Embodiments of the present disclosure disclose a combined scanning X-ray generator, a composite inspection apparatus and an inspection method. The combined scanning X-ray generator includes: a housing; an anode arranged in the housing, the anode including a first end of the anode and a second end of the anode opposite the first end of the anode; a pencil beam radiation source arranged at the first end of the anode and configured to emit a pencil X-ray beam; and a fan beam radiation source arranged at the second end of the anode and configured to emit a fan X-ray beam; wherein the pencil beam radiation source and the fan beam radiation source are operated independently.

Embodiments of the present disclosure disclose a combined scanning X-ray generator, a composite inspection apparatus and an inspection method. The combined scanning X-ray generator includes: a housing; an anode arranged in the housing, the anode including a first end of the anode and a second end of the anode opposite the first end of the anode; a pencil beam radiation source arranged at the first end of the anode and configured to emit a pencil X-ray beam; and a fan beam radiation source arranged at the second end of the anode and configured to emit a fan X-ray beam; wherein the pencil beam radiation source and the fan beam radiation source are operated independently.

The present invention relates to a system and a method for high-voltage switching for a computed tomography apparatus. The system comprises an oscillating circuit with a non-linear inductor and a capacitor. The inductor and the capacitor are connected in series, and the capacitor is connected to a high-voltage line of a high-voltage power supply. The inductor comprises an inductance that decreases with increasing current through the inductor, such that the inductance of the inductor significantly chances during a resonant operation of the oscillating circuit, thereby providing essentially a square voltage applied to the capacitor. The square voltage modulates the high-voltage of the high-voltage generator thus switching high-voltage levels applied to an electrode of a computed tomography system.

The present invention relates to a system and a method for high-voltage switching for a computed tomography apparatus. The system comprises an oscillating circuit with a non-linear inductor and a capacitor. The inductor and the capacitor are connected in series, and the capacitor is connected to a high-voltage line of a high-voltage power supply. The inductor comprises an inductance that decreases with increasing current through the inductor, such that the inductance of the inductor significantly chances during a resonant operation of the oscillating circuit, thereby providing essentially a square voltage applied to the capacitor. The square voltage modulates the high-voltage of the high-voltage generator thus switching high-voltage levels applied to an electrode of a computed tomography system.

An X-ray detector is disclosed, including a detection unit to generate a detection signal for incident X-ray radiation; a signal analysis module to determine a set of count rates for incident X-ray radiation based upon the detection signal and signal analysis parameters for X-ray radiation; and a switchover control unit for switching between first signal analysis parameters and second signal analysis parameters. When an amount of X-ray radiation is incident on the detection module, a first set of count rates is generated for a first time interval based upon first signal analysis parameters and a second set of count rates is generated for a second time interval based upon second signal analysis parameters, different from the first signal analysis parameters. An X-ray imaging system including the detector; a method for determining count rates for X-ray radiation; and a method for calibrating signal analysis parameters are also disclosed.

An X-ray detector is disclosed, including a detection unit to generate a detection signal for incident X-ray radiation; a signal analysis module to determine a set of count rates for incident X-ray radiation based upon the detection signal and signal analysis parameters for X-ray radiation; and a switchover control unit for switching between first signal analysis parameters and second signal analysis parameters. When an amount of X-ray radiation is incident on the detection module, a first set of count rates is generated for a first time interval based upon first signal analysis parameters and a second set of count rates is generated for a second time interval based upon second signal analysis parameters, different from the first signal analysis parameters. An X-ray imaging system including the detector; a method for determining count rates for X-ray radiation; and a method for calibrating signal analysis parameters are also disclosed.

A system can have an x-ray source that generates a series of individual x-ray pulses for multi-energy imaging. A first x-ray pulse can have a first energy level and a subsequent second x-ray pulse in the series can have a second energy level different from the first energy level. An x-ray imager can receive the x-rays from the x-ray source and can detect the received x-rays for image generation. A generator interface box (GIB) controls the x-ray source to provide the series of individual x-ray pulses and synchronizes detection by the x-ray imager with generation of the individual x-ray pulses. The GIB can control x-ray pulse generation and synchronization to optimize image generation while minimizing unnecessary x-ray irradiation.

A system can have an x-ray source that generates a series of individual x-ray pulses for multi-energy imaging. A first x-ray pulse can have a first energy level and a subsequent second x-ray pulse in the series can have a second energy level different from the first energy level. An x-ray imager can receive the x-rays from the x-ray source and can detect the received x-rays for image generation. A generator interface box (GIB) controls the x-ray source to provide the series of individual x-ray pulses and synchronizes detection by the x-ray imager with generation of the individual x-ray pulses. The GIB can control x-ray pulse generation and synchronization to optimize image generation while minimizing unnecessary x-ray irradiation.

A radiation therapy system includes an X-ray imaging system that is configured with a combined and simplified filter and collimator positioning mechanism. In addition, an X-ray imager of the RT system is only positioned at a few discrete locations within a plane that is a fixed distance from the imaging X-ray source when generating X-ray images. As a result, for each of these discrete imaging positions, the simplified filter and collimator positioning mechanism positions a specific collimator-filter combination in a specific location between the X-ray source and the imager.

A radiation therapy system includes an X-ray imaging system that is configured with a combined and simplified filter and collimator positioning mechanism. In addition, an X-ray imager of the RT system is only positioned at a few discrete locations within a plane that is a fixed distance from the imaging X-ray source when generating X-ray images. As a result, for each of these discrete imaging positions, the simplified filter and collimator positioning mechanism positions a specific collimator-filter combination in a specific location between the X-ray source and the imager.