KR20060020778A - The x-ray radiograpy & fluoroscopy system which has aec(auto exposure control) & apr(anatomical programming)function by mcu(micro control unit)processor - Google Patents

Abstract

In the present invention, the microprocessor (MCU) is adopted to automatically set the necessary parametors for the patient based on clinical data obtained through numerous experiments in advance, thereby easily adjusting the amount of X-ray automatically according to the patient's condition. By implementing the APR function that can be automatically adjusted to shoot the optimal X-Ray amount according to the patient, implemented to control the unnecessary X-Ray amount, and in the present invention sufficient image quality even with the minimum X-Ray amount AEC (Auto Exposure Control) and ABC (Auto Brightness Control) functions are implemented to improve the performance of the X-ray shooting / vision system. The AEC function terminates the exposure of X-Ray when the required amount of X-Ray is exposed on the X-Ray film. The AEC function prevents the patient from being exposed to unnecessary X-Ray. It will automatically adjust to a level that satisfies. The APR function automatically monitors the clinical data obtained from existing clinical trials to determine the extent of X-Ray exposure, depending on the patient's situation, for example, adults and children, fat and skinny, tall or short patients. By setting it automatically, it provides convenience for the use of doctor or radiologist, and at the same time, the patient can take X-ray in the best condition. In addition, the patient has been exposed to a large amount of unnecessary X-Ray for a long time because the patient uses a 60-Hz sign wave so that the patient can fit only the minimum amount of X-Ray, but the Invertor (Fig. 2) C-1) By generating X-Ray with High Frequecny (30-40Khz), High Frequency Generator is implemented so that the patient can get high quality image while being exposed to minimum X-Ray amount in the shortest time. In addition, in the present invention, a) high voltage transformer and b) back pressure circuit and c) change box of FIG. 12 are designed to be improved in the same package. This operation requires special manufacturing know-how. This is also an important element of the present invention. In addition, in the prior art, the AEC (automatic exposure adjustment) function cannot be performed using the car ion chamber 1 and the other ion chamber 2 of FIG. 1, but in the present invention, AEC and automatic ABC function that can adjust the brightness is implemented, and the existing X-ray camera and seeing function is analog in view of the present invention, in this design, the analog signal entering the b) TV Monitor of FIG. Micro process that implements application program that can convert and convert digital signal to digital signal that can be displayed in workstation and save digitized image signal on PC hard disk through D converter and manage image data for each patient. It is the invention of intelligent X-ray shooting / projection that implements automatic exposure control (AEC) and APR function using MCU).

X-Ray Capture / Perspective System using High Frequency Generator with APR, AEC, ABC

Description

The X-Ray Radiograpy & Fluoroscopy System which has AEC (Auto Exposure Control) & APR (Anatomical Programming) that implements AEC and APR functions using a micro process (MCU) function by Micro Control Unit (MCU)

1): Block Diagram of Main Control System

Fig. 2) X-ray shooting / spreading full explanatory diagram

Fig. 3: X-ray camera flow and step-by-step waveform diagram

4): Induction of current in a transformer

5): high voltage circuit

Fig. 6: Filament Circuit

7): Space charge compensator

Fig. 8: Circuit separating exposure start and end switch

Fig. 9: Theoretical X-ray tube rating table at tube voltage 70kVp

10): Continuous exposure table of AEC

Fig. 11: Part of the conventional high pressure generation

Fig. 12: Partial View of Current High Pressure Generation

Fig. 13: Output voltage waveform diagram of rectifier

14): Block diagram of Display & Key Input Sub-System

15): Main Control System Mode

Figure 16): kVp Control System

Figure 17: mA Control System

Figure 18: Block Diagram of kV Control Sub System

19): Block Diagram of Control Sub System

20): Block Diagram of Calibration System

Fig. 21) Block Diagram of Anatomic Program Sub System

Fig. 22) Block Diagram of Error Check System

The technical field of the present invention is a medical equipment, X-RAY imaging and viewing device using X-RAY for imaging the patient's condition in a hospital, The X-Ray Radiography / Fluoroscopy System has caused a lot of inconvenience because the radiologist randomly set the data necessary for X-Ray imaging manually without using a microprocess. It also has an automatic exposure control (AEC) function or ABC (automatic brightness). Because there is no APR function that makes it easy to select the X-ray amount according to the patient's condition based on the data obtained in advance, the measurement error may occur depending on the patient because accurate adjustment could not be made due to the random selection of the radiation source. Unnecessary X-Ray penetration could damage the patient. Also, in the conventional high pressure generating part of FIG. 11, a) the high voltage transformer and b) the back pressure circuit are built in the same package, but the c) change box of FIG. 11) has a separate package, A separate cable was required, and in order to supply the high pressure between the tube (1) and the tube (2) of Fig. 1), according to the transfer command of the microprocessor (MCU) in the b) Control cosole of Fig. 1). 11) c) Since the high pressure must be transferred in the change box, there was a point of anxiety in the patient due to the noisy noise caused by this.

Conventional The X-Ray Radiography / Fluoroscopy System has a lot of inconveniences because the radiologist arbitrarily sets the data necessary for X-ray imaging manually without using a microprocess, and the patient cannot be precisely adjusted due to the random selection of the radiologist. In some cases, measurement errors may occur, and unnecessary X-rays may cause damage to patients or radiologists. In view of the above, the present invention provides a technical problem to solve the conventional problems by employing a microprocessor (MCU) to enable automatic setting for a patient based on data obtained through a number of experiments in advance. In addition, the present invention provides a technical problem for embedding AEC (automatic exposure control device), ABC (automatic brightness control device) and APR (Aatomic Programming) functions as a method for improving the performance of the X-Ray generator. The AEC function terminates the exposure of X-Ray when the required amount of X-Ray is exposed on the X-Ray film. The AEC function prevents the patient from being exposed to unnecessary X-Ray. It will automatically adjust to a level that satisfies. The APR function automatically monitors the clinical data obtained from existing clinical trials to determine the extent of X-Ray exposure, depending on the patient's situation, for example, adults and children, fat and skinny, tall or short patients. By setting it automatically, the technical task of providing the convenience of the doctor or radiologist and allowing the patient to take X-rays in the best condition, and also the patient can meet the minimum amount of X-Ray Conventionally, the patient has been exposed to a large amount of unnecessary X-Ray for a long time to obtain the necessary image by using 60Hz sign wave, but the patient is shortest by generating X-Ray with High Frequecny (30-40Khz) using Invertor. The technical challenge of ensuring good image quality while being exposed to the minimum amount of X-Ray in time, and also the existing X-Ray filming and seeing functions In view of the analog point, in the present invention, by converting and converting the digital signal into a digital signal, it is possible to store and print on the hard disk of a PC, so that each patient can easily manage the image data and send it to a remote place to obtain a doctor at a place. The technical challenge was to solve the patient without receiving it.

The block diagram of the main control system of FIG. 1 shows a part that controls the overall operation to be described in the present patent, and the software program is designed to be manufactured using a microprocessor.

All operation of this system is operated by using CPU input / output port and internal / external peripherals. 1)-A) Display & Key Input System, b) kV Control System, c) mA Control System, e) Calibration System, F) Anatomic Program Subsystem, External I / O Control System, H) Error Check It consists of a system, and all these operations are controlled and monitored by the Main Control System. 2) The overall X-ray photographing / perspective diagram is a block diagram presented for the overall description of this paper. C) High frequency X-ray generator and a) LCD display, b) control console, d) high voltage transformer, e) back pressure circuit bar, c) change box and x-ray shooting. Tube (1) and Tea) Ion chamber (1) and for viewing purposes) Tube (2) and other) Ion chamber (2) and lower) Film cassette, Far) Grid and car) Image Intensifier And image detector (CCD), b) TV-Monitor are necessary components. C) High frequency X-ray generator is C-1) rectifier, C-2) high voltage adjusting circuit and inverter, c) filament adjusting circuit. -4) It consists of Timer. In addition, in consideration of the fact that the existing X-ray camera and the projection function are analog, in the present invention, the analog signal entering the b) TV monitor of FIG. 2) is displayed through the A / D converter of FIG. 2). It is possible to save and print the converted digital signal and digitalized image signal on the hard disk of PC, and have devised an application program that can manage the image data for each patient.

The X-ray generator of Figure 2) is an important component for carrying out the present design, which supplies electrical energy to the X-ray tube and controls the exposure time. The X-ray tube requires two kinds of power sources, one for heating the filament, which is supplied from the multi-filament control circuit of Fig. 1), and the other is the anode of the X-ray tube for accelerating electrons. It is designed to supply the power between the cathode and the cathode. 3) The filament adjusting circuit of FIG. 1 includes a variable resistor and a step down transformer for adjusting current, and the 2-2 high voltage adjusting circuit and an inverter of FIG. 1) are step-up transformers. Transformer) and Invertor are required, and these designs are designed like Figure 4) High voltage circuit and Figure 5) Filament circuit. C) The input of the high frequency X-ray generator of Fig. 1) is an alternating current, so the alternating current is converted to direct current through the rectifier. In other words, the X-ray generator is always 110-220Volts, 60Hz or 380-440Volts, 50Hz through the a) AC power circuit of Fig. 2) as shown in Fig. 2) X-Ray imaging / transmission flow and step-by-step waveform diagram. AC current power is necessary, and this is converted into DC through b) DC rectifier circuit in Fig. 2) and c) Invertor circuit in Fig. 3 to generate high voltage. D) High voltage is supplied to the X-ray tube through the high voltage transformer and e) transformer circuit of Fig. 3), which provides electrical energy to accelerate the generated electrons from the cathode to the anode. In order to show this step, we need to show the flow of steps, and the waveforms that change in each step. In addition, as a third circuit, there is a circuit of Fig. 2) -4) Timer which determines the exposure time. These three circuits are closely related to each other and will be described separately. X-Ray generator is composed of b) Control Console of Fig. 2) and c) High-frequency X-ray generator and high voltage transformer of Fig. 2).

And a back pressure circuit.

2) b) Cotrol Console to select the technical elements of the radiation dose and see-through dose, and serves to initialize the radiation of the X-Ray. C) The high frequency X-ray generator of Fig. 2) d) the high voltage transformer and c) the rectifiers and c-2) the high pressure regulating circuit and inverter and the c) filament adjusting circuit and the d- 4) It can be composed of 4 main circuits of Timer, and by their operation, it provides voltage, current, time width required to generate X-Ray in X-Ray Tube. D) The high voltage transformer of FIG. 1) has a function to adjust the voltage, especially since a circuit for increasing and decreasing input AC power is provided, and when AC is input to the primary coil, voltage and current are induced to the secondary coil. The winding of the coil can be adjusted according to the number of times the input to output voltage. The relationship between these inputs and outputs is T1 / T2 = V1 / V2, where T1 = number of turns of the secondary coil, T2 = number of turns of the secondary coil, and V1 = voltage input to the secondary coil, V2 = Refers to the voltage output to the secondary coil. 2) D) The high voltage transformer refers to a transformer that increases the voltage output from the secondary side, while the current decreases, and the multi-rectifier of FIG. 2) is a direct current required for the X-ray tube. It is designed to convert alternating current to DC for direct current. C-1) rectifier of Fig. 2) has a built-in current limiting circuit to protect the filament of the X-ray tube from overcurrent. In addition, there are two methods of rectifying, one of which outputs an output waveform of a half-wave rectifier such as b) of FIG. 13 through a half-wave rectifying circuit, and the other of full-wave rectifying circuit (Full-Wave). The output wave of c) full-wave rectifier of Figure 13) is adopted by adopting Wave), which is configured so that two pairs of rectifiers operate separately, and a) by the 60 Hz AC waveform (signature wave pulse) of Figure 13). In both / negative pulses, the electrons flow from the cathode of the X-ray tube to the anode.

The most ideal secondary voltage waveform is a steady-state DC waveform having a stable smooth state without transient variation as shown in d) high frequency output waveform of Fig. 13). In the present invention, a high frequency X-ray generator using a high frequency output waveform is adopted. It was.

Advantages of the high frequency X-ray generator include: 1) the ripple factor is very low, even when supplied with single-phase power, and has a voltage waveform that is almost constant voltage, such as three-phase full-wave rectification. 2) It is possible to reduce about 35% of the patient's dose than the single phase propagation device under the same exposure conditions. 3) When the mAs of the high frequency generator are the same as the single phase propagator and the tube voltage is adjusted according to various tests, the X-ray generation rate is 60% on average. Therefore, the exposure time is relatively short when trying to obtain the same film concentration. The exposure time can also be precisely controlled by counting the high frequency of the modulator, resulting in high accuracy. 4) When the generator's kW rating is 30-50kW, the transformer is developed in a very small and light form so that the transformer can be installed in the same weight and X-ray tube of the cookie. E / f x n x A = Constant, E = transformer voltage, n = winding, f = frequency, A = cross section of iron core. In the above equation, if the frequency is increased to about 100 times (60Hz to 30,000Hz), the number of windings and the cross section of the iron core can be reduced by 500 times, which means that the cross section of the iron core can be reduced by about 500 times. The basic principle of the high frequency generator is to induce a voltage in the secondary coil proportional to the rate of change of the primary coil current of the transformer. The induced voltage is proportional to the rate of change of the magnetic flux according to Faraday's law. The high frequency generator raises the 60Hz input supply frequency to 30,000Hz before being sent to the transformer primary coil. This is called an Invertor, as seen in C-2) High Voltage Adjustment Circuit and Invertor of Fig. 1).

As shown in Figure 1, the inverter rectifies the input power 60Hz current into DC at 120Hz and smooths in step 2). The smooth DC is received by the modulator (chopper) in step 3), converted to 30,000 Hz, and sent to the primary side of the high voltage transformer in step 4). As rectification in step 5), the transformer output of high pressure 30,000Hz is rectified again to 13,000 high pressure pulses per second, smothing again in the high pressure filter in step 6), and ripple free voltage, which is called constant voltage, is sent to the X-ray tube. As a result, a constant voltage waveform can be achieved regardless of the input power supply, which does not require any special power supply or voltage stabilizer. Exposure time control can be precisely controlled by counting the high frequency of the modulator. D) components of the high voltage transformer of Figures 1) and 2) are step-down trans-formers for the filament circuit in a grounded metal box filled with oil; Up transformer) and multi-1) rectifier of Fig. 1) that converts alternating current (AC) into direct current (DC). The potential difference required for the circuit is up to 150 kVp, e) back pressure circuit in Fig. 1) and d) high voltage transformer in Fig. 1), and c) 1) rectifier in Fig. 1) in the oil that combines insulation and prevents sparking between components. Soaked. This oil is a refined common oil that is designed to act as both an insulating action and cooling the heat caused by power loss (copper loss, iron loss).

For the detailed understanding of the present invention, the operation of each component will be described. First, d) high voltage transformer of FIG. 1), the power of the X-ray generator is 110-220 volts, 60 Hz or 380-440 volts, 50 Hz AC, but the voltage required for filament heating is about 10 volts. Since the potential difference given to i) Tube (1) and C) Tube (2) for the acceleration of electrons is required 40-150 kVp, the transformer is stepped up or down to the required potential difference (voltage). If there is one point with a 10 volt negative potential and the other with a 10 volt positive potential, the potential difference between the two points is 20 volts. The flow of electrons due to the potential difference is called current, and the electrons flow toward the positive potential. As shown in FIG. 3, two conductors are wound around an iron core facing each other, and a primary coil is called a primary circuit, and a secondary coil is called a secondary circuit. When current flows in the primary coil, a magnetic field is generated in the iron core and the magnetic field is induced by the secondary coil.

Current flows By using this mutual induction phenomenon, the transformer can freely raise or lower the AC voltage. The current flows through the secondary circuit only when the magnetic field changes (increases or decreases) and no current flows while it remains stable. The high voltage circuit uses alternating current as shown in FIG. This is because the alternating current periodically changes in polarity and the potential difference (voltage) changes continuously. If the current flows in one direction when the voltage is positive, the current flows in the opposite direction when the current is negative. An important characteristic of alternating current is that the voltage changes continuously and thus the magnetic field also changes continuously, so supplying such alternating current to the primary coil of a transformer can cause the alternating current (induction current) to continue to flow in the secondary coil as well. Because. The voltage between the two circuits of the transformer is proportional to the number of turns of the two circuits. N1 / n2 = v1 / v2, where n1 = number of turns of the main circuit, n2 = number of turns of the secondary circuit, v1 = voltage of the main circuit, v2 = voltage of the secondary circuit, and secondary to the primary coil Transformers with a large number of turns of coils are called step-up transformers because the secondary voltage increases.

As it decreases, it is called a step down transformer. The current between the two circuits is also proportional to the number of turns of the two circuits. n1 / n2 = i2 / i1, where n1 = number of turns of the main circuit, n2 = number of turns of the secondary circuit, i1 = current of the main circuit, i2 = current on the secondary circuit. Since the voltages given to i) Tube (1) and c) Tube (2) in Fig. 1 are always expressed as the maximum value (kVp), to find the maximum value of the transformer secondary voltage, x1.41 is obtained. Since the transformer does not generate energy, the power of the two circuits is the same according to the law of energy conservation. Therefore, as the voltage increases, the current decreases relatively, i.e., v1i1 = v2i2. Where v1 = main circuit voltage, v2 = secondary circuit voltage, i1 = main circuit current, i2 = secondary circuit current, and if the power of the transformer is 3,000 Watts, high voltage (100v x 31A), low voltage (30,000) vx 0.1A) is the same. The high voltage control circuit and inverter of FIG. 1 accelerate the flow of electrons from the cathode of the X-ray tube to the anode by applying a specified voltage (kVp) and a waveform to the X-ray tube. It is a circuit that provides electrical force to emit X-Ray.

4 is a simplified illustration of a high-voltage circuit. In the figure, only a few terminals are drawn and illustrated, but in practice, a large number of terminals are required for each tube voltage value used in the X-ray apparatus. In this paper, there are 31 terminals in the range of 40-100 kVp in a 2kVp control unit. 3) Filament adjusting circuit and Fig. 5) Filament circuit of Fig. 1 are circuits for supplying the required voltage to provide the required tube current, and in addition to the variable resistor and step-down transformer, the space charge compensator and the filament voltage It consists of a ballast. In the filament circuit of Fig. 5), the filament in the X-ray tube is designed to emit hot electrons when heated by a coiled tungsten wire. Step-Down Transformer (Filament Heating Transformer) has a low potential difference for heating the filament, so it is about 10 volts and current is 3-5A. This is not the current flowing through the X-ray tube, but only the heating of the filament. Since the input power (120-220 volt) is higher than the filament heating voltage (10 volt) it is necessary to reduce the voltage using a step-down transformer. 5)

The filament transformer is also called a filament transformer, and the winding ratio of the primary and secondary coils is about 10: 1 and is immersed in the metal box grounded together with the high voltage transformer. In the present invention, since two filaments are used through the filament adjusting circuit of FIG. 2), two separate step-down transformers are used for each filament. The filament voltage must be designed so that it can be adjusted very precisely.

Therefore, in the present invention, it is designed to be adjusted in b) Control Console of FIG. 1). In addition, a voltage stabilization circuit is provided to compensate for a difference in current flowing through the X-ray tube according to a change in the selected voltage (kVp). Built. Even if the voltage fluctuation is small, the rate of change of the relative tube current is considerably large, so a stable voltage must be supplied. In other words, 5% of filament voltage fluctuation causes 20-30% of X-ray tube current. The filament voltage stabilizer of Fig. 6) is designed to act instantaneously and automatically, and has two input and output terminals. The output terminal is connected to the main circuit of the mA regulator and the filament transformer and stabilizes the output voltage when the input voltage changes. In addition, when shooting with high tube current, many electrons need to be emitted from the filament. The electrons are not affected by the space charge and all electrons do not move when the potential difference is given to the X-ray tube. Increasing the tube voltage causes many electrons to move from the space charge to the anode, increasing the tube current, and lowering the tube voltage also reduces the electrons traveling to the anode, resulting in less tube current.

Thus, even if a specific tube current (D) tube current regulator of FIG. 6) is selected, the current flowing through the X-ray tube may change according to the increase or decrease of the tube voltage. If the tube current is fixed at 500mA and the tube voltage is gradually increased from 50kVp to 90kVp, the amount of moving electrons decreases at 50kVp, and the filament heating temperature increases. This control device is the space charge compensator of Fig. 6). The space charge compensator is the main coil of the filament transformer and the secondary winding of the special compensation transformer is wound around the tube current regulator as shown in Fig. 6). Or sub-tractive voltage. C) Timer is a circuit for adjusting the start time and exposure time and end time of X-ray exposure, the mechanical part of the timer controls the exposure time, and the switch starts and ends. Adjust the time In this design, the X-ray timer circuit is designed to control the exposure time from 1/100 second to 10 seconds. The operating mechanism of the X-ray exposure is a timer selector of the control panel as shown in Fig. 7). After determining a specific time, pressing the first step of the exposure button in step 2 heats the filament and rotates the anode to complete the exposure preparation. do. Pressing the second stage again closes the circuit and starts exposure. After a certain time, the timer opens the circuit and ends the exposure. The actual opening and closing of the circuit is the switch, and the timer only instructs the switch to work. Sending the operating current to the two switch coils is also supplied separately from the start and end circuits to start exposure when one switch is closed and end exposure when another switch is open. The exposure start switch is an open relay and closes when the current is supplied to the coil, and the exposure end switch opens when the current is supplied as a closed relay. In this design, the main circuit is opened and closed at "0" voltage x) of sine wave of input AC power. Opening and closing the circuit at the “0” point of the AC voltage cycle can reduce arc discharge, resulting in even image quality even at very short exposure times. In the present invention, the AEC (automatic exposure control device), ABC (automatic brightness control device) and APR (Aatomic Programming) functions are built in as a method for improving the performance of the X-ray generator. The automatic exposure control device stops the exposure of X-Ray when the required amount of X-Ray is exposed on the X-Ray film. This prevents the patient from being exposed to unnecessary X-Ray and improves image quality. It is automatically adjusted to the level of satisfaction. For this function, an AEC detector called the ion chamber is used, which is designed to be placed in front of or behind the cassette containing the film. K) and ta) ion chambers of FIG. 1 used in the present invention may be referred to as a chamber filled with gas in a kind of flat plate, and X-rays flow through the chamber, causing gas particles to ionize and reach the chamber. This produces a current proportional to the concentration of Ray. In this paper, the initial adjustment function is added to provide a predetermined current according to the film density. Therefore, when this current amount is reached, the timer circuit is automatically operated to terminate the X-ray exposure. In addition, if the radiologist specifies voltage (kVp) and current (mA) in advance in b) Control Console of FIG. 1), the AEC function of the present invention operates to automatically determine the exposure time of X-ray. The aim of the AEC is to provide X-ray exposure during exposure with the lowest possible exposure time within the maximum kW rating of the X-ray tube. The lowest possible exposure time does not mean very short exposure time, but rather shorter exposure time. In general, to shoot, select mA in the control panel to lock, then set kVp and exposure time. However, the AEC generator has the ability to output the same mAs with short exposure time while automatically changing the mA when selecting mAs other than mA. In the theoretical X-ray tube rating table at the tube voltage of 70 kVp in Fig. 8, if 200 mA is selected when the shooting conditions must be 70 kVp and 200 mAs, the exposure time 1.0 (200 mAs) must be selected. If you choose an exposure time of 1.0 seconds, blur will naturally occur and the image quality will deteriorate. However, if you select 300mA, you cannot shoot more than 0.5 seconds (150 mAs), and if you select 400mA, you can shoot over an exposure time of 0.3 seconds (120mAs). The reason for this is that the exposure time is limited within the allowable rating according to the X-ray tube rating table in Fig. 8). Therefore, 200 mA, 1.0 second must be selected for this X-ray tube rating to obtain 200 mAs. However, as shown in FIG. 9, the AEC function is designed to shorten the same 200 mAs to 0.5 seconds instead of 1.0 seconds by selecting a high mA and then automatically changing to the lower side. Selecting 70 kVp and 200 mAs in AEC selects 0.05 seconds (30 mAs) at 600 mA, 0.15 seconds (75 mAs) at 500 mA, 0.1 seconds (40 mAs) at 300 mA, and seconds at 60 mA (60 mAs). ), The total exposure time can be exposed to 205 mAs at 0.5 seconds. The exposure time is not broken for each mA, but the mA varies during continuous exposure. One of the core functions of the present invention, APR (Aatomic Programming), is a function frequently used to select voltage (kVp) and current (mA) during each X-ray imaging. It has a built-in constant value inside the control console. In particular, in this paper, an additional push button for the APR function is built in the b) Control Consol of Figure 1), which selects the voltage (kVp), current (mA) and AEC time, and X-ray exposure time that the radiologist can select. User convenience is provided so that it can be used with a predetermined value. In doing so, the radiologist was designed to select and use the patient simply by pressing a button without the need for complicated instructions. It is very important to keep the brightness constant in perspective. Regardless of whether the patient is dry or fat, maintaining a constant image without glare is the ABC (Auto Brightness Control) function. In the present invention, a fixed amount of X-Ray is always emitted at the input of an image intensifier. It is designed to adjust automatically in X-Ray generator as much as possible. The above has described the overall aspect of the hardware of the present invention, and together with the hardware element, the microprocessor (MCU) in the control console of FIG. First, when the user turns on the power, the microprocessor (MCU) in B) Control Console of FIG. 1 initializes the elements necessary for booting, for example, Register, Interrupt, LCD, etc., and then turns on the Power LED. After executing the Write routine to display the characters to be displayed on the LCD, in order to correctly operate the parts and functions, read the various parameters pre-stored in the EPROM in B) Control Console of Fig. 1) and start setting. The setting to be started at this time can be done in two cases, one is a routine that sets the basic settings that should be set when the first X-ray filming / projecting device is manufactured at the factory, and the second is the user's use. Setting routine to change the condition. To do this setting, first, to find out what command the user sent, see Figure 14) Display and Key Input Sub-System as shown in the block diagram. E) It will be recognized in e) / bar), and key scan will be done in Fig. 14) -d), and it will be displayed through LCD / LED in Fig. 14) -d), and Fig. 14-a) / b) Will be processed through At this time, as shown in Figure 15) Main Control System Mode, the function is performed depending on whether it is "Anatomic mode", "General operation mode" or "Calibration mode". In case of power on, check whether EPROM in b) Control Console of Fig. 1) is correct and then set it in order to perform a smooth command between the control console of Fig. 1) -b) and the high frequency X-ray generator of c). The necessary data is written to the EPROM using a microprocessor (MCU) in the control console of FIG. 1), and in the case where "normal mode" is selected in FIG. 15), FIG. 16) kVp Control System, FIG. 17). When the mA Control System is performed and "Calibration Mode" is selected, Figure 18) Block diagram of kV Control Sub-System and Figure 19) Block diagram of mA Control Sub-System and Figure 20) Heating Calibration of Block Diagram of Calibration System Do this It said, "Anatomic Mode" FIG. 21) Anatomic Program Sub System for Block is selected - the Diagram is to be performed. Main Control System of FIG. 15 is a part that controls and monitors the entire system. The microprocessor controls external devices using I / O ports and timers. The main control system is divided into three modes. In the "normal operation mode", the user operates the system normally. In the "calibration mode", the parameters related to the X-ray generation, the main function of the system, are matched with the actual values. It is executed when it is first produced or when the system is changed. And Anatomic mode is a mode that saves data about shooting that is used frequently for the user's convenience. 14) Display & Key Input System is a part for displaying Key input and Parameter by user's operation on the screen. Display & Key Input System includes Push Switch Input, Membrane Input,

It is divided into Key Scan, Key Pressing Check, Key Mapping, and Dynamic Display. 16) kV Control System, kV setting, kV Offset calculation, kV Data calculation, kV

Data output, kV output time calculation It is divided into kV detection and PWM waveform generation.The user sets kV and calculates kV offset to generate kV data from E2PROM, and this value is output by D / A conversion. Before converting to analog value, generate PWM waveform using kV Data value and actual generated kV detection value.Figure 17) mA Control System detects mA setting, mA Offset calculation, mA Date calculation, mA Data output, mA detection filament current It is divided into PWM waveform generation and mA output time calculation. The mA mA is calculated from the set mA and the corresponding mA data is generated from the EPROM. The generated mA data value generates PWM waveform through D / A conversion. The PWM waveform generates an analog converted command value and detected current value as input.

The Calibration System is divided into 18) kV Calibration, 19) mA Calibration, and 20) Heating Calibration. Calibration outputs the set value and compares the detected value. When there is a difference, the offset value is changed so that the actually output value matches the detected value. Each Offset value will be saved after calibration is completed. Finally, the error check system is divided into error check, error processing, and error display parts. Error check is not only periodic but also checks before and after executing a specific action for quick response. Depending on the importance of the error, the error handling method is different and the status of the error is displayed.

Make it easy for users and service engineers to take action.

The present invention operates a high frequency generation circuit in a high frequency X-ray generator using a microprocessor (MCU), thereby minimizing the amount of X-rays during X-ray imaging, so that the radiation And a speaker protection effect that allows the patient to receive only the minimum required amount of X-rays, The X-Ray Radiography / Fluoroscopy System has a lot of inconveniences because the radiologist randomly sets the data necessary for X-Ray imaging manually without using the microprocessor (MCU), and also the accurate adjustment due to the random selection of the radiation carrier. Not this could lead to measurement errors depending on the patient.

In response to this, in the present invention, a microprocessor is used to automatically scan all parameters according to a patient and automatically set them so that they can be conveniently used by both a radiologist and a patient, but are optimized for each patient in an optimal shooting condition. According to this, by automatically adjusting to shoot at the optimum X-Ray amount, it is possible to obtain the effect of controlling unnecessary X-Ray amount. In particular, in the present invention, an additional push button required for the APR (Anatomical-Program) function is built in the b) Control Console of Fig. 1, which the radiologist can select voltage (kVp), current (mA) and AEC time, and X -User convenience is provided so that Ray exposure time can be used with predetermined value. In doing so, the radiologist was designed to select and use the patient simply by pressing a button without the need for complicated instructions. It is very important to keep the brightness constant in perspective. The ABC function is to maintain a constant image regardless of whether the patient is dry or fat. In the present invention, the X-Ray generator emits a fixed amount of X-Ray at the input of the Image Intensifier. In addition, it automatically adjusts the error check function, and built-in error check function enables quick response by inspecting before and after performing periodic specific operation. Intelligent X that implements automatic exposure adjustment (AEC) and APR function using micro process (MCU) designed to easily handle user and service engineer by displaying error status according to the importance of error. Ray invention.

Claims (11)

In order to improve the performance of the X-ray generator, AEC (automatic exposure control device) and ABC (automatic brightness control device) functions using the car ion chamber 1 and the other ion chamber 2 shown in FIG. By easily setting the exposure level of X-ray automatically according to adults and children, fat body and skinny body, tall patient or short patient, it is convenient for doctor or radiologist and the patient is in the best condition. The APR function that allows X-Ray to be taken at is the APR (Anatomic Programming) function, which is one of the core functions of the present invention, to select voltage (kVp) and current (mA) during each X-ray imaging. It is often used to extract enough experimental data in advance, and built a certain value in the control console in advance, and in particular, in the present invention, an additional push button required for the APR function is built in b) Control Consol of FIG. This provided the radiator with a choice of voltage (kVp), current (mA), and X-ray exposure time at predetermined values. By doing so, the radiologist can use APR function and 21) Anatomic Program Sub System that can be selected and used according to the patient by simply pressing a button without the need for complicated user manuals. In the prior art, c) Change box of FIG. 11) is a separate package, and a high voltage cable for connecting high pressure was needed separately. I gave it Fig. 12) Current high pressure generating part to prevent this The patient has been exposed to a large amount of unnecessary X-Ray for a long time because the patient uses 60Hz sign wave so that the patient can only fit the minimum amount of X-Ray when shooting. However, X-Ray is generated by High Frequecny (30-40Khz). Invertor implementing the High Frequency Generator (Fig. 2) so that the patient can obtain a good quality image while being exposed to the minimum X-ray amount in the shortest time.  The current flowing through the X-ray tube may change as the tube voltage increases or decreases. If the tube current is fixed at 500mA and the tube voltage is gradually increased from 50kVp to 90kVp, the amount of moving electrons decreases at 50kVp, and the filament heating temperature increases. The space charge compensator of FIG. Considering the fact that the existing X-ray camera and the projection function are analog, in the present invention, the analog signal entering the b) TV Monitor of FIG. 2) can be displayed on the workstation through the A / D converter of FIG. 2). Digital conversion function that can convert and convert digitized video signal into hard disk of PC and print, and implement application program that can manage image data for each patient. Routines to set the elements that should be set by default when the X-ray shooting / visioning system is first manufactured at the factory, and a user first executes a command to set the setting when the user wants to change shooting / perspective conditions during use. Figure 14) Display & Key Input Sub-System to Find Out Figure 16) kVp Control System and Figure 18) kVp Control Sub-System Figure 17) mA Control System and Figure 19) mA Control Sub-System 20) Calibration System Figure 22) Error check system

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