CT imaging system

Abstract

The utility model provides a CT (Computed Tomography) imaging system, which comprises an X-ray source, a power supply, sensor modules, a level logic module, a microcontroller module, a driving module and a relay module, the sensor modules detect X-ray intensity and convert the X-ray intensity into electric signals, level signals are output after comparison, and the level logic module receives the signals of the sensor modules and transmits the signals to the microcontroller module. All the sensor modules output high levels to the microcontroller module when outputting low levels, the microcontroller module drives the driving module after receiving high level signals, and then the relay module controls the X-ray source to supply power, the system monitors the X-ray intensity in real time and accurately controls the X-ray source to work in a stable state, the imaging quality is effectively improved, and the system is suitable for large-scale popularization and application. Accurate and clear image data are provided for medical diagnosis, and the problem that the imaging quality is affected due to the fact that the output intensity of an X-ray source in a traditional CT imaging system is unstable is solved.

Description

Technical Field

[0001] This utility model relates to the field of image processing technology, specifically a CT imaging system. Background Technology

[0002] Computed tomography (CT) technology has become an indispensable diagnostic tool in clinical medicine. It uses X-rays to obtain tomographic images of the human body, which can intuitively present the structure of various tissues and organs, providing doctors with detailed information to help in the early detection of diseases and the formulation of treatment plans. It is widely used in fields such as tumor detection, diagnosis of cardiovascular and cerebrovascular diseases, and fracture analysis. The stability and reliability of the X-ray source play a crucial role in this process.

[0003] Traditional CT imaging systems typically rely on simple power control methods to supply X-ray sources. However, due to power fluctuations, component aging, and other reasons, the output intensity of the X-ray source may become unstable, directly affecting image quality, diagnostic results, and patient safety. In the prior art, CN118921824A discloses a control system for an X-ray source. Its control module is electrically connected to a high-voltage circuit module and an X-ray source module, providing drive signals to both modules and receiving several sampled signals from them for monitoring their operational status and feedback control. This method requires high precision in manufacturing processes and assembly, and the high-voltage circuit module poses a significant safety risk. Therefore, it is essential to provide a novel CT imaging system capable of real-time monitoring and intelligent control of the X-ray source. Utility Model Content

[0004] The purpose of this invention is to provide a CT imaging system to solve the problems mentioned in the background art.

[0005] To achieve the above objectives, this utility model provides the following technical solution:

[0006] A CT imaging system includes an X-ray source electrically connected to a power supply for generating and emitting an X-ray beam that penetrates the object being scanned, and further includes:

[0007] Sensor module: The sensor module is electrically connected to the level logic module and is used to convert weak light signals into electrical signals and output level signals after comparison;

[0008] Level logic module: The level logic module is electrically connected to the microcontroller module and is used to receive the output signals of each sensor module. When all sensor modules output low-level signals, it outputs a high-level signal.

[0009] Microcontroller module: The microcontroller module is electrically connected to the driver module and is used to receive signals from the level logic module and control the driver module according to its output;

[0010] Drive module: The drive module is electrically connected to the relay module and is used to receive drive signals from the microcontroller module to drive the relay module to perform actions;

[0011] Relay module: The relay module is connected in series in the power supply circuit between the X-ray source and the power supply, and is used to control the power supply of the X-ray source;

[0012] Power supply: The power supply is electrically connected to the X-ray source and is used to provide the working power for the X-ray source.

[0013] Furthermore, the sensor module is provided in multiple groups, each group including two sensor units and a voltage comparator. The sensor units are located at the emission position of the X-ray source and are used to detect the intensity of the X-rays emitted by the X-ray source and convert it into an electrical signal. The sensor units and the input terminal of the voltage comparator are electrically connected. The voltage comparator is used to emit a low-level signal when the output voltages of the two sensor units are consistent.

[0014] Furthermore, the sensor unit includes a photodiode, a preamplifier circuit, and a second-order bandpass filter circuit. The photodiode and the preamplifier circuit are electrically connected to convert the optical signal into a current signal. The preamplifier circuit includes an operational amplifier A1 and corresponding matching resistors R2 and R3. The output terminal of the operational amplifier A1 is the input terminal of the second-order bandpass filter circuit. The second-order bandpass filter circuit includes operational amplifiers A2 and A3, corresponding matching resistors R4, R5, R6, R7, R8, R9, R10, R11, and capacitors C1, C2, C3, and C4. Resistors R4, R5, R6, and capacitor C2 are connected between the two input terminals of the operational amplifier A2, and resistors R8, R9, and capacitors C3 and C4 are connected between the output terminal and the operational amplifier A3. The output terminal of the operational amplifier A3 is electrically connected to the input terminal of a voltage comparator to output a voltage signal with most of the noise filtered out to the voltage comparator.

[0015] Furthermore, the voltage comparator is used to output a low-level signal when the voltage signals at the non-inverting input terminal IN1+ and the inverting input terminal IN1- are the same, and to output a high-level signal when the voltage signals at the non-inverting input terminal IN1+ and the inverting input terminal IN1- are different.

[0016] Furthermore, the level logic module is a basic NOR gate circuit. Two PMOS transistors, T1 and T3, are connected in series. Their sources are electrically connected to the power supply Vdd, and their drains are electrically connected to the output terminal Y. The gate of PMOS transistor T1 is electrically connected to the input terminal A, and the gate of PMOS transistor T3 is electrically connected to the input terminal B. Two NMOS transistors, T2 and T4, are connected in parallel. Their sources are grounded, and their drains are electrically connected to the output terminal Y. The gate of NMOS transistor T2 is electrically connected to the input terminal A, and the gate of NMOS transistor T4 is electrically connected to the input terminal B. The output terminal Y is electrically connected to the drains of both the PMOS and NMOS transistors. Utilizing the inverting amplification characteristic of the transistors, when both input terminals A and B are low, the output terminal Y is high; when both input terminals A and B are high, the output terminal Y is low. The output terminal Y is electrically connected to the microcontroller module and is used to output level signals.

[0017] Furthermore, the driving module includes an NPN transistor Q1, a diode D1, and corresponding matching resistors R12, R13, and R14. The coil of the relay module is electrically connected to the driving module, and the contacts of the relay module are electrically connected to the X-ray source and the power supply for controlling the switch. A resistor R12 is connected between the NPN transistor Q1 and the output terminal of the microcontroller module for controlling the relay coil to be energized. The diode D1 is used for reverse freewheeling to provide a discharge path for the relay coil when the NPN transistor Q1 switches from conducting to turning off.

[0018] Compared with the prior art, the beneficial effects of this utility model are:

[0019] This invention sets up multiple sensor modules at the X-ray source emission position. Two sensor units in each module detect X-ray intensity and convert it into an electrical signal. A voltage comparator then determines whether to emit a low-level signal based on whether the output voltages of the two sensor units are consistent. Only when the voltage comparators of all sensor modules output low-level signals does the logic module output a high-level signal to the microcontroller module. This, in turn, controls the power supply to the X-ray source through subsequent drive and relay modules. This design ensures that the power supply control of the X-ray source is closely related to the stability of the X-ray intensity, allowing power to be supplied only when the X-ray intensity reaches a specific stable state. This more precisely ensures that the X-ray source operates under suitable conditions, improving imaging quality. Attached Figure Description

[0020] Figure 1 This is the overall system structure of this utility model;

[0021] Figure 2 This is a schematic diagram of the sensor module structure in this utility model;

[0022] Figure 3This is a circuit diagram of the sensor module in this utility model;

[0023] Figure 4 This is a circuit diagram of the level logic module in this utility model;

[0024] Figure 5 This is a circuit diagram of the drive module and relay module in this utility model.

[0025] In the diagram: 10 X-ray source, 20 sensor module, 21 sensor unit, 22 voltage comparison unit, 30 level logic module, 40 microcontroller module, 50 driver module, 60 relay module, 70 power supply. Detailed Implementation

[0026] The technical solutions of the present utility model will be clearly and completely described below with reference to the accompanying drawings of the embodiments. Obviously, the described embodiments are only some embodiments of the present utility model, and not all embodiments. Based on the embodiments of the present utility model, all other embodiments obtained by those of ordinary skill in the art without creative effort are within the protection scope of the present utility model.

[0027] Example:

[0028] Please see Figures 1 to 5 This utility model provides a technical solution:

[0029] A CT imaging system includes an X-ray source 10, a sensor module 20, a sensor unit 21, a voltage comparison unit 22, a level logic module 30, a microcontroller module 40, a drive module 50, a relay module 60, and a power supply 70, wherein:

[0030] The X-ray source 10 is electrically connected to the power supply 70, which provides the X-ray source 10 with the electrical energy required for its operation. The X-ray source 10 is responsible for generating and emitting an X-ray beam, which is used to penetrate the object being scanned.

[0031] The sensor module 20 is configured with multiple groups, each group containing two sensor units 21 and a voltage comparator 22. The sensor units 21 are located at the emission position of the X-ray source 10. Their internal photodiodes convert the received X-ray light signal into a current signal. The photodiodes are SA88010RS22-J00 silicon PIN photodiodes with high speed and high sensitivity, packaged in a transparent optical SMD2015 package. The signal is then amplified by a preamplifier circuit consisting of operational amplifier A1 and matching resistors R2 and R3. The amplified signal is then input to the operational amplifier... The second-order bandpass filter circuit, consisting of amplifiers A2 and A3, resistors R4, R5, R6, R7, R8, R9, R10, R11, and capacitors C1, C2, C3, and C4, filters out most of the noise. The operational amplifiers A1, A2, and A3 used in the preamplifier circuit and the second-order bandpass filter circuit are all LM6211. Finally, the processed voltage signal is output to voltage comparator 22, which is an LM393. Voltage comparator 22 outputs a low-level signal when the output voltages of the two sensor units 21 are the same, and a high-level signal when they are different.

[0032] The level logic module 30 adopts a basic NOR gate circuit, consisting of two series-connected PMOS transistors T1 and T3 and two parallel-connected NMOS transistors T2 and T4. The sources of PMOS transistors T1 and T3 are connected to the power supply Vdd, their drains are connected to the output terminal Y, and their gates are connected to input terminals A and B, respectively. The sources of NMOS transistors T2 and T4 are grounded, their drains are connected to the output terminal Y, and their gates are also connected to input terminals A and B, respectively. The PMOS transistors conduct when the gate voltage is lower than the source voltage, and the NMOS transistors conduct when the gate voltage is higher than the source voltage. When the input terminal... When both A and B are low, the gate voltages of PMOS transistors T1 and T3 are lower than the source voltage Vdd, so T1 and T3 are turned on. The gate voltages of NMOS transistors T2 and T4 are lower than the source voltages, so T2 and T4 are turned off. The output terminal Y outputs a high-level signal to the microcontroller module 40. When the input terminals A and B are high, the gate voltages of PMOS transistors T1 and T3 are close to Vdd, so T1 and T3 are turned off. The gate voltages of NMOS transistors T2 and T4 are higher than the source voltages, so T2 and T4 are turned on. The output terminal Y outputs a low-level signal.

[0033] The microcontroller module 40 is electrically connected to the output of the level logic module 30. The STM32F407 microcontroller module is based on a Cortex-M4 core and uses pipeline technology to quickly process data and instructions. In the CT imaging system, it responds to the level logic module signals in a timely manner and controls the drive module 50. Its flash memory stores the program code, and SRAM is used for data temporary storage to ensure the continuity of data processing. It communicates with external devices through interfaces such as GPIO, SPI, I2C, and USART to facilitate system monitoring. The microcontroller module 40 receives the level signals output by the level logic module 30. When it receives a high-level signal, it sends a drive signal to the drive module 50.

[0034] The driving module 50 includes an NPN transistor Q1, a diode D1, and matching resistors R12, R13, and R14. The NPN transistor used is a PN2222. The base of the NPN transistor Q1 is connected to the output terminal of the microcontroller module 40 through resistor R12 to control the relay coil to be energized. The diode D1 is used for reverse freewheeling. When the NPN transistor Q1 changes from being on to being off, it provides a discharge path for the relay coil. After receiving the driving signal from the microcontroller module 40, the driving module 50 drives the relay module 60 to operate.

[0035] The relay module 60 is connected in series in the power supply circuit between the X-ray source 10 and the power supply 70. The relay module adopts a G6D-1174P-US-DC24 relay, which has a single-pole double-throw contact configuration. Its coil is electrically connected to the drive module 50, and its contacts are electrically connected to the X-ray source 10 and the power supply 70. The power supply to the X-ray source 10 is controlled by a control switch.

[0036] The working principle of this utility model:

[0037] After the system starts up, the sensor unit 21 in the sensor module 20 begins to detect the intensity of X-rays emitted by the X-ray source 10 in real time and continuously, and converts it into an electrical signal. The voltage comparator 22 in each group of sensor modules 20 continuously compares the voltages output by the two sensor units 21. If the X-ray intensity detected at each position is stable and consistent, the voltage comparators 22 of all sensor modules 20 output a low-level signal. The level logic module 30 receives the low-level signals from all sensor modules 20 and outputs a high-level signal to the microcontroller module 40 according to its logic circuit characteristics.

[0038] After receiving a high-level signal, the microcontroller module 40 confirms that the X-ray intensity is stable and immediately sends a drive signal to the drive module 50. The NPN transistor Q1 in the drive module 50 conducts after receiving the drive signal, which energizes the coil of the relay module 60 and closes the relay contacts, thereby connecting the power supply circuit between the X-ray source 10 and the power supply 70. The X-ray source 10 starts to work and emits an X-ray beam to scan the object being scanned.

[0039] During the operation of the X-ray source 10, if any set of sensor modules 20 detects a change in X-ray intensity, causing its internal voltage comparator 22 to output a high-level signal, the level logic module 30 will immediately change its output state upon receiving the high-level signal and output a low-level signal to the microcontroller module 40. Upon receiving the low-level signal, the microcontroller module 40 will determine that the X-ray intensity is unstable and will quickly send a control signal to the drive module 50, causing the NPN transistor Q1 to be cut off, the coil of the relay module 60 to be de-energized, the contacts to open, and the power supply circuit between the X-ray source 10 and the power supply 70 to be cut off, thus stopping the X-ray source 10 from working.

[0040] Through this real-time monitoring and precise control mechanism, this CT imaging system can ensure that the X-ray source 10 always operates under a stable X-ray intensity, thereby effectively improving imaging quality and providing more accurate and clearer image data for medical diagnosis.

[0041] Although embodiments of the present invention have been shown and described, it will be understood by those skilled in the art that various changes, modifications, substitutions and alterations can be made to these embodiments without departing from the principles and spirit of the present invention, the scope of which is defined by the appended claims and their equivalents.

Claims

1. A CT imaging system, characterized in that, The system includes an X-ray source (10) and a power supply (70), which are electrically connected to the X-ray source (10) to provide power for the operation of the X-ray source (10). It also includes: The sensor module (20) is provided in multiple groups, each group including two sensor units (21) and a voltage comparator (22). The sensor unit (21) is set at the emission position of the X-ray source (10) and is used to detect the intensity of X-rays emitted by the X-ray source (10) and convert it into an electrical signal. The input terminals of the sensor unit (21) and the voltage comparator (22) are electrically connected. The voltage comparator (22) is used to emit a low-level signal when the output voltages of the two sensor units (21) are consistent. The level logic module (30) is electrically connected to the output of the voltage comparator (22) inside each sensor module (20), and its output is electrically connected to the microcontroller module (40). It is used to output a high-level signal to the microcontroller module (40) when each voltage comparator (22) outputs a low-level signal. The microcontroller module (40) is electrically connected to the input of the driver module (50) and is used to send a drive signal to the driver module (50) when it receives a high-level signal output by the level logic module (30). The output terminal of the drive module (50) is electrically connected to the input terminal of the relay module (60), and is used to drive the relay module (60) to perform an action when a drive signal is received from the microcontroller module (40); A relay module (60) is connected in series in the power supply circuit between the X-ray source (10) and the power supply (70) to control the power supply of the X-ray source (10).

2. The CT imaging system according to claim 1, characterized in that: The sensor unit (21) includes a photodiode, a preamplifier circuit, and a second-order bandpass filter circuit; The photodiode and the preamplifier circuit are electrically connected to convert the optical signal into a current signal. The preamplifier circuit includes an operational amplifier A1 and corresponding matching resistors R2 and R3. The output terminal of the operational amplifier A1 is the input terminal of a second-order bandpass filter circuit. The second-order bandpass filter circuit includes operational amplifiers A2 and A3, corresponding matching resistors R4, R5, R6, R7, R8, R9, R10, R11, and capacitors C1, C2, C3, and C4. Resistors R4, R5, R6, and capacitor C2 are connected between the two input terminals of the operational amplifier A2, and resistors R8, R9, and capacitors C3 and C4 are connected between the output terminal and the operational amplifier A3. The output terminal of the operational amplifier A3 is electrically connected to the input terminal of the voltage comparator (22) to output a voltage signal with most of the noise filtered out to the voltage comparator (22). The voltage comparator (22) outputs a low-level signal when the voltage signals of the non-inverting input terminal IN1+ and the inverting input terminal IN1- are the same, and outputs a high-level signal when the voltage signals of the non-inverting input terminal IN1+ and the inverting input terminal IN1- are different.

3. A CT imaging system according to claim 1, characterized in that: The level logic module (30) is a basic NOR gate circuit. Two PMOS transistors T1 and T3 are connected in series. Their sources are electrically connected to the power supply Vdd, and their drains are electrically connected to the output terminal Y. The gate of PMOS transistor T1 is electrically connected to the input terminal A, and the gate of PMOS transistor T3 is electrically connected to the input terminal B. Two NMOS transistors T2 and T4 are connected in parallel. Their sources are grounded, and their drains are electrically connected to the output terminal Y. The gate of NMOS transistor T2 is electrically connected to the input terminal A, and the gate of NMOS transistor T4 is electrically connected to the input terminal B. The output terminal Y is electrically connected to the drains of the PMOS transistor and the NMOS transistor. Utilizing the inverting amplification characteristics of the transistor, when both input terminals A and B are low, the output terminal Y is high, and when both input terminals A and B are high, the output terminal Y is low. The output terminal Y is electrically connected to the microcontroller module (40) and is used to output level signals.

4. A CT imaging system according to claim 1, characterized in that: The drive module (50) includes an NPN transistor Q1, a diode D1 and corresponding matching resistors R12, R13 and R14. The coil of the relay module (60) is electrically connected to the drive module (50), and the contacts of the relay module (60) are electrically connected to the X-ray source (10) and the power supply (70) for controlling the switch. A resistor R12 is connected between the NPN transistor Q1 and the output terminal of the microcontroller module (40) to control the relay coil to be energized. The diode D1 is used for reverse freewheeling to provide a discharge path for the relay coil when the NPN transistor Q1 switches from being on to being off.

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