A power supply facility for supplying a magnetic resonance facility with electrical power includes a control facility, a network connection to a power network, and an electrical energy store, such as a battery. The network connection is configured for an installed power level that is lower than a maximum power level that may be demanded by the magnetic resonance facility. The control facility is configured, in the event that a power demand of the magnetic resonance facility exceeds the installed power, to provide the power from the network connection and the energy store.

A method of handling a peak power requirement of a medical imaging device 106 is presented. The method includes determining, using at least one controlling unit 107, 108, a first voltage corresponding to a direct current (DC) link 116, a second voltage corresponding to one or more energy storage devices 110, or a combination thereof, where a power source 102 is coupled to a plurality of loads via the DC link, and the energy storage devices are coupled to the DC link. Further, the method includes comparing, using the at least one controlling unit, the first voltage with a first reference value and the second voltage with a second reference value and regulating, using at least one controlling unit, at least one of the first voltage and the second voltage based on the comparison, to handle the peak power requirement of the medical imaging device.

A control computer for a magnetic resonance imaging system has an analog-to-digital conversion array, a multiplexer array connected to the analog-to-digital conversion array, and a control module that receives at least one input signal via the multiplexer array and the analog-to-digital conversion array. A signal processing board for a magnetic resonance imaging system has a substrate with the aforementioned components thereon that form the aforementioned control computer.

An NMR system includes a radio frequency (RF) NMR application-specific integrated circuit (ASIC) chip configured to generate an RF output signal and a rectifier configured to receive the RF output signal and convert the RF output signal to (a) a direct current (DC) pulsed field gradient (PFG) signal or (b) a DC trigger signal for at least one of (i) activating at least one component of an NMR system external to the NMR RF ASIC chip and (ii) synchronizing at least one component of an NMR system external to the NMR RF ASIC chip.

A computer-implemented method for sequencing magnetic resonance imaging waveforms uses a multistage sequencing hardware. A method comprises creating, with the aid of a computer processor, an active memory region that includes waveforms and schedules being played, and creating one or more buffer memory regions that contain waveforms and schedules not currently being played. Next, the waveforms and schedules in the one or more buffer memory regions may be updated while waveforms may be played in the active memory region. Upon completion of the waveform playback in the active memory region, the active and buffer memory regions may be swapped so that the former buffer memory region becomes the active memory region, and the former active memory region becomes the buffer memory region. The method may be repeated as needed until the imaging process is completed or otherwise halted.

A circuit arrangement for generating a current for an inductive load is provided. The circuit includes a switched output state, a modulator, a current measuring device, a controller, a compensator, and a summer The switched output stage is configured to generate the current from a supply voltage. The modulator is configured to modulate the supply voltage of the output stage depending on a modulator input signal of the modulator. The current measuring device is configured to determine the actual value of the current. The controller is configured to generate a controller signal depending on a setpoint value of the current and the actual value of the current. The compensator is configured to generate from the setpoint value of the current at least one compensation control signal that compensates for nonlinearities of the output stage. The summer is configured to generate the modulator input signal additively from the controller signal and the at least one compensation control signal.

A computer-implemented method is disclosed for providing an actuation sequence which specifies transmit signals for at least one high-frequency transmit channel of an antenna arrangement of a magnetic resonance device for acquiring measurement data of an object under investigation by the magnetic resonance device. The method includes providing different actuation sequences, wherein each sequence is the result of an optimization method and which differs with regard to the value of an optimization parameter taken into account in the course of the optimization method. The method further includes providing a plurality of field distribution maps, (e.g., at least one B.sub.0 map and/or at least one B.sub.1 map), acquired by the or a further magnetic resonance device from the object under investigation. The method further includes selecting the actuation sequence to be used from the different actuation sequences depending on the field distribution maps and providing the actuation sequence to be used.

An asymmetric electromagnet system, method, and method of producing an asymmetric electromagnet system, wherein the asymmetric electromagnet system is for generating an imaging magnetic field in an imaging region with an imaging isocentre, the imaging region being asymmetrically positioned within a gradient coil bore inside a magnetic resonance imaging (MRI) system during imaging, the electromagnet assembly comprising: an asymmetric gradient coil configured to generate a gradient field in the asymmetrically positioned imaging region, at least one gradient axis having the gradient field with a constant offset component such that the position at which the gradient field passes through zero is offset with respect to the imaging isocentre of the asymmetrically positioned imaging region.

An MRI apparatus includes a charge/discharge controlling unit, a judging unit and a condition restricting unit. The charge/discharge controlling unit includes a charge/discharge element, receives electric power, and charges the charge/discharge element by using the received electric power. The charge/discharge controlling unit also supplies a gradient magnetic field coil with electric power discharged from the charge/discharge element at a time of performance of magnetic resonance imaging. The judging unit judges whether capacitance of the charge/discharge element falls below a threshold value or not. The condition restricting unit restricts electric power amount supplied to the gradient magnetic field coil by restricting conditions of an imaging sequence, when the capacitance of the charge/discharge element falls below the threshold value.

A gradient system for a magnetic resonance imaging system can include at least two examination areas using a common basic magnetic field and a number of gradient coils in the at least two examination areas, and a gradient controller configured such that it controls the electric current flowing through at least two gradient coils for similar gradient axes in different examination areas in a temporal synchronous manner.