit provides a stable high-voltage power supply for the detector. The temperature measurement module monitors the system temperature in real time and transmits the temperature information to the main controller 3. The main controller 3 adjusts the high-voltage output to achieve temperature compensation for the detector.

[0068] 2) External Flash: Used to store dose data, configuration parameters, etc.

[0069] 3) RTC (Real-Time Clock): Used for data timestamps and timed tasks.

[0070] 4) Charging communication interface: used for charging and wired communication.

[0071] 5) Input wake-up: Used for wired communication to wake up the device when it is powered off.

[0072] 6) Power management: including battery charging, power measurement, multiple voltage outputs and low power management.

[0073] 7) Communication module interface: A communication module interface is reserved.

[0074] 8) Key input: Used for device operation and parameter setting.

[0075] The technical effects of this application are as follows: This application employs a dual-channel structure combining a real-time instantaneous response current measurement channel and a cumulative charge measurement channel. The real-time measurement channel, through rapid current conversion, is specifically designed for rapid measurement in high-dose, short-duration pulsed radiation fields, solving the problem of dose underestimation or alarm failure caused by the saturation of traditional electronic personal dosimeters under pulsed fields. The cumulative charge measurement channel can measure cumulative charge over a wide dose rate range, including the background, ensuring accurate and effective measurement of cumulative dose in low-dose environments. This dual-channel design achieves both rapid dose rate alarm and high-precision cumulative dose measurement within a compact size. The dual-channel design, combined with the STM32L476 microcontroller, further reduces the overall power consumption of the dosimeter, improves its portability and environmental adaptability in medical interventional pulsed radiation fields, and reduces the production cost of the dosimeter.

[0076] The various embodiments in this specification are described in a progressive manner, with each embodiment focusing on the differences from other embodiments. The same or similar parts between the various embodiments can be referred to each other.

[0077] This document uses specific examples to illustrate the principles and implementation methods of this application. The descriptions of the above embodiments are only for the purpose of helping to understand the methods and core ideas of this application. Furthermore, those skilled in the art will recognize that, based on the ideas of this application, there will be changes in the specific implementation methods and application scope. Therefore, the content of this specification should not be construed as a limitation of this application.

Claims

1. An electronic personal dosimeter applied to a medical intervention pulsed radiation field, characterized in that, The application relates to an electronic personal dosimeter applied to a medical intervention pulse radiation field, which comprises a transient-cumulative dual-channel detector, an ADC, a main controller and a segment code screen. The transient-cumulative dual-channel detector is arranged in the medical intervention pulse radiation field, and an output end of the transient-cumulative dual-channel detector is connected with an analog input end of the ADC; the transient-cumulative dual-channel detector is used for simultaneously collecting a transient response current and a cumulative integrated charge of the medical intervention pulse radiation field. A digital output end of the ADC is connected with an SPI end of the main controller; the ADC is used for converting the analog transient response current and the cumulative integrated charge into digital quantities; and the main controller is an STM32L476 ultra-low power microcontroller. An LCD end of the main controller is connected with the segment code screen; and the main controller is used for converting the transient response current and the cumulative integrated charge into a radiation dose rate and a radiation cumulative dose respectively based on scaling, and transmitting the radiation dose rate and the radiation cumulative dose to the segment code screen for real-time display.

2. The electronic personal dosimeter for use in medical interventional pulsed radiation fields according to claim 1, characterized in that, The transient-cumulative dual-channel detector specifically comprises a response current rapid measurement circuit and an integrated charge measurement circuit. The response current rapid measurement circuit is used for measuring the transient response current of the medical intervention pulse radiation field. The integrated charge measurement circuit is used for measuring the cumulative integrated charge of the medical intervention pulse radiation field.

3. The electronic personal dosimeter for use in medical interventional pulsed radiation fields according to claim 2, characterized in that, The electronic personal dosimeter applied to the medical intervention pulse radiation field further comprises a first comparator and a second comparator. A same-phase input end of the first comparator is connected with an output end of the response current rapid measurement circuit, an opposite-phase input end of the first comparator is connected with a DAC output port of the main controller, and an output end of the first comparator is connected with an analog input end of the ADC; the first comparator is used for triggering the main controller to interrupt when the voltage of the transient response current is greater than a first voltage threshold value, and starting the ADC through the main controller to measure the transient response current; A same-phase input end of the second comparator is connected with an output end of the integrated charge measurement circuit, an opposite-phase input end of the second comparator is connected with a DAC output port of the main controller, and an output end of the second comparator is connected with an analog input end of the ADC; the second comparator is used for triggering the main controller to interrupt when the voltage of the cumulative integrated charge is greater than a second voltage threshold value, and starting the ADC through the main controller to measure the cumulative integrated charge.

4. The electronic personal dosimeter for use in medical interventional pulsed radiation fields according to claim 2, characterized in that, The response current rapid measurement circuit at least comprises a single-chip logarithmic detector; and the single-chip logarithmic detector is of a model ADL5303.

5. The electronic personal dosimeter for use in medical interventional pulsed radiation fields according to claim 2, characterized in that, The integrated charge measurement circuit at least comprises a switch integration trans-impedance amplifier; and the switch integration trans-impedance amplifier is of a model IVC102.

6. The electronic personal dosimeter for use in medical interventional pulsed radiation fields according to claim 1, characterized in that, The electronic personal dosimeter applied to the medical intervention pulse radiation field further comprises an alarm module. The alarm module is connected with a GPIO end of the main controller; the alarm module is used for triggering an alarm when the radiation dose rate and the radiation cumulative dose are over-limited; and the alarm at least includes sound, light and vibration.

7. The electronic personal dosimeter for use in medical interventional pulsed radiation fields according to claim 1, characterized in that, The application further relates to an electronic personal dosimeter applied to a medical intervention pulsed radiation field. The temperature measuring circuit is connected with an I2C end of the main controller, and is used for monitoring the environmental temperature of the medical intervention pulsed radiation field and transmitting the environmental temperature to the main controller, so that the high-voltage output is adjusted by the main controller to perform temperature compensation on the instantaneous-accumulation dual-channel detector.

8. The electronic personal dosimeter for use in medical interventional pulsed radiation fields according to claim 1, characterized in that, The detector is a silicon PIN detector.

9. The electronic personal dosimeter for use in medical interventional pulsed radiation fields according to claim 1, characterized in that, The detector is packaged in a ceramic tube shell LCC10 package.

10. The electronic personal dosimeter for use in medical interventional pulsed radiation fields according to claim 1, characterized in that, The model of the ADC is ADS131M02.

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