MRI SCANNER WITH ACTIVE INTERFERENCE SUPPRESSION AND INTERFERENCE SUPPRESSION METHOD FOR AN MRI SCANNER

Abstract

The invention relates to an MRI scanner and a method for operation of said MRI scanner. The MRI scanner has a first receiving antenna for receiving a magnetic resonance signal from a patient in a patient tunnel, a second receiving antenna for receiving a signal having the Larmor frequency of the magnetic resonance signal, and a receiver. The second receiving antenna is located outside of the patient tunnel or near an opening thereof. The receiver has a signal connection to the first receiving antenna and the second receiving antenna and is designed to suppress an interference signal by the second receiving antenna in the magnetic resonance signal received by the first receiving antenna.

Description

The invention relates to an active interference suppression method in an MRI scanner and also to an MRI scanner with a receiver.

MRI scanners are imaging facilities, which for imaging an examination object align nuclear spins of the examination object with a strong external magnetic field and excite them with a magnetic alternating field for precession about this alignment. The precession or return of the spins from this excited state back into a state with lower energy in its turn creates as a response a magnetic alternating field, which is received via antennas.

A spatial encoding is impressed on the signals with the aid of magnetic gradient fields, which subsequently makes it possible to assign the received signal to a volume element. The received signal is then evaluated and a three-dimensional imaging representation of the examination object is provided. To receive the signal, local receiving antennas, known as local coils, are preferably used that, to achieve a better signal-to-noise ratio, are arranged directly on the examination object. The receiving antennas can also be built into a patient couch.

MRI scanners require radio frequency screening in two respects. On the one hand radio frequency pulses with powers in the kilowatt range are generated to excite the nuclear spins, which are only partly absorbed in the patient. Radio waves that leave the patient tunnel are radiated out into the room and must therefore be screened out to adhere to emission limit values.

Conversely the magnetic resonance signals to be received for the imaging are extremely weak. In order to obtain a sufficient signal-to-noise ratio (SNR) here, a screening out of external interference signals is required.

In the prior art complex screening cabins are therefore installed around an MRI scanner, in order to reduce both emissions and also immissions.

A knee coil with local screening is known from publication DE 10 2014 207 843.

An object of the invention could therefore be to reduce the outlay for screening.

The object is achieved by an inventive MRI scanner as claimed in claim 1 and claim 2 and also by an inventive method for operation of the MRI scanner as claimed in claim 21 and claim 22.

The inventive MRI scanner has a patient tunnel, a first receiving antenna for receiving a magnetic resonance signal from a patient, wherein the patient is in the patient tunnel, a second receiving antenna for receiving a signal having the Larmor frequency of the magnetic resonance signal and a receiver. The receiver has a signal connection to the first receiving antenna and the second receiving antenna and is preferably designed to prepare the magnetic resonance signal for imaging.

The second receiving antenna is arranged outside or in the vicinity of an opening of the patient tunnel. An opening of the patient tunnel is seen in particular as the openings through which the patient couch with the patient is moved into the patient tunnel and, depending on the region to be examined, also leave the patient tunnel again at the opposite end. In the vicinity in this case is seen as a distance from the opening of less than 0.1 m, 0.2 m. 0.5 m, 1 m or 2 m. In the vicinity can also be seen as a distance from the opening of less than a quarter wavelength or a half wavelength of a radio wave in the air having a Larmor frequency of the MRI scanner.

The first receiving antenna in this case preferably receives the magnetic resonance signal, which however always has a small portion of the interference signal. Conversely the second receiving antenna not only receives the interference signal, but also a minimal or negligible portion of the magnetic resonance signal. For the sake of simplicity the signal received by the first receiving antenna will still be referred to below as the magnetic resonance signal (even when having a portion of the interference signal to be removed) and the signal received by the second receiving antenna will be referred to as the interference signal.

The receiver is designed in this case to suppress an interference signal received with the second receiving antenna in a magnetic resonance signal received by the first receiving antenna. Examples of forms of embodiment are described in greater detail for the dependent claims.

In the form of embodiment of claim 2, in this case the possibility is considered in particular that the interference signal is more wideband than the magnetic resonance signal. The portions outside the frequency range of the magnetic resonance signal correlate in this case with the portions within the frequency range of the magnetic resonance signal. Therefore it can also be sufficient in accordance with the invention for the second receiving antenna to receive the wideband interference signal and for the receiver to be designed to evaluate this signal only partly, for example in a frequency range that is not the same as or is outside the frequency range of the magnetic resonance signal and then to suppress the interference signal in a magnetic resonance signal received by the first receiving antenna as a function of this part signal. As an alternative or in addition it would also be conceivable however for the second receiving antenna already only to receive frequencies outside the frequency range of the magnetic resonance signal and to forward these to the receiver. As a result of the correlation for example the amplitude of the frequency components of the interference signal in the frequency range of the magnetic resonance signal can be linked with an amplitude outside it. In this way it is also conceivable for the second receiving antenna, in conjunction with receiver during a magnetic resonance scan, only to monitor frequency components outside the frequency range of the magnetic resonance signal for interference signals and to suppress the interference signal in the signals of the first receiving antenna. It would be possible in this case for example for the receiver to establish a relationship between the interference signal from the first receiving antenna and interference signal portion from the second receiving antenna, also referred to as the transfer function, for an interference signal in the frequency range of the magnetic resonance signals between detections of magnetic resonance signals and during the detection of magnetic resonance signals for example, to adapt the amplitude or scaling on the basis of portions of the interference signal received by the second receiving antenna outside the frequency range of the magnetic resonance signal.

It is also conceivable for a filter to be provided between the second receiving antenna and the receiver, which preferably lets the interference signal through and suppresses magnetic resonance signals. For example a filter that suppresses the magnetic resonance signals could be provided for an interference element with portions outside the frequency band of the magnetic resonance signal. The filter could also be adaptive or controllable. In this way it would be conceivable for the interference suppression control to adapt the filter to the Larmor frequency of a slice currently being acquired.

An explanation is given below as to how the interference signal can be suppressed in the signals of second receiving antenna by the receiver. For example the receiver can have a summation device, which forms a linear combination of one or more parameters dependent on the magnetic resonance signal and interference signal. Furthermore the receiver can have an interference suppression controller, which is designed to vary the parameter or parameters in such a way that an energy of the interference signal is minimal in the linear combination. In this case one or more parameters can be complex, in order to model a phase displacement or a phase displacement can be specified by a separate parameter. A number of parameters in particular allow the effective suppression of different interference sources.

Non-linear combinations of the signals depending on the parameter or parameters are also conceivable however.

The interference suppression controller could also weight interference signals with especially large amplitude especially heavily in the parameters compared to weaker interference signals in the interference suppression, since through the especially great distance of the signal level in relation to a statistical background interference, these strong interference signals are able to be suppressed especially well. In this case different interference signals are in particular seen as interference signals that can be separated by different point of origin by means of a number of second receiving antennas, occupy different frequency ranges or are differentiated by different temporal behavior.

The receiver can be designed in this case to carry out this inventive processing of the received magnetic resonance signal and of the interference signal for suppression of the interference signal in real time, for example by means of a field-programmable gate array (FPGA) or a digital signal processor (DSP).

It is also possible however for the receiver to have a memory and initially to store the received interference signal and the received magnetic resonance signal, wherein the interference signal is only suppressed at a later point in time with a delay of for example the duration of an echo sequence, an excitation sequence or an entire image acquisition of an individual slice or the entire image acquisition sequence. The delay can for example be greater than 50 ms, 100 ms, 0.5 s, 1 s, 10 s, 1 min or more.

A receiver in the sense of the invention can be seen as the hardware for analog and/or digital radio frequency processing such as for example amplifiers, filters and mixers in real time, but also an image evaluation unit for later generation of an image from the received magnetic resonance signals.

The inventive method for operation of the inventive MRI scanner has the step of receiving interference signals by means of the receiver via the second receiving antenna. Because of the arrangement of the second antenna in the vicinity of the opening, the interference signal received by the second antenna received has scarcely any portions of the magnetic resonance signal or none at all.

In another step the receiver receives a magnetic resonance signal via the first receiving antenna. The first receiving antenna can involve a body coil or a local coil of the MRI scanner for example.

In a further step of the method, the receiver processes the magnetic resonance signal as a function of the interference signal by the receiver into a receive signal, wherein the dependency is a function of a parameter. For example it is conceivable for the receiver to form a linear combination of interference signal and magnetic resonance signal with the parameter as factor, wherein the parameter can be complex, in order to map a phase displacement. A number of parameters are also conceivable.

In another form of embodiment of the inventive method, there is provision for the receiver to receive portions of a wideband interference signal outside the frequency range of the magnetic resonance signal by means of the second receiving antenna. In this case portions of the interference signal outside the frequency range of the magnetic resonance signal correlate with portions within the frequency range. For example it is conceivable for the amplitudes of the interference signal within and outside the frequency range of the magnetic resonance signal to be proportional to one another, if the same source is involved. In the suppression of the interference signal in the magnetic resonance signals received by the first receiving antenna described below, the scaling with the amplitude of the signal of the second receiving antenna can then be provided as the dependency for example.

In an advantageous way, any influencing of the suppression of the interference signal by the magnetic resonance signals during an image acquisition can be avoided by the separate frequency ranges. In other words, by the evaluation of the signals received by the second receiving antenna by the receiver in frequency ranges that are not the same as the frequencies of the magnetic resonance signals, it can be avoided that scattered-in magnetic resonance signals are interpreted as an interference signal can be avoided and suppressed by the interference suppression controller.

Preferably in this case the interference suppression controller also takes account of different characteristics of signals in the frequency band of the magnetic resonance signals and outside it. These can for example be different attenuations or signal delays, which can be taken into account by other amplification factors and phase displacements. The different characteristics can be established for example by calibration measurements to determine transfer functions, as will be explained below for the dependent claims.

In this case it is conceivable for interference signals to be detected between and/or also during the MR signal acquisition by the receiver. A permanent detection advantageously allows the temporal course of an interference signal to be better detected and thus also better estimated for the future, which allows a more precise suppression.

An intermediate acquisition, i.e. between the acquisition of MR signals, makes it possible on the other hand to avoid the MR signals being evaluated as interference signals. In this case it is also conceivable for not only the second receiving antenna or antennas to detect the interference signals in this case, but also simultaneously the first receiving antenna or first receiving antennas, so that it is known exactly how an interference signal received by the second receiving antennas will be acquired by the first receiving antennas. This relationship, also referred to as a transfer function, then allows a more precise determination of parameters for interference suppression and thus a better suppression of the interference by the receiver.

The different methods (different frequency, temporal restriction) can also be combined with one another and/or employed alternately, in order to arrive at an improved interference suppression overall.

Furthermore it is also conceivable for there to be an averaging of the results over longer or over a number of acquisition periods and/or also between the different methods.

In another step the receiver, for example by means of an interference suppression controller, sets the parameter in such a way that a portion of the interference signal is reduced in the receive signal. It is conceivable for example for the parameter to be set by the interference suppression controller in an optimization method in such a way that an energy of the interference signal is minimized in the receive signal.

As already explained previously for the receiver, the receiver in this case can also store the magnetic resonance signal and/or the interference signal in this case so that the steps of processing and of setting the parameters can also take place spaced apart in time from receipt of the signals by the first receiving antenna and the second receiving antenna.

In an advantageous way, the inventive MRI scanner and the method for operation by the second receiving antenna and the inventive receiver make it possible to reduce the portion of external interference signals in the magnetic resonance signal and therefore to manage with simpler and lower-cost screening measures.

Further advantageous forms of embodiment are specified in the dependent claims.

In a possible form of embodiment of the inventive MRI scanner, the MRI scanner is designed to receive magnetic resonance signals having a Larmor frequency in an industrial band. A resonant frequency of the nuclear spins used for the imaging in the MRI scanner in a static magnetic field BO of a field magnet of the MRI scanner is referred to in this case as the Larmor frequency of the MRI scanner. Frequency bands released for use by medical or technical devices are referred to here as the industrial band, for which simplified regulations for emission and approval are available. These are also referred to as ISM bands (Industrial, Scientific, Medical Band). An example of a frequency band in which there may also be emissions with high powers, lies between 26.9 and 27.3 MHz. Other such frequency bands lie between 6.7 MHz and 6.8 MHz, 13.5 MHz and 13.6 MHz, 40.6 MHz and 40.7 MHz and also 433.0 MHz and 434.8 MHz.

An MRI scanner is not only dependent on the lowest possible interference being received, but on the strong excitation pulses also not interfering with other devices. In the ISM band the legal tolerance limits are significantly higher, so that a legally-conformant restriction through screening of the emitted excitation pulses is more easily possible at this frequency or even is not required. In synergistic connection with the active screening in order to suppress receive-side interference by other devices in the ISM band, an MRI scanner can be realized in an advantageous way entirely without a screening cabin.

In a possible form of embodiment the MRI scanner in this case the MRI scanner has a transmit path for transmitting the excitation pulses with a filter. The filter in this case is designed to suppress signals outside the ISM band. For example the filter can involve a bandpass filter for the ISM band used, that damps out frequencies outside the ISM band by more than 12 dB, 24 DB, 40 dB or 60 dB relative to a signal with minimal attenuation within the ISM band. Depending on the implementation of the radio frequency generation of the MRI scanner, the filter can be arranged for example between final stage and a hybrid coupler, between hybrid coupler and transmit/receive switch or between transmit/receive switch and transmit antenna.

The filter makes it possible in an advantageous way to restrict radio frequency power transmitted essentially to the ISM band and in this way to adhere to the stricter limit values outside the ISM band. In this way there can even be operation of the MRI scanner in the ISM band without an RF cabin.

Basically however it is also conceivable to use an ISM band with a screening cabin without active interference suppression on the receive side, in particular when the emissions by the excitation pulse are critical for an approval. This also applies to the forms of embodiment described below, which relate to a restriction or optimization of the excitation pulse for the ISM band.

In a conceivable form of embodiment of the inventive MRI scanner, the MRI scanner has a transmit antenna for transmitting an excitation pulse, wherein the MRI scanner has non-linear components for tuning the transmit antenna. These can be PIN diodes for example, but also other diodes or active components such as transistors or FETs. In this case the non-linear components are arranged in an area of the MRI scanner screened off from the patient tunnel for radio frequency and the filter for the ISM band or ISM filter is arranged in the signal connection between non-linear component and antenna, preferably in the screened-off area.

In an advantageous way, by the screening-off of the non-linear components from the patient tunnel and the environment, emissions from frequency components are avoided that are created by the non-linearity during the excitation pulse by the components used for tuning and as harmonics no longer lie in the ISM. The filter prevents harmonics being transmitted via the signal connection between non-linear component and transmit antenna. In this way the arrangement of the non-linear components contributes to adherence to emission limit values and makes it possible or simplifies dispensing with the screening of the entire MRI scanner by a radio frequency cabin.

In a possible form of embodiment of the inventive MRI scanner, the MRI scanner has radio frequency unit with a preliminary interference suppressor. The preliminary interference suppressor is designed to provide preliminary interference suppression of the excitation pulse for excitation of the nuclear spins in such a way that the signal components of the excitation pulse on transmission, i.e. in particular after amplification by a radio frequency power amplifier outside the ISM band, are reduced by comparison with an excitation pulse without preliminary interference suppression. It is conceivable for example for the preliminary interference suppressor to create and mix-in signal components, which after an amplification by the radio frequency unit correspond to the harmonics created by the non-linearity of the radio frequency unit from the excitation pulse, but have a reversed leading sign and in this way the harmonics reduce or extinguish each other. The preliminary interference suppressor in this case can be realized for example in a digital signal generator or also corresponding signals can be created from an input signal for a power amplifier by analog components. The preliminary interference suppressor in this case can also be adaptive, for example be controlled in its characteristics as a function of a loading of the patient tunnel. Also conceivable is a part regulation by a fast feedback from a sensor in the transmit path, such as e.g. a directional coupler.

In an advantageous way, the preliminary interference suppressor reduces harmonics outside the ISM band and in this way facilitates or makes possible adherence to the emission limit values even without a screening cabin.

In a conceivable form of embodiment of the inventive MRI scanner, a limit frequency for a propagation of a radio wave in the patient tunnel is greater than a Larmor frequency of the MRI scanner. The limit frequency is seen as the frequency at which a radio wave propagating in the longitudinal (z direction) through the patient tunnel can still form in the patient tunnel as a hollow conductor. The limit frequency is also referred to as the cut-off frequency for a waveguide, here for the patient tunnel as a hollow conductor.

If the frequency of a radio signal lies below this, then in an advantageous way there is an exponential drop in the field strength of an interference signal coming from outside with the distance from the opening inside the patient tunnel, so that the interference signal is significantly reduced in the examination region (Field of View, FoV).

In a possible form of embodiment of the inventive MRI scanner, the second receiving antenna is arranged at an opening of the patient tunnel or on the patient couch. For example the second receiving antenna can be arranged directly at an edge of an opening or below the surface on which the patient lies.

In particular, if the frequency of the interference signal lies below the limit frequency for a free wave, the patient and the patient tunnel form a coaxial conductor for the interference signal. A second receiving antenna in the vicinity of the patient and the opening can detect the interference signal coupled into the patient tunnel through the patient in an advantageous way and in this way make possible an especially effective suppression by the receiver.

In a possible form of embodiment, the MRI scanner has a waveguide that surrounds the MRI scanner, wherein the waveguide has a limit frequency or cut-off frequency that is greater than the Larmor frequency of the MRI scanner. A waveguide in this case is seen as any electrically-conducting structure, which surrounds the MRI scanner at least in four spatial directions around the outside, for example in the form of a tube or a prism, and through its conductivity at the Larmor frequency of the MRI scanner essentially suppresses a propagation of radio waves or electrical fields through the conducting structure. In other words, on a side of the electrically-conducting structure of the waveguide facing away from the MRI scanner a signal with Larmor frequency is attenuated compared to a signal on the side facing towards the MRI scanner by more than 30 dB, 40 dB, 60 dB or more.

It is also conceivable for an inventive waveguide or even a classical screening cabin to surround the inventive MRI scanner in one form of embodiment. A radio-frequency-proof door to the screening cabin or the waveguide is replaced however in this case by an electrically conducting tunnel, which for its part represents a waveguide with a cut-off frequency greater than the Larmor frequency.

Through the attenuation of the alternating fields in the tunnel, emission into the surroundings is reduced, so that an expensive RF-proof door that is difficult to use and susceptible to faults can be dispensed with, in particular at the higher limit values for frequencies in ISM bands.

Here too use of a waveguide as door or screening is also basically conceivable without any active interference suppression in the receive path.

In a conceivable form of embodiment of the inventive MRI scanner, the waveguide has an electrically conductive connection to the patient tunnel. In this case it is conceivable for the waveguide together with the patient tunnel to embody an end-to-end or contiguous waveguide. It is also possible for the waveguide to be connected electrically at both ends of the patient tunnel to the patient tunnel or for two waveguides at opposite ends of the patient tunnel to be connected electrically-conductively to said tunnel. In this case the waveguide can also have a limit frequency or cut-off frequency that is different from the limit frequency of the patient tunnel but is likewise above the Larmor frequency of the MRI scanner.

In a conceivable form of embodiment of the inventive MRI scanner, the second receiving antenna has an essentially omnidirectional receive characteristic. An essentially omnidirectional receive characteristic is seen as a sensitivity distribution of the receiving antenna in all spatial directions, in which the difference between a maximum sensitivity and a minimum sensitivity as a function of the different directions is less than 6 dB, 12 dB, 18 dB or 24 dB. This preferably also applies to different polarizations of the interference signal.

The incident interference signal can come from different directions and with different polarizations, so that an antenna with a directional characteristic or preferred polarization cannot detect all interference signals. An antenna with an omnidirectional receive characteristic on the other hand can detect all interference signals in an advantageous way.

In a possible form of embodiment of the inventive MRI scanner, the MRI scanner has a plurality of second antennas and the receiver is designed to suppress the interference signal in the magnetic resonance signal as a function of receive signals of the plurality of second receiving antennas. Preferably the plurality of second receiving antennas are arranged spaced apart from one another, for example at a distance greater than a quarter of a wavelength or a half wavelength of a radio wave having the Larmor frequency.

In an advantageous way, a plurality of spatially distributed antennas is also better suited to detecting one or more interference sources and thus to improving the interference suppression.

In a conceivable form of embodiment of the inventive MRI scanner, the plurality of receiving antennas is arranged in a symmetry arrangement in relation to the patient tunnel. Conceivable for example is an arrangement at the edge of the opening of the patient tunnel at two opposite points, on the corner points of a regular polygon or polyeder.

In an advantageous way, a symmetry relationship of the parameters can also be produced by means of the symmetry of the antennas and in this way the optimization method for reducing the interference signal can be simplified and/or speeded up.

In a possible form of embodiment of the inventive MRI scanner, the MRI scanner has an interference suppression transmitter and an interference suppression antenna. The interference suppression antenna is arranged at a distance from the patient tunnel. The interference suppression transmitter is designed in this case to generate a signal in a frequency range of an excitation pulse of the MRI scanner and to output it via the interference suppression antenna in such a way that a field strength of the excitation pulse will be reduced by destructive interference in an area surrounding the MRI scanner. Reduced is seen as reduction of the field strength or attenuation of the signal of the excitation pulse in the area by more than 6 dB, 12 dB, 24 dB, 40 dB or 60 dB.

In an advantageous way, the field strength of the electromagnetic waves emitted by the excitation pulse in the environment of the MRI scanner can be reduced by the interference suppression transmitter and the interference suppression antenna in such a way, in particular in synergy with the other proposed measures, that even without an RF cabin the legal limit values can be adhered to.

In a conceivable form of embodiment of the inventive MRI scanner, the MRI scanner has a plurality of interference suppression antennas, wherein the interference suppression antennas are arranged at a distance from the patient tunnel and relative to one another. The distances are preferably less than a wavelength of a free radio wave having the Larmor frequency and/or greater than a tenth of the wavelength. For example the interference suppression antennas can be arranged in a plane around the opening of the patient tunnel. The interference suppression transmitter is designed to output signals in a frequency range of an excitation pulse of the MRI scanner via the interference suppression antennas, so that a field strength of the excitation pulse is reduced by destructive interference in a number of areas of an environment of the MRI scanner.

In an advantageous way, it is possible with a number of interference suppression antennas and activation signals of the interference suppression transmitter to reduce the electromagnetic fields in a number of areas or to reduce the emissions in a number of directions or ideally to bring them down to zero. The number of directions without emissions in this case corresponds to zero points of the emission diagram of a multipole. A resulting electromagnetic wave from a signal of the excitation pulse from a local transmit antenna and the interference suppression antennas is thus as a multipole field (e.g. quadrupole field), that in an advantageous way drops significantly more quickly as the distance from the source increases than a dipole field for example and in this way makes it possible to adhere to limit values for emissions even without an RF cabin.

In a possible form of embodiment of the inventive MRI scanner, the interference suppression transmitter is designed to generate the signals for the interference suppression antenna or interference suppression antennas by phase displacement and/or amplitude adaptation as a function of one or more transmission interference suppression parameters. Preferably the respective signal or signals for the interference suppression antenna or interference suppression antennas are generated from the excitation pulse by adjustable amplifiers or attenuators and phase displacement elements in the interference suppression transmitter. The amplitude relationships and phase displacements in this case can represent the transmit interference suppression parameters or be derived from the transmit interference suppression parameter or transmit interference suppression parameters, for example by analytical functions, tables or iteration methods.

The excitation pulse in this case can be detected for example via a sensor such as a directional coupler in the line between radio frequency power amplifier and transmit antenna or a sensor antenna in the patient tunnel. It is also conceivable to generate the signals for the interference suppression antennas directly from the digital data of the excitation pulse by scaling and phase displacement with A/D converters and amplifiers.

In an advantageous way, transmit interference suppression parameters, by reducing the number of variables, simplify a subsequently specified determination of the setting of the interference suppression transmitter and make possible a more rapid adaptation to changed conditions such as other excitation pulses or being surrounded by patient or operating personnel.

In a possible form of embodiment of the MRI scanner, the transmit interference suppression parameters are set when the installation is manufactured.

In a conceivable form of embodiment of the inventive MRI scanner, the MRI scanner has a calibration element in an environment of the MRI scanner and an interference suppression controller. The calibration element is preferably an antenna or sensor with which an electrical and/or magnetic field strength of an electrical and/or magnetic alternating field with a frequency of the excitation pulse is detected and can be forwarded to the interference suppression controller. The interference suppression controller is designed to detect a field strength in a frequency range of an excitation pulse at the location of the calibration element by means of the calibration element. For example the interference suppression controller can have a calibration receiver. The interference suppression controller is furthermore designed, depending on the detected field strength, to set the transmit interference suppression parameters in such a way that a field strength of the excitation pulse is reduced in a predetermined environment of the calibration element. For example the interference suppression controller can vary or optimize an amplitude and/or phase of the interference suppression antenna or antennas in such a way that a reduction and/or a local minimum of the field strength is obtained by destructive interference at the location of the calibration element.

In an advantageous way, by the adaptive setting of the transmit interference suppression parameter or parameters, there can be a reaction to an environment changed by persons or equipment in the environment of the MRI scanner, in order to adhere to the limit values for emission even under changing conditions. If necessary the transmission can be interrupted and/or a new determination of the parameters initiated if a limit value is exceeded.

In a possible form of embodiment of the inventive MRI scanner, the interference suppression antenna has a radio frequency power amplifier. The radio frequency power amplifier is preferably designed in this case to generate an electromagnetic alternating field sufficient for suppression of stray fields of the excitation pulse via the interference suppression antenna from an activation signal with a low radio frequency power, for example less than 10 mW, 50 mW or 100 mW.

The radio frequency power amplifier makes it possible, compared to a purely passive interference suppression antenna, to connect this by a thin, flexible radio frequency cable to the interference suppression transmitter and in this way to simplify the installation. In advantageous interaction with the patient tunnel as waveguide and the plurality of interference suppression antennas, in this case only a power in the range of a few watts is required, so that the locally arranged radio frequency power amplifier can be made small and light, which simplifies the installation.

In this case, the inventive transmission interference suppression by means of destructive interference can also be applied independently of the other features of the inventive MRI scanner. For example use of an active interference suppression transmitter even without active receive-side interference suppression is conceivable, in particular when the permitted electromagnetic radiation is the limiting factor.

Particular synergies are produced however in ISM bands by the higher permitted limit values, which in conjunction with a receive-side interference suppression make possible operation even without closed screening cabins.

In a conceivable form of embodiment of the inventive method, the step of setting the parameter has the step of an averaging over time with the formation of a temporal average value as a function of the interference signal. For example the amplitude and/or phase of the interference signal can be detected and averaged via a lowpass or by forming the average over a window, so that the parameter only follows slow changes.

In an advantageous way, the averaging over time leads to the interference suppression not being falsified by short-term, possibly sporadic influences and to higher-frequency interference components not being artificially created by the interference suppression.

In a possible form of embodiment of the inventive method with an MRI scanner with calibration element, the setting step has the following sub-steps:

In one step, the receiver measures a first transfer function between a first receiving antenna and the calibration element. The measurement can take place for example by the receiver or the interference suppression controller instructing the interference suppression transmitter via a signal connection to transmit a signal with a predetermined amplitude and/or predetermined phase in a frequency range of the magnetic resonance signal and/or in an adjacent frequency range via the calibration antenna. In this case a signal connection between interference suppression transmitter and calibration element is necessary. The receiver can then receive the signal via the first receiving antenna and define a first transfer function in this way. This can also occur simultaneously for a number of first receiving antennas. Basically however it would also be conceivable to detect the transfer function by transmitting via the first receiving antenna and receiving via the calibration element.

In a further step, the receiver measures a second transfer function between second receiving antenna and the calibration element. This can take place in the same way as previously described. If the signal is transmitted via the calibration element, then in an advantageous way both transfer functions can be detected at the same time.

Preferably the signals transmitted for detection of the first and second transfer functions are encoded so that the receiver can establish the amplitude and phase relationship in a simple way. For example a pseudo random code would be conceivable, which allows a fast and safe autocorrelation of the signals. The signal in this case can be modulated in amplitude, frequency and/or phase. Also conceivable are spread-spectrum modulations, in which the signal for establishing the transfer function can also remain below the noise limit of the MR signals and a simultaneous transmission is possible during a detection of an MR signal. In this way changes in the environment can be addressed permanently. The permanent emission of the signal can also be achieved by use of a frequency range adjacent to the MR signals. Then however the different propagation conditions by the different frequencies in the determination of the transfer functions must be taken into account.

In a further step the interference suppression parameter, or with a number of first and second receiving antennas the interference suppression parameters are set as a function of the measured first transfer function or transfer functions and second transfer function or transfer functions, so that a portion of an interference signal received by the second receiving antenna or antennas is reduced in a signal received by the receiver via the first receiving antenna. In this case the interference signal received by the second receiving antenna or antenna preferably also continues to be taken into account. The transfer functions in this case are applied to the form in which the signal of an individual receiving antenna is taken into account. This can be achieved for example by the interference suppression parameters for the interference signal separated via an autocorrelation in the received MR signal being set in such a way by a variation method or linear optimization method by the interference suppression controller that the interference signal portion is minimized. In this case the transfer functions are included as predetermined attenuations and phase displacements between receiving antennas and receiver. For a calibration element, the transfer function in this case in precise terms is only valid for an interference source at a specific location or direction. When sufficiently many and suitably positioned calibration elements are used to determine the transfer functions, transfer functions can also be determined independently of the respective location the calibration element.

In an advantageous way, the determination of the transfer functions using the calibration element makes it possible for the receive interference suppression to react to different conditions in the environment, such as for example position of people or equipment and the propagation conditions changed thereby and to adapt the interference suppression.

In a possible form of embodiment of the inventive method, the setting step occurs in a period of a sequence in which no magnetic resonance signal is received, in particular also no signal for excitation of the spins is sent. Within a sequence for image acquisition there are periods of time in which no excitation pulses are emitted and also there is no acquisition of a magnetic resonance signal for imaging. Preferably this involves periods of the sequence in which the examination object or the patient is not emitting any appreciable magnetic resonance signal, i.e. the level of the signal is at least 12 dB, 24 dB, 36 dB 48 dB or 60 dB below a maximum magnetic resonance signal. In this form of embodiment of the method the setting step takes place in such a period.

The interference suppression controller of the receiver is correspondingly designed to carry out the setting step in such a period. For example it can receive a trigger signal from the controller of the MRI scanner.

In an advantageous way, the setting of the parameters can be simplified without a magnetic resonance signal, for example by an energy of the signal received by the first receiving antenna being minimized as a function of the parameters. Even if the interference signal changes in its amplitude over time for example the parameters set continue to remain valid and effective with the same spatial arrangement.

In another possible form of embodiment of the inventive method, it is also conceivable however for the setting of the parameter to take place permanently, i.e. in short intervals of 1 ms, 10 ms or 100 ms or especially in real time with a delay of less than 10, 100 or 500 microseconds.

In an advantageous way, the permanent setting of the parameter in real time or almost in real time allows there to be a reaction to new interference signals occurring and their negative effect on the imaging to be minimized as much as possible.

In a further conceivable form of embodiment, the receiver has a memory and stores the received magnetic resonance signal and the received interference signal. The receiver in this case can for example in the sense of the invention also comprise an image evaluation processor. It is however also conceivable in one form of embodiment for the receiver in the narrower sense, i.e. the devices used for editing the received radio frequency magnetic resonance signals, to include the memory. The setting of the parameters and the processing of the magnetic resonance signal with the interference signal as a function of the parameter for reduction of the interference signal by the receiver to a receive signal can then take place with a delay to the receipt. The delay can for example comprise the duration of an echo sequence or also of an entire image acquisition sequence, for example more than 10 ms, 100 ms, 0.5 s, 10 s or even several minutes, hours or in principle also days.

In an advantageous way, the storage makes it possible to use resources of the MRI scanner already available as well or, on account of the fact that real time processing is not required, also to provide the interference suppression at lower cost with less computing power. The retroactive interference suppression also makes possible a comparison of results of different parameter settings and suppression methods and thus an optimization of the interference suppression.

In one conceivable form of embodiment of the inventive method, the receiver or the interference suppression controller has an autocorrelation facility. The interference suppression controller can determine a portion of the interference signal in the magnetic resonance signal, for example an amplitude and a phase displacement, by means of the autocorrelation facility.

In another possible form of embodiment, the interference suppression controller has an estimation device, which for example establishes the portion of the interference signal by an optimization method in which the interference portion is minimized in the magnetic resonance signal by variation of the parameter or the parameters, such as by Least Mean Square Root (LSR) or similar methods.

With a number of parameters the interference suppression controller optimizes the plurality of the parameters in such a way that as large a portion of the interference signal as possible is reduced. This can be of advantage for example with a number of interference sources or reflections.

In an advantageous way, autocorrelation or estimation allow a flexible adaptation to different interference sources.

In a possible form of embodiment of the inventive method, the step of setting the parameters has the following the following sub-steps:

In one sub-step, the received magnetic resonance signals are transformed into an image space. In this case the usual methods used in MR imaging such as for example a Fourier transform are used, but also other methods such as compressed sensing are conceivable.

In another sub-step of the method, the interference signals are separated in the image space from the magnetic resonance data. This can take place for example by comparing two adjacent volumes or by two items of image data of the same volume acquired at different points in time. While the image data is the same or similar, image artifacts created by interference signals are markedly different on account of the lack of correlation.

It is also conceivable for the acquired image space or the associated volume to be greater than the examination object. Regions that do not have any magnetic resonance signal, but merely interference signals, are then detected in the image space. Through this segmentation the interference signal can be separated and established.

In a further sub-step, the interference signals separated in the image space are transformed back into a raw data space or k-space, for example once more with a Fourier transform.

In another sub-step, the parameters for the suppression of the interference signals are determined from the transformed interference signals in the raw data space. For example the coordinates in the k-space specify information about phase and frequency of an interference signal, so that taking into account the arrangement of the first receiving antenna and second receiving antenna and also attenuation factors and phase displacement of the signal paths, an attenuation and signal delay can be determined, after the application of which to the interference signal of the second receiving antenna in a sum signal with the receive signal of the first receiving antenna, the interference in the magnetic resonance signal is reduced.

It is also conceivable however for the interference signals to be suppressed directly in the image space, for example by hiding the corresponding image data. This can be used in particular when the image data does not lie in the examination region or can be replaced by data without any interference already acquired from this region. It is also conceivable to identify the data with interference in the image space by a particular indicator, e.g. a color or brightness value, so that image artifacts caused by interference cannot be taken for features of the examination object.

In an advantageous way, the recognition of the interference signals in the image space allows a separation or segmentation of magnetic resonance data and interference. This enables the interference signals to be acquired separately in a simple way and the characteristics to be better identified, which leads to a better and more effective suppression.

In a conceivable form of embodiment of the inventive method, the sub-steps of the transformation, of the separation, of the back transformation and of the determination of the parameters on rows of data in the received magnetic resonance signals take place in the raw data space.

Through the application of the inventive method to individual rows of the raw data space and their transforms in the image space, in an advantageous way the parameters can be changed more quickly than for example during acquisition of an entire slice and there can thus be a faster reaction to changes of the interference signals. A repetition of the acquisition for an entire slice can be avoided in this way.

In a possible form of embodiment of the inventive method, the receiver monitors the interference signal in one step for changes and adapts the parameters in a further step if there is a change. For example it is possible, through a movement of the interference source or a reflecting object in the environment of the MRI scanner, for the field distribution of the interference source to change in phase and amplitude. The receiver can then detect such changes of the interference signal and adapt the parameter or the parameters accordingly, so that for example the interference signal received by the second receiving antenna or the second receiving antennas is added to the MRI signal with adapted amplification and/or phase displacement. In this case it is conceivable for the receiver to take account of threshold values during the monitoring and for only a threshold value being exceeded to be seen as a change. Likewise it is conceivable for the receiver to undertake an averaging over time in order to edit out short-term fluctuations. The averaging in this case can for example involve characteristics of the interference signal such as amplitude, phase, frequency and/or frequency distribution, in order not to react to short-term fluctuations and to introduce as few additional noise components into the magnetic resonance signal by the interference suppression as possible. It is also conceivable to average the parameters over a period of time or filter them with a lowpass during the setting step.

In an advantageous way, a monitoring of the interference signal by the receiver allows there to be a reaction to changes of the interference signal and in this way to insure effective noise suppression over a longer period of time of a variable interference signal. Thresholds and averaging in this case allow the changes to be limited and variations caused by instabilities or artifacts caused by compensation that is too great to be avoided.

In a possible form of embodiment of the inventive method, the receiver stores a first received magnetic resonance signal in a memory in one sub-step. In another sub-step the receiver stores a second received magnetic resonance signal in a memory. In a further sub-step the receiver compares the first received magnetic resonance signal and the second received magnetic resonance signal. If the receiver recognizes a deviation in this process that is to be attributed to external interference sources, the receiver carries out an interference suppression measure or signals a fault to the controller of the MRI scanner, so that this initiates the interference suppression measure. In this way sudden differences in amplitude in magnetic resonance signals of slices lying close to one another or measurements of the same slice, for example from a calibration measurement, can possibly be interference signals.

In an advantageous way, interference signals can be recognized by the comparison of the magnetic resonance signals of adjacent regions or the same regions at different times. This is also conceivable in an application without second receiving antenna for receiving the interference signal.

In a conceivable form of embodiment of the inventive method, the interference suppression measure is the discarding of the first and/or second received magnetic resonance signal. It is also conceivable, in addition or as an alternative, for an acquisition of the first and/or second magnetic resonance signal to be repeated. The interference suppression measure can also comprise a setting of the parameter.

Through the proposed interference suppression measures, image artifacts in the magnetic resonance recordings after recognition of an interference signal can be avoided.

In a possible form of embodiment of the inventive method for operation of an MRI scanner, the MRI scanner has a patient tunnel, a first receiving antenna for receiving a magnetic resonance signal from a patient in the patient tunnel, a second receiving antenna for receiving a signal with the Larmor frequency of the magnetic resonance signal and a receiver, wherein the second receiving antenna is arranged outside the patient tunnel or in the vicinity of an opening of the patient tunnel. The method has the step of receipt of an interference signal by the receiver via the second receiving antenna. Through the arrangement of the second receiving antenna, said antenna is more sensitive to signals outside the patient tunnel, which merely because of their spatial origin cannot be magnetic resonance signals. Basically the signal of the second receiving antenna can basically also have small portions of a magnetic resonance signal, but which because of their small portion can be not considered initially for the interference suppression or can be further reduced or avoided with means and methods specified in dependent claims.

In another step, the receiver receives a magnetic resonance signal via the first receiving antenna. In this case the signal that is primarily used for image acquisition is referred to as the magnetic resonance signal. For example the first receiving antennas can involve local coils on the body of the patient. The magnetic resonance signal can contain portions of the interference signal, which are to be further reduced with the inventive facility or method as described below.

In a further step, the received magnetic resonance signal of the first receiving antenna is discarded depending on the interference signal received by the second antenna. For example the interference signal received by the second receiving antenna can lie above a threshold level, so that despite the propagation attenuation between location of the second receiving antenna and location of the first receiving antenna, a fault is to be expected from the image obtained from the magnetic resonance signal. The receiver or the control of the MRI scanner can then discard the signal of the first receiving antenna. It is then conceivable for the MRI scanner subsequently to repeat the acquisition of the discarded signal.

In an advantageous way, an interference signal can already be recognized on the basis of the signal amplitudes by the different arrangement of first and second receiving antenna.

In a conceivable form of embodiment of the inventive method for operation of an MRI scanner having a Larmor frequency in an ISM band, the method has the step of determining an excitation pulse for excitation of nuclear spins in an examination object. The determination in this case takes place as a function of predetermined frequency limits of the ISM band. Preferably in this case the excitation pulse is determined in such a way that it only has spectral portions outside the ISM band below predetermined threshold values. The restriction to the ISM band can be achieved for example by the measures described for claims given below.

In another step of the method, the MRI scanner emits the excitation pulse.

In a further step of the method the MRI scanner receives a magnetic resonance signal and in another step establishes a mapping of a distribution of nuclear spins in the examination object. The mapping can subsequently be output on a display.

Within the ISM band, markedly higher limit values for radio waves emitted into the environment are usually allowed. Excitation pulses, depending on slice density and duration can be so wideband that they have portions outside the ISM band, even if the Larmor frequency lies within the ISM band. If this is avoided by the measures explained below, then additional measures such as an RF cabin can dispensed with, without exceeding the limit values.

In a possible form of embodiment of the inventive method the step of determining an excitation pulse has the sub-steps of determining an excitation pulse to excite the nuclear spins in a slice of the examination object as a function of a relative position of the slice for a magnet unit, of a predetermined gradient strength, of a thickness of a slice and of the type of measurement. This can take place for example by using parameterized libraries on excitation pulses.

In a further test step it is established by the MRI scanner whether the excitation pulse lies within the predetermined frequency limits. This can take place for example by spectral analysis by means of FFT.

If the excitation pulse does not lie within the predetermined frequency limits, the establishing steps are repeated. In these a pulse parameter is varied, which on establishing the excitation pulse has an effect on a spectral frequency distribution of the excitation pulse.

If the excitation pulse lies within the predetermined frequency limits, it is emitted in a further step by the MRI scanner.

In a conceivable form of embodiment of the inventive method, the pulse parameter with an effect on the establishing of the excitation pulse is one of the parameters duration of the excitation pulse, thickness of the slice, relative position of the slice or strength of the gradients. In other words, to obtain a different excitation pulse that lies within the ISM frequency band having the Larmor frequency of the MRI scanner, the duration of the excitation pulse, the thickness of the slice to be excited or also the position of the slice or the strength of the gradients can be changed for example. A simultaneous variation of a number of parameters is also conceivable.

By variation of one or more pulse parameters, an excitation pulse can be established in an advantageous way that does not exceed the limits of the frequency band and in this way makes operation within the permitted framework possible.

In a possible form of embodiment of the inventive method, the step of emission has the sub-step of altering the position of the examination object relative to the magnet unit before the step of emitting the pulse.

Through the gradient fields, it can occur at the edges of the FoV that the resonant frequency of the nuclear spins deviates more strongly from the average Larmor frequency of the MRI scanner established by the BO field. By repositioning the slice to be acquired more towards the isocenter of the BO field, with the same bandwidth of the excitation pulse, a complete excitation of a slice can be obtained, without departing from the band limits of the ISM band.

In a possible form of embodiment of the inventive MRI scanner, the MRI scanner has a control unit for controlling the image acquisition, which in particular can influence parameters of the image acquisition such as time of the excitation pulse and/or time of the acquisition of the magnetic resonance signal or also frequency of the excitation pulse and/or frequency range of the receiver on receipt of the magnetic resonance signal. Furthermore the MRI scanner has an interface connected to the control unit for signaling. The interface, as explained below, can be an interface for exchange of data with other magnetic resonance systems or also a radio frequency interface. The control unit is designed to synchronize an image acquisition as a function of a signal received by another MRI scanner via the interface. Synchronization here is seen as any activity that reduces mutual interference. This can comprise time coordination, but also for example a change of frequencies.

In an inventive MRI scanner, the control unit can also be designed to transmit a signal with information about an impending image acquisition to another MRI scanner. This feature, in a similar way to a plug and socket connection, supplements the aforementioned MRI scanner, which is designed to receive a signal from another MRI scanner. The information preferably relates to a time of emission and/or frequency of an excitation pulse. Preferably an inventive MRI scanner, as explained below, is designed both for transmitting and also for receiving a signal. The MRI scanner will also be referred to below as the first MRI scanner.

A signaling connection can also be established between the inventive first MRI scanner and a second inventive MRI scanner. The first MRI scanner and the second MRI scanner each have an interface and a control unit for this purpose. The first MRI scanner and the second MRI scanner are connected for signaling via the interfaces. The signal connection makes it possible at least to transmit a signal from the first MRI scanner to the second MRI scanner, but a bidirectional exchange of information is also conceivable. Point-to-point connections on an electrical, optical or wireless path are conceivable. Networks such as LAN, WAN, specifically TCP/IP, are also possible as a signal connection. The control unit of the first MRI scanner is designed to transmit information for an impending image acquisition process via the interface to the second MRI scanner. A time of a planned emission of an excitation pulse in absolute time or relative to the signal, or also to the frequency of a frequency range of the excitation pulse is conceivable. The control unit of the second MRI scanner is designed in this case to receive the information via the interface and to carry out an image acquisition as a function of the received information. For example the control of the second MRI scanner can be designed to shift the acquisition of a magnetic resonance signal, i.e. a sequence or a part thereof, in time so that it does not disturb the excitation pulse of the first MRI scanner. The second MRI scanner is also referred to below as the other MRI scanner.

The inventive method for operation of an MRI scanner can also be expanded for operation of a first MRI scanner with a control unit for controlling the image acquisition and an interface connected to the control unit for signaling. The method then has the step of receipt of a signal by the control unit via the interface from a second MRI scanner. This can involve an explicit exchange of information, in which the first MRI scanner receives information or a message from the second MRI scanner via a data interface, which features parameters such as time and/or frequency of an intended image acquisition. It is also conceivable however for the first MRI scanner to monitor the environment for example via a receiver for magnetic resonance signals.

In another step the control unit of the first MRI scanner sets a parameter of the image acquisition as a function of the received signal. It is for example conceivable for a sequence to be shifted in time.

In a further step, an image acquisition according to the parameter set is carried out by the first MRI scanner. For example the sequence can be begun at a changed point in time, so that the excitation pulses of both MRI scanners occur at the same time or the excitation pulse of the first MRI scanner occurs at a point in time at which the second MRI scanner is not receiving any image-relevant magnetic resonance signals.

In an advantageous way, the inventive MRI scanner, in conjunction with a second MRI scanner and the method for operation, enable mutual interference by two MRI scanners during simultaneous operation to be reduced.

In a possible form of embodiment of the inventive MRI scanner, the interface is designed for the exchange of data. In other words, the first MRI scanner is designed both to transmit data via the interface both to a second MRI scanner and also to receive data via the interface data from a second MRI scanner. In this case the control unit is designed, by means of exchange of information via the interface, to synchronize an image acquisition with a second MRI scanner. In other words the control units agree between themselves by messages how the image acquisition takes place, so that mutual disruptions are reduced.

In a conceivable form of embodiment of the inventive MRI scanner, the signal has information about a time and/or frequency of a transmit process. The time in this case can be specified in absolute terms for example or relative to the time at which the message was sent. A mid frequency and/or a bandwidth, a frequency range or also a channel specification that encodes a frequency range can be given as a specification.

In a possible form of embodiment of the inventive method for operation of a first MRI scanner and a second MRI scanner, the method furthermore has the step of establishing information about an impending image acquisition of the second MRI scanner by a control unit of the second MRI scanner and in a further step of transmitting a signal with the information to the first MRI scanner.

For example the control unit can receive via the interface a message from a second MRI scanner that said scanner will transmit an excitation pulse with a mid frequency equal to the Larmor frequency+100 kHz with a bandwidth of 200 kHz in 2 seconds. The first MRI scanner can then for example interrupt a sequence before its own excitation pulse and continue after the second MRI scanner has ended its sequence, or transmit the next excitation pulse simultaneously with the excitation pulse of the second MRI scanner. In an advantageous way mutual disruption by an excitation pulse of the second MRI scanner during a receive phase can be avoided in this way.

In a possible form of embodiment of the inventive MRI scanner, the signal has information about a time and/or frequency of a receive process. The information can specify a beginning or a duration and frequency for example, as to how there will be receiving from the second MRI scanner beginning in a second for 2 seconds at a mid frequency equal to the Larmor frequency minus 300 kHz with a bandwidth of 200 kHz. The first MRI scanner can then for example interrupt a sequence in such a way that it does not transmit an excitation pulse in this time in the said frequency band.

In an advantageous way, even on receipt of a message about a planned receipt in other units, an emission of the first MRI scanner can be shifted so that a disruption is reduced.

In a possible form of embodiment it is conceivable for the control unit of the first MRI scanner to be designed to change the frequency of an image acquisition process as a function of the received information. For example it is conceivable for an image acquisition to comprise different slices, wherein these are differentiated by a gradient magnetic field in the z-axis and thus in the effective Larmor frequency of the magnetic resonance signal. In this way a simultaneous operation with reduced interaction is possible, provided the order of the slices in the image acquisition is arranged so that there is never an acquisition in the same frequency range in both systems.

In an advantageous way, the differentiation via the frequency makes possible a simultaneous acquisition of the magnetic resonance signals in adjacent MRI scanners and thus a better use of the examination time.

In a conceivable form of embodiment of the inventive MRI scanner, the first MRI scanner has a receiver as the interface. A receiver here is seen in particular as a receiver for magnetic resonance signals including an antenna such as a local coil or body coil. In this case the first MRI scanner is designed to acquire an excitation pulse of a second MRI scanner outside an image acquisition and to carry out the image acquisition as a function of the acquired excitation pulse. For example it is conceivable for the first MRI scanner then initially to acquire or wait for magnetic resonance signals of a slice with another effective Larmor frequency, until a maximum duration for an acquisition of magnetic resonance signals has elapsed in the second MRI scanner emitting the excitation pulse.

In this way, the synchronization can be undertaken in an advantageous way even without a data connection or changes in the second MRI scanner.

In a possible form of embodiment of the inventive method for operation of a first MRI scanner and a second MRI scanner, the method furthermore has the step of establishing information about an impending image acquisition of the second MRI scanner by a control unit of the second MRI scanner and in a further step of transmitting a signal with the information to the first MRI scanner.

Basically it is also conceivable for the different measures described to be combined with one another. A protocol for an exchange of information in two MRI scanners can also be provided, through which the image acquisitions from both systems are interleaved with one another in an optimized way, so that the duration of the acquisition only changes slightly without any mutual disruptions occurring. In the simplest case all excitation pulses could be undertaken at the same time for example, provided an image acquisition is taking place in both MRI scanners in the same period of time.

The characteristics, features and advantages described above as well as the manner in which these are achieved will become clearer and easier to understand in conjunction with the description given below of the exemplary embodiments, which will be explained in greater detail in conjunction with the drawings, in which:

FIG. 1 shows a schematic diagram of an MRI scanner with the inventive facility;

FIG. 2 shows a schematic diagram of the receiver and the first receiving antenna and the second receiving antennas;

FIG. 3 shows a schematic diagram of a flowchart of a form of embodiment of the inventive method;

FIG. 4 shows a schematic diagram of a radio frequency unit of an inventive MRI scanner;

FIG. 5 shows a schematic diagram of an inventive MRI scanner surrounded by a waveguide;

FIG. 6 shows a schematic diagram of an inventive MRI scanner with an interference suppression transmitter;

FIG. 7 shows a schematic diagram of a flowchart of a part aspect of the inventive method;

FIG. 8 shows a schematic diagram of a flowchart of a part aspect of the inventive method;

FIG. 9 shows a schematic diagram of a flowchart of a part aspect of the inventive method;

FIG. 10 shows a schematic diagram of a flowchart of a part aspect of the inventive method;

FIG. 11 shows a schematic diagram of an inventive MRI scanner, in a network with further MRI scanners;

FIG. 1 shows a schematic diagram of a form of embodiment of an MRI scanner 1 with an inventive local coil 50.

The magnet unit 10 has a field magnet 11, which creates a static magnetic field BO for alignment of nuclear spins of samples or of the patient 100 in a recording region. The recording region is characterized by an extremely homogeneous static magnetic field BO, wherein the homogeneity relates in particular to the magnetic field strength or the amount. The recording region is almost spherical and is arranged in a patient tunnel 16, which extends in a longitudinal direction 2 through the magnet unit 10. A patient couch 30 is able to be moved in the patient tunnel 16 by the drive unit 36. Usually the field magnet 11 involves a superconducting magnet, which can provide magnetic fields with a magnetic flux density of up to 3T, with the latest devices even beyond this. For lower field strengths however permanent magnets or electromagnets with normally conducting coils can be used.

Furthermore the magnet unit 10 has gradient coils 12, which are designed for spatial differentiation of the acquired imaging regions in the examination volume by superimposing on the magnetic field BO variable magnetic fields in three spatial directions. The gradient coils 12 are usually coils made of normally conductive wires, which can create fields orthogonal to one another in the examination volume.

The magnet unit 10 likewise has a body coil 14, which is designed to irradiate a radio frequency signal supplied via a signal line into the examination volume and to receive resonant signals emitted from the patient 100 and output them via a signal line.

A control unit 20 supplies the magnet unit 10 with the various signals for the gradient coils 12 and the body coil 14 and evaluates the received signals.

In this way the control unit 20 has a gradient controller 21, which is designed to supply the gradient coils 12 with variable currents via supply lines, which when their timing is coordinated, provide the desired gradient fields in the examination volume.

Furthermore the control unit 20 has a radio frequency unit 22, which is designed to generate a radio frequency pulse with a predetermined temporal course, amplitude and spectral power distribution to excite a magnetic resonance of the nuclear spins in the patient 100. In this case pulse powers in the kilowatt range can be achieved. The excitation pulses can be irradiated into the patient 100 via the body coil 14 or also via a local transmit antenna.

A controller 23 communicates via a signal bus 25 with the gradient control 21 and the radio frequency unit 22.

A local coil 50 is arranged on the patient 100 as a first receive coil, which is connected to the radio frequency unit 22 and its receiver via a connecting line 33. It is also conceivable however for the body coil 14 to be a first receiving antenna in the sense of the invention.

Arranged at an edge of the opening of the patient tunnel 16 are four second receiving antennas 60, which are arranged at the corners of a square, which is encompassed by the circular opening, so that the corners lie on the edge of the opening. The four second receiving antennas 60 are connected to the receiver 70 of the radio frequency unit 22 for signaling. As a result of the plurality of second receiving antennas 60 it is conceivable in this case for these not to all have an omnidirectional receive characteristic, but to be dipoles for example and to supplement each other to form an omnidirectional receive characteristic by their different alignment. It would also be conceivable however for example to provide a crossed-dipole as a single second antenna with omnidirectional receive characteristic.

It is also possible, as an alternative or in addition, for a second receiving antenna 60 to be arranged in the patient couch 30.

The patient tunnel in this case preferably has a radius R for which the following applies:

R<(Lambda_L*1.841)/(2*Pi)

Lambda_L in this case specifies the wavelength of a radio wave in air at the Larmor frequency of the MRI scanner 1. If the radius R is less than the right-hand term, then the radio wave propagates exponentially attenuated in the patient tunnel 16 and the interference signal is heavily attenuated in the middle in the examination region FoV. Lambda_L is also referred to as the limit wavelength of a round hollow conductor, the associated frequency as the limit frequency.

Only the patient 100 acts through their finite conductivity as the core of the coaxial cable, the sheath of which is the wall of the patient tunnel 16, and passes on an electromagnetic signal coupled in at the legs or the top of the head into the examination region. In an advantageous way the second receiving antenna 70 or the second receiving antennas 70 arranged in the vicinity of the opening or in the patient couch 30 in this case receive the interference signal passed on from the patient 100 into the FoV and thereby make the compensation in the receiver 70 especially effective.

FIG. 2 shows a schematic diagram of the functional units of a possible form of embodiment of a receiver 70.

The summation device 71 weights the signals entering from the first receiving antenna or local coil 50 and from the second receiving antennas 60 with parameters, which can also be complex, in order to specify a phase displacement. In an analog receiver 70 this can take place by an adjustable amplifier in conjunction with an adjustable phase shifter. The real part of the parameter then corresponds to the amplification factor and the imaginary part of the phase displacement. Subsequently, in a preferred form of embodiment the weighted signals are summed, but other non-linear signal operations for combination of the individual signals are also conceivable.

An interference suppression controller 72 receives the combined signal and also the individual signals of the first receiving antenna and the second receiving antennas 60. In order to determine a portion of the interference signal in the combined signal, it is conceivable for example for the interference suppression controller 72 to undertake an autocorrelation of the signals. However it is also conceivable for the energy of the combined signals to be determined. In a conceivable form of embodiment the interference suppression controller 72 determines the portion of the interference signal in sections of sequences of the MRI scanner in which no magnetic resonance signal for imaging is expected, so that the combined signal only has the interference signal. This can be the case for example in dephased sections of an echo sequence, since the amplitudes of individual nuclear spins cancel each other out because of their different phase and do not generate any signal overall.

The interference suppression controller 72 then optimizes the parameters in the summation device according to a Least Square Root (LSR) method for example, so that the portion or the energy of the interference signal in the combined signal is minimized.

Basically the receiver 70 can be designed both in analog signal processing technology, so that for example gain control and phase displacement are controlled by a parameter and then converted using analog means, or also as a digital receiver, which either already receives digitized signals from the first receiving antenna and/or the second receiving antenna 60 or already digitizes said signals at the signal input by means of an A/D converter.

For imaging, the receiver 70 forwards the combined signal, in which the interference signal is very largely suppressed, to the controller 23 of the MRI scanner.

In this case it is also possible for the bandwidth of the interference signal to be wider than the magnetic resonance signal. The portions outside the frequency range of the magnetic resonance signal usually correlate in this case with the portions within the frequency range of the magnetic resonance signal. Therefore it can also be sufficient in accordance with the invention for the second receiving antenna 60 to receive the wideband interference signal only in part, for example in a frequency range that is not the same as or is outside the frequency range of the magnetic resonance signal. In addition or as an alternative the receiver 70 can also be designed only to accept frequencies in this frequency range from the second receiving antenna. The receiver 70 is designed in this case, depending on this part signal, to suppress the interference signal in a magnetic resonance signal received by the first receiving antenna. Because of the correlation for example the amplitude of the frequency components of the interference signal in the frequency range of the magnetic resonance signal can be linked with an amplitude outside the frequency range. In this way it is also conceivable for the second receiving antenna 60 in conjunction with the receiver 70 only to monitor frequency components outside the frequency range of the magnetic resonance signal for interference signals during an MRI scan and to suppress the interference signal in the signals of the first receiving antenna as a function thereof. It would be possible in this case for example for the receiver 70 to establish a relationship between interference signal from the first receiving antenna and interference signal portion from the second receiving antenna 60, also referred to as the transfer function, for an interference signal in the frequency range of the magnetic resonance signals between acquisitions of magnetic resonance signals and during the acquisition of magnetic resonance signal for example to adapt the amplitude or scaling of received portions of the interference signal on the basis of the second receiving antenna outside the frequency range of the magnetic resonance signal.

In another conceivable form of embodiment of the inventive MRI scanner (1), the interference signal is not suppressed in the receive signal in real time, i.e. not immediately on receipt of the interference signal and/or of the magnetic resonance signal, but the magnetic resonance signal and the interference signal are stored by the receiver 70, which in this case can also comprise parts of the controller 23 of the MRI scanner 1 or of an image evaluation unit, in a memory. The steps set out below for the method then no longer take place in real time or almost in real time, but can be carried out on the stored data with a delay, for example in advance of an image evaluation.

In this case for example a combination of receipt with the second antenna outside the frequency band of the MR signal with a real time interference suppression or a suppression at a separate point in time, for example during image evaluation, is conceivable.

The interference suppression in the receiver shown in FIG. 2 can also be carried out with a single second antenna 60. Conversely it is possible for the receiver 70 to have a number of channels or for a number of receivers 70 to be provided in the MRI scanner 1, in order to suppress interference in the magnetic resonance signals of a number of local coils 50. In this case it is conceivable for the signals of the second receiving antennas 60 in this case to be used by a number of receivers 70 or channels of the receiver 70 for interference suppression.

In this case it is both conceivable for the dependence between the interference signal received by the second antenna and the interference suppression to be linear and also non-linear. Linear dependencies in this case can be a phase displacement about a value determined or a linear scaling with a value determined from the signal of the second antenna. It is also conceivable however for the transfer function for the interference signal to have non-linearities on the path from the first receiving antenna and/or second receiving antenna, for example through mixers or non-linear amplifiers, so that non-linear operations for interference suppression in the receiver 70 must also be applied to the interference signal received by the second receiving antenna 60.

FIG. 3 shows a schematic flowchart of an inventive method.

In a step S10, the receiver 70 receives an interference signal via the second receiving antenna 60 or via the plurality of second antennas 60. The interference signal is transmitted via a signal connection to the receiver 70. In this case it is also conceivable for the interference signal to be digitized first of all by an A/D converter, before it is transmitted to the receiver 70, embodied in this case as a digital receiver 70.

In a step S20, the receiver 70 receives a magnetic resonance signal via the first receiving antenna, for example the local coil 50. With a number of local coils 50, correspondingly more receivers 70 can be provided or also one receiver 70 with a number of channels, each with a summation device 71. The interference suppression controller 72 in this case can be provided separately in each case or also jointly, which can speed up the subsequent setting or similar parameters for different channels.

In a step S30, the receiver 70 processes the magnetic resonance signal as a function of the interference signal or the interference signals with a number of second receiving antennas 60 into one receive signal. For example the interference signal or signals of the second receiving antenna or second receiving antennas 60 and the magnetic resonance signal of the first receiving antenna are weighted with different parameters and delayed and subsequently combined. This can be the creation of a linear combination for example. The created receive signal or sum signal depends in this case on one or more parameters.

In another step S40, the parameter or the parameters are set by the receiver 70, in particular by the interference suppression controller 72 in such a way that a portion of the interference signal in the receive signal is reduced. If for example the interference signal received by the second receiving antenna 60 is scaled by the parameters set so that it has the same amplitude as the interference signal portion received via the first receiving antenna and if it is provided with a phase displacement relative thereto of 180 degrees, then the interference signal in the created signal is exactly canceled out. The parameter or the parameters can be established in this case via optimization methods such as for example Least Square Root (LSR) or Wiener filter.

The step S40 in this case can also have the sub-step S41, to form a temporal average value and to set the parameter for interference suppression as a function of this average value. For example an amplitude or phase of the interference signal can be averaged in order to compensate for statistical fluctuations and introduce less interference into the magnetic resonance signal through the interference suppression.

In this case it is also conceivable for the steps S10 to S30 to be carried out in each case on received magnetic resonance signals and received interference signals in real time, in particular with analog receivers 70. However it is also conceivable for the steps S10 to S30 to be carried out in each case on stored interference signals and magnetic resonance signals, which are digitized for example for an individual sequence or individual sections thereof.

In a possible form of embodiment of the inventive method the step S40 is carried out with interference signals from a period of a sequence in which no magnetic resonance signal for imaging is received. For example the parameters can be determined with interference signals of the second receiving antenna 60 and a signal of the first receiving antenna in a time section of the interference suppression controller 72 in which the nuclear spins are dephased and create no magnetic resonance signal. However it is also conceivable in this time section without magnetic resonance signal for the interference signal and the signal of the first receiving antenna to just be acquired digitally and evaluated later.

In this case it is conceivable in a step S50 for the interference suppression controller 72 to monitor the interference signal for changes, for example different amplitude, frequency or phase. On detection of such a change or if the change exceeds a predetermined threshold value, the interference suppression controller 72 can modify the steps S10 of receipt of interference signal and S20 receipt of the magnetic resonance signal as well as the setting of a parameter for interference suppression as a function of the received interference signal in a step S51, in order to adapt the interference suppression to the changed interference signal.

Basically it is also conceivable in a form of embodiment of the inventive method for the received interference signal and/or magnetic resonance signal to be stored by the receiver 70 in a step S25. In this case the receiver 70 can also comprise parts of the controller 23 of the MRI scanner 1 or an external image evaluation processor. The steps S20 to S40 are carried out retroactively in this case, for example at the end of an echo sequence, an excitation sequence, a signal acquisition for a slice of the examination object or also after acquisition of all data.

The decoupling of the signal acquisition from interference signal and magnetic resonance signal from the interference suppression thus make it possible in an advantageous way to employ lower-cost components with lower computing power or also to use existing resources, e.g. from the image evaluation, twice. It is also then conceivable to compare and select different parameter settings or optimize them retrospectively. The application can also be limited to periods of time with disruptions.

FIG. 4 shows a schematic diagram of a radio frequency unit of an inventive MRI scanner. The diagram in this case does not show all details of the radio frequency unit, but only those relevant for an inventive interference suppression on the transmit path.

The transmit path of the radio frequency unit 22 in this case has a pulse generator 220, a preliminary interference suppressor 221, a power amplifier 222 and an ISM filter 223.

The pulse generator 220 can have an oscillator, a modulator and a mixer for example, with which a pulse is generated in the baseband is then converted to the Larmor frequency.

The preliminary interference suppressor 221 is designed for preliminary interference suppression of an excitation pulse for excitation of the nuclear spins in such a way that portions of the signal of the excitation pulse outside the ISM band are reduced compared to an excitation pulse without preliminary interference suppression. It is conceivable for example for preliminary interference suppressor 221 to create and mix-in signal portions that, after an amplification by the power amplifier, correspond to harmonics created by the non-linearity of the power amplifier from the excitation pulse, but have a reversed sign and in this way reduce or extinguish the harmonics. The same is conceivable for intermodulations of signal portions by the non-linearity. The preliminary interference suppressor 221 in this case can be realized for example in a digital signal creation or also corresponding signals are created from an input signal for a power amplifier by analog components. It is also conceivable for the preliminary interference suppressor 221 to be integrated in a digital pulse generator 220 for example.

The output signal of the preliminary interference suppressor 221 is amplified in the power amplifier 222. A power amplifier 22 with a linear characteristic curve is conceivable here. It is also possible however for the preliminary interference suppressor 222 to change the input signal of the power amplifier 222 in just such a way that, after amplification by the power amplifier 222, a signal is generated without unwanted harmonics. In other words the characteristic curve of the preliminary interference suppressor 221 multiplied by the characteristic curve of the power amplifier 222 ideally gives a linear characteristic curve, so that the system consisting of preliminary interference suppressor 221 and power amplifier 222 amplifies a pulse of the pulse generator without unwanted harmonics.

The preliminary interference suppressor 221, in one form of embodiment, as shown in FIG. 4 by the dashed line from the output of the ISM filter 223, can also be adaptive in the sense that, by monitoring the output signal of the power amplifier 222, it adapts the preliminary interference suppression, so that the overall system, consisting of preliminary interference suppressor and power amplifier, has a linear characteristic.

Subsequent to the power amplifier 222 the signal is preferably still filtered by an ISM filter 223. The filter in this case preferably suppresses frequency components outside the ISM band that the MRI scanner 1 needs for image acquisition. For example the filter can involve a bandpass filter for the ISM band used that attenuates frequencies outside the ISM band by more than 12 dB, 24 DB, 40 dB or 60 dB relative to a signal with minimal attenuation within the ISM band. A lowpass is also possible. Depending on the radio frequency generation of the MRI scanner the filter can be arranged for example between power amplifier 222 and a hybrid coupler not shown, between hybrid coupler and a transmit/receive switch not shown or between transmit/receive switch and transmit antenna.

In a form of embodiment the MRI scanner also has tuning elements for the transmit antenna. These can be PIN diodes for example, but also other diodes or active components such as transistors or FETs. These tuning elements are provided in order to tune the transmit antenna in the case of receipt and to avoid interactions with the receiving antennas. The tuning elements usually have non-linear characteristic curves can therefore generate harmonics during transmission. In a preferred form of embodiment the ISM filter 223 is therefore arranged between the tuning elements and the transmit antenna.

The non-linear components are also preferably arranged in an area of the MRI scanner screened off from the patient tunnel for radio frequency.

Thus the arrangement of the non-linear components contributes to adherence to irradiation limit values and makes possible or simplifies dispensing with screening of the entire MRI scanner with a radio frequency cabin.

Shown schematically in FIG. 5 is a form of embodiment of an inventive MRI scanner 1, surrounded by a waveguide. The waveguide 260 can be provided in this case by any electrically conductive surface surrounding the outer circumference of the MRI scanner 1 in at least 4 spatial directions. An electrically conductive surface is seen here in particular as a metallic or metalized surface or mesh, which attenuates an electromagnetic wave with the Larmor frequency at a crossing by 60 dB, 80 dB, 100 dB or more. The conductivity of the surface in this case can also be anisotropic through geometrical subdivision such as slots, provided the conductivity in parallel to the electrical field vector of the alternating field is sufficient to achieve the attenuation.

Preferably in this case the surface forms the waveguide 260 as a tunnel around the MRI scanner e.g. in the form of a cylinder, cube, prism with a width that does not allow any formation of a free wave with Larmor frequency. With a cube this is the case for example if the longer dimension of the cross section is less than a half wavelength of an electromagnetic wave with the Larmor frequency. In other words, the cut-off frequency or limit frequency of the waveguide 260 is greater than the Larmor frequency. The electromagnetic field thereby falls exponentially with the distance from the source, so that alternating fields leaking out of the patient tunnel 16 fall rapidly. It is conceivable in this case for the waveguide 260 to be open at one or both ends, since the distance to the patient tunnel 16 means that the exponential attenuation is already strong enough to adhere to the limit values allowed in the ISM band.

It is also conceivable for the MRI scanner 1 to be surrounded by screening that has larger dimensions than the half wavelength. Then however, instead of a radio-frequency-tight door, a tunnel-shaped access opening 261 made of conducting material with a correspondingly small cross section to the MRI scanner 1 can be provided, the dimensions of which suppress the free propagation of the wave by a cut-off frequency greater than the Larmor frequency. The access opening 261 in this case is preferably connected electrically-conductively for radio frequency with the screening and/or the waveguide. In a form of embodiment the waveguide 260 is also connected electrically-conductively to the patient tunnel 16 for radio frequency.

FIG. 6 shows a schematic diagram of a form of embodiment of an inventive MRI scanner 1 with an interference suppression transmitter 80. Electrical waves or alternating waves are also able to be suppressed by electrical fields with the same frequency and amplitude amount, but opposite polarity or a phase displacement by 180 degrees. If amplitude amounts or phase do not match exactly, then at least a reduction by the destructive interference is achieved. An inventive MRI scanner 1 has interference suppression antennas 81 for creating these alternating fields for interference suppression, which are arranged around the source of the fields, here around the patient tunnel 16. Preferably the interference suppression antennas 81 cover all spatial directions around the opening and a symmetry is used, such as e.g. the same distances to the opening of the patient tunnel 16 and/or a distribution at the same angular distances to the opening in order to simplify an activation of the individual interference suppression antennas 81. Through amplitude and phase able to be set individually for each interference suppression antenna 81, however, any given distribution is also conceivable. Depending on the type of the alternating field, antennas with preferably an electrical field such as for example dipoles or with magnetic field such as for example transmit coils can also be involved here. The alignment of the antennas or the polarization of the field generated in this case is preferably oriented to the field direction of the alternating fields to be suppressed.

The signal that is transmitted from the interference suppression antennas 81 is intended to reduce the emission of the excitation pulse and must thus have a predetermined amplitude and phase relationship to the excitation pulse. Preferably the signals are therefore derived as analog signals or also from the digital pulse generation. It is however also conceivable to provide the signals through separate units independently of the pulse generation, provided the necessary amplitude and phase relationship is established.

In FIG. 6, a connecting line between the body coil 14 as source of the electromagnetic waves and the interference suppression transmitter is specified symbolically. A direct connection via a power distributor or for example a directional coupler would be conceivable, a sensor in the patient tunnel would also be possible for direct acquisition of the electromagnetic field. It would also be possible however to obtain a reference signal for creating the signal for interference suppression from the power amplifier 222 or the pulse generator 220.

The reference signal for interference suppression derived from the excitation pulse is subsequently delayed or phase-shifted by adjustable phase shifters 82 for the individual interference suppression antennas 81 and subsequently has its amplitude amplified by adjustable amplifiers 83, before it is transmitted via the interference suppression antennas 81.

The phase shifters 82 and the amplifiers 83 are adjusted in this case by an interference suppression controller 84 via a signal connection. It is conceivable in this case for the interference suppression controller 84 to set predetermined phase shifts and amplitudes, which are established for example during the installation of the MRI scanner 1.

It is also possible however for the adjustment to take place by a calibration measurement. In this case it is conceivable for a calibration receiver 85 to record the alternating field to be suppressed by means of one or preferably more calibration elements 86 distributed in the room. At the same time the calibration receiver 85 acquires the signals supplied to the interference suppression antennas 81 and transfers the acquired values to the interference suppression controller 84. The interference suppression controller 84 can then for example adjust the interference suppression controller 84 by a linear optimization method such as LSR of the phases and amplitudes of the individual interference suppression antennas in such a way that, at the location of the calibration antennas 86 the field strength is zero. If the n calibration elements 86 are distributed across the spatial angle then the resulting alternating field from body coil 14 and interference suppression antennas 81 can be changed to a multipole field with n zero points or radiation areas, which decrease at a higher power with distance and make an effective suppression possible.

Basically in this case the propagation of the fields is reversible. For calibration it would also be conceivable for the calibration element or elements 86 to transmit a signal and for the body coil 14 and the interference suppression antennas 84 to receive the signal and then for the interference suppression controller 84 to establish a suitable phase relationship and amplitudes.

Moreover, the calibration element 86 could also be used for transmitting a reference signal for receive interference suppression. In this case the reference signal would have to be encoded or modulated so that it is able to be distinguished from a magnetic resonance signal by the receiver 70. This could for example also be achieved below the interference limit of the magnetic resonance signal with a spread-spectrum modulation. Also conceivable would be a transmission in an adjacent frequency range. In this case it is necessary for the receiver 70 to be able to establish a correlation between the reference signal and the signals received via the second and first receiving antennas, in order to optimize the interference suppression. In this way settings for suppression of interference signals from specific directions could be determined for example.

FIG. 7 shows a schematic of a flowchart of a possible form of embodiment of an inventive method for operation of the inventive method. In FIG. 7, the aspect of how an excitation pulse has to be designed and transmitted is considered in particular, in order to adhere to regulatory limit values for radio frequency radiation even without a screening cabin, in particular when the Larmor frequency lies in an ISM band. The steps of an inventive method already explained in FIG. 3 are summarized in FIG. 7 under step S130 and are not explained once again. However it is basically also possible to implement the measures explained for FIG. 7 for limiting emission during the excitation pulse even without the receive interference suppression from FIG. 3.

In a step S110 an excitation pulse for excitation of nuclear spins in an examination object is determined by the controller 23. To do this, first of all, in a step S111 an excitation pulse for excitation of the nuclear spins in a slice of the examination object is established by the controller 23. This can take place for example as a function of the selected sequence or type of examination by selecting from a library of excitation pulses. The frequency, the duration, the power and the spectral distribution in this case depend on a number of parameters. The mid frequency is produced from the nuclear spins to be acquired, the strength of the homogeneous static magnetic field BO, the location of the slice in relation to the gradient field and also the strength of the gradient field. The spectral distribution and bandwidth for its part is produced from the strength of the gradient field and the thickness of the slice in the direction of the field gradients. The amplitude for its part depends on the duration of the excitation pulse, the volume to be excited and the desired excitation strength, also referred to as the flip angle. In this case, in sub-step S111, a set of parameters is determined as a function of these boundary conditions, which describe a possible excitation pulse for these boundary conditions. It is conceivable for a library or table of different sets of parameters to be specified for specific standard situations, such as for example acquiring images of specific organs, and to be selected from it.

In a further sub-step S112 a check is performed by the controller 23 as to whether the established excitation pulse lies within the predetermined frequency limits. In the simplest case the highest and the lowest frequency of the excitation pulse can be computed for example with the aid of the mid frequency and the spectral frequency distribution. It is also conceivable in this case to compute the power distribution and assess limit values for a frequency-dependent power.

The sub-step S111 is repeated if it is determined in the assessment that the established excitation pulse exceeds limit values, in particular limit values for an allowable emission of radio frequency power. This relates above all during operation of the MRI scanner in an ISM band to an emission outside the ISM band that is subject to greater restrictions.

In this case, parameters that influence this are varied on repetition of sub-step S111. A longer pulse can achieve the same excitation with a lower power for example. With a smaller gradient a smaller frequency bandwidth is required in order to excite the same slice thickness.

If the excitation pulse established in sub-step S111 adheres to the limit values, then it is transmitted in a step S120 of the method by the radio frequency unit 22.

In a step S130, as already described for FIG. 3 in an exemplary form of embodiment, the magnetic resonance signal is received by the receiver 70.

Subsequently, in a step S140, a map of a distribution of nuclear spins by the controller 23 from the received magnetic resonance signal is established. Preferably the mapping is finally reproduced on a display.

FIG. 8 shows a schematic of a flowchart of a further sub aspect of the inventive method shown in FIG. 3, here a possible interference suppression by previously acquired image information.

In this case the receiver 70 receives in a step S21 a first received magnetic resonance signal and stores it in a memory. In this case it is also conceivable for the signal acquired in step S21 to originate from a calibration measurement or a pre-scan that has also been acquired with other parameters or a lower resolution.

In a further step S22 the receiver 70 receives a second received magnetic resonance signal and stores this. Preferably the second magnetic resonance signal involves a signal for an image acquisition.

In a step S23 the first received magnetic resonance signal and the second received magnetic resonance signal are compared. This can already take place in the raw data for example or not until the image space, for example after a Fourier transform. In a preferred form of embodiment the comparison is undertaken on a row basis in the k-space. If the first magnetic resonance signal and the second magnetic resonance signal differ significantly, in particular if a possibly different recording situation has already been taken into consideration in the comparison, then with a deviation that is to be attributed to external interference an interference suppression measure is performed. Interference signals can be characterized by the frequency, amplitude or a characteristic curve or duration for example.

An interference suppression measure in this case can be a repetition of the acquisition for example that, in particular for a row in the k-space, leads to shorter delays. It is also conceivable to set the signal to zero, above all if it should involve a region from which no image signal is to be expected.

FIG. 9 shows a schematic of a flowchart of a further sub aspect of an inventive method for interference suppression, here a possible interference suppression by analysis of the acquired image information in an image space.

In this possible form of embodiment of the inventive method, the magnetic resonance signal is investigated in the image space to detect the interference signal and to define the parameters for interference suppression. To do this, in a sub-step S42, the received magnetic resonance signals are transformed by the controller 23 in an image space, for example by a Fourier transform. This step can also be performed like the subsequent steps on individual rows of the raw data space, so that a detection and correction can be performed more quickly.

In another sub-step S43, the interference signals are separated by the controller 23 from the magnetic resonance data. This is possible for example if regions in the image space can be determined by a segmentation from a pre-scan or other additional information about patient and location, at which no magnetic resonance signals from nuclear spins are to be expected. Signals arising there in the image space are then to be assigned to a disruption.

In a further sub-step S44, the interference signals are transformed back into a raw data space, for example by a further Fourier transform.

In another sub-step S45, the parameters for interference suppression can then be determined from the interference signals separated from the useful signal and transformed back in the raw data space, for example as phase and amplitude for destructive interference in the receiver from the signals of the first and second receiving antennas. It is also conceivable in this case for the steps of back transformation and the determination of parameters to be linked to one another, since frequency and phase in the raw data space are linked to the position in the image space.

FIG. 10 shows a schematic of a flowchart of a further sub aspect of an inventive method for interference suppression, which establishes transfer functions between first receiving antennas and second receiving antennas 60 with one or more additional calibration elements 86.

In a sub-step S80 in this case a transfer function between a first receiving antenna and the calibration element 86 is established. For this it is conceivable for a signal to be transmitted by the interference suppression controller via the calibration element 86 with the coordination of controller 23, which is received and evaluated by the first receiving antenna. Preferably the signal is encoded by means of pseudo random sequence or in another way in such a way that a correlation between sent and received signal can be easily established by the receiver 70.

In a sub-step S82 a transfer function between a first receiving antenna and the calibration element 86 is established in the same way. For this it is conceivable for a signal to be transmitted via the calibration element 86 with the coordination of the controller 23 by the interference suppression controller, which is received by the second receiving antenna 60 and is evaluated in the receiver 70.

On account of the reversibility of the propagation of the electromagnetic fields signals could also be sent however by the first receiving antenna and the second receiving antenna 62, which will be received by the calibration element 86.

In another sub-step S82 at least one parameter for interference suppression as a function of the measured transfer functions is set in such a way that a portion of an interference signal received by the second receiving antenna 60 is reduced in a signal received by the receiver 70 via the first receiving antenna. For example it can be defined in each case via the transfer functions how an interference signal arrives from the direction of the calibration element 86 at the input of the receiver 70 via the first receiving antenna and the second receiving antenna 60, in particular with which amplitude and phase displacement. Thus for example an additional phase displacement can be set in receiver 70, so that the signals from first receiving antenna and second receiving antenna are superimposed destructively in the receiver and the fault is suppressed. As a further parameter, the amplification of the amplitude can be set so that there is an extinction for an interference signal from a point in space. With a number of first receiving antennas and second receiving antennas 60 more parameters or pairs of parameters are to be adapted accordingly, which can take place for example by linear optimization methods such as LSR.

Shown in FIG. 11 is an interaction between a number of inventive MRI scanners 1. In this case the control unit 20 of the first MRI scanner 1 receives a signal from a second MRI scanner 101 via an interface. The control unit 21 in this case is designed to synchronize an image acquisition as a function of a signal received via the interface from the second MRI scanner.

A number of possible forms of embodiment are shown simultaneously in FIG. 11. On the one hand the interface can be the LAN interface 26, via which the MRI scanner 1 is connected to the second MRI scanner 101 for signaling. Also conceivable however are all other interfaces for the exchange of information such as WIFI, WAN or serial or parallel point-to-point-connections.

In this case it is conceivable in a form of embodiment for the second MRI scanner 101 to transmit a message about a planned image acquisition with the signal. The message can for example specify that at a specific time t, at the frequency f, an excitation pulse of duration d will be sent by the second MRI scanner 101. The control unit 20 of the first MRI scanner 1 then synchronizes its own image acquisition as a function of this information.

One possibility is for the control unit 20 to synchronize its own excitation pulse in such a way that it occurs at the same time, since because of the extremely high field strengths that are required for excitation, the excitation pulses of adjacent MRI scanners, because of the attenuation already provided by the construction of the MRI scanners, do not disrupt one another.

More sensitive to disruptions on the other hand is the receipt of magnetic resonance signals from the examination volume or the patient 100. Since here an attenuation in relation to the excitation pulse of over 100 dB is present, an excitation pulse of an adjacent MRI scanner 101 can disrupt the receipt of MR signals even when screening is present. The control unit 20 of the MRI scanner 1 can therefore plan and carry out the image acquisition in such a way that this does not coincide with the excitation pulse of the second MRI scanner 101. For example own excitation pulses and the readout sequences dependent thereon can be applied so that the receipt windows of the first MRI scanner 1 do not coincide with the excitation pulses of the second MRI scanner 101.

In this case it is also conversely possible for second MRI scanner 101 to transmit information about a planned receipt. The message can for example specify that at a specific time t, at the frequency f for the duration d, an MR signal is to be recorded by the second MRI scanner 101. The first MRI scanner 1 can then set its own transmission process so that no transmission process takes place in the time window specified in the message, at least not on a frequency band that comprises the frequency f including a bandwidth specified in the message.

Finally combined messages are moreover conceivable, in which transmit and receive processes are agreed mutually between the first MRI scanner 1 and the second MRI scanner 101, preferably in such a way that the image acquisition devices can be executed with the least possible delay by interleaving.

In another form of embodiment, which is shown in FIG. 11, it is also conceivable however for the signal to be a radio wave of an excitation pulse itself and the interface for example the local coil 50 with the radio frequency unit 22. Preferably in this case receipt also or just takes place at times at which the first MRI scanner 1 is not itself recording an MR signal. On the basis of the excitation pulse the control unit 20 can detect that a second MRI scanner 101 has just transmitted an excitation pulse and therefore is then planning an acquisition of a magnetic resonance. It is then for example conceivable for the first MRI scanner 1 then not to transmit any excitation pulse itself for a certain time. It would also be possible for the first MRI scanner 1 to use the excitation pulse of the second MRI scanner 101 itself as a trigger pulse and to transmit its own excitation pulse almost synchronously, since usually pauses without receipt and thus possible mutual interference lie between excitation pulse and receipt of the magnetic resonance signal.

Regardless of whether the transmission of an excitation pulse is detected directly via the received electromagnetic field of the pulse or via a message via the data interface, it is also conceivable in this case for the control unit 20 to change the frequency of the next excitation pulse as a function of the signal. In MRI scanning individual slices in the direction of the BO field, usually along the z-axis 2, are differentiated by a superimposed gradient field in the z direction in their frequency and are thus able to be distinguished. The control unit 20 can for example change the order of the scanning of individual slices, so that the first MRI scanner 1 and the second MRI scanner 101 each acquire slices with different mid frequency and in this way crosstalk or interaction are avoided by the different frequencies. An additional degree of freedom that the control unit 20 can use in this case is also the location of the patient 100 on the movable patient couch 30 relative to the isocenter of the field magnet 10. By moving the patient 100 along the z-axis a little, the different location in relation to the z gradient field means that the Larmor frequency also changes for a slice. The first MRI scanner 1 can thus, by a relative movement of the patient along the z-axis, also acquire the same slice in the body of the patient 100 with different frequencies, so that an interaction with the second MRI scanner 101 can be avoided.

Although the invention has been illustrated in greater detail by the preferred exemplary embodiment, the invention is not restricted by the disclosed examples and other variations can be derived herefrom by the person skilled in the art, without departing from the scope of protection of the invention.

Claims

1. An MRI scanner, wherein the MRI scanner (1) has a patient tunnel (16), a first receiving antenna for receiving a magnetic resonance signal from a patient (100) in the patient tunnel (16), a second receiving antenna (60) for receiving a signal having the Larmor frequency of the magnetic resonance signal, and a receiver (70), wherein the second receiving antenna (60) is arranged outside or in the vicinity of an opening of the patient tunnel (16), wherein the receiver (70) is connected to the first receiving antenna and the second receiving antenna (60) for signaling and the receiver (70) is designed to suppress an interference signal received with the second receiving antenna (60) in a magnetic resonance signal received by the first receiving antenna.

2. An MRI scanner, wherein the MRI scanner (1) has a patient tunnel (16), a first receiving antenna for receiving a magnetic resonance signal from a patient (100) in the patient tunnel (16), a second receiving antenna (60) for receiving a signal close to the Larmor frequency of the magnetic resonance signal and a receiver (70), wherein the second receiving antenna (60) is arranged outside or in the vicinity of an opening of the patient tunnel (16), wherein the receiver (70) is connected to the first receiving antenna and the second receiving antenna (60) for signaling and the receiver (70) is designed to suppress a wideband interference signal received with the second receiving antenna (60) outside a frequency range of the magnetic resonance signal in a magnetic resonance signal received by the first receiving antenna.

3. The MRI scanner as claimed in claim 1 or 2, wherein the MRI scanner (1) is designed to receive magnetic resonance signals having a Larmor frequency in an industrial band.

4. The MRI scanner as claimed in claim 3, wherein the MRI scanner (1) has a transmit path for transmitting an excitation pulse with an ISM filter (223), wherein the ISM filter (223) is designed to suppress signals outside the ISM band.

5. The MRI scanner as claimed in claim 4, wherein the MRI scanner has a transmit antenna for transmitting an excitation pulse, wherein the MRI scanner (1) has non-linear components for tuning the transmit antenna, wherein the non-linear components are arranged in an area of the MRI scanner screened off for radio frequency from the patient tunnel, wherein the ISM filter (223) is arranged between non-linear component and antenna.

6. The MRI scanner as claimed in claim 3 with a radio frequency unit (22), wherein the radio frequency unit (22) has a preliminary interference suppressor (221), which is designed for preliminary interference suppression of an excitation pulse for excitation of nuclear spins in such a way that signal portions of the excitation pulse outside the ISM band are reduced compared to an excitation pulse without preliminary interference suppression.

7. The MRI scanner as claimed in one of the preceding claims, wherein a limit frequency for a propagation of a radio wave in the patient tunnel (16) is greater than a Larmor frequency of the MRI scanner (1).

8. The MRI scanner as claimed in one of the preceding claims, wherein the MRI scanner (1) has a waveguide (260) that surrounds the MRI scanner (1), wherein the waveguide (260) has a limit frequency that is greater than the Larmor frequency of the MRI scanner (1).

9. The MRI scanner as claimed in claim 8, wherein the waveguide (260) has an electrically conductive connection (262) to the patient tunnel (16).

10. The MRI scanner as claimed in one of the preceding claims, wherein the second receiving antenna (60) as arranged on an opening of the patient tunnel (16) or on the patient couch (30).

11. The MRI scanner as claimed in one of the preceding claims, wherein the second receiving antenna (60) has an omnidirectional receive characteristic.

12. The MRI scanner as claimed in one of the preceding claims, wherein the MRI scanner (1) has a plurality of second receiving antennas (60) and the receiver (70) is designed to suppress the interference signal in the magnetic resonance signal as a function of receive signals of the plurality of second receiving antennas (60).

13. The MRI scanner as claimed in claim 12, wherein the plurality of second receiving antennas (60) is arranged in an arrangement symmetrical to the patient tunnel (16).

14. The MRI scanner as claimed in one of the preceding claims, wherein the receiver (70) has an autocorrelation device and the autocorrelation device is designed to determine a portion of the signal received by the second receiving antenna (60) in the magnetic resonance signal received by the first receiving antenna.

15. The MRI scanner as claimed in one of claims 1 to 13, wherein the receiver (70) has an estimation device and the estimation device is designed to estimate a portion of the signal received by the second receiving antenna (60) in the magnetic resonance signal received by the first receiving antenna.

16. The MRI scanner as claimed in one of the preceding claims, wherein the MRI scanner (1) has an interference suppression transmitter (80) and an interference suppression antenna (81), wherein the interference suppression antenna (81) is arranged at a distance from the patient tunnel (16), wherein the interference suppression transmitter (80) is designed to output a signal in a frequency range of an excitation pulse of the MRI scanner (1) via the interference suppression antenna (81) as a function of a transmit interference suppression parameter so that, in a predetermined area of an environment of the MRI scanner (1), a field strength of the excitation pulse is reduced by destructive interference.

17. The MRI scanner as claimed in claim 16, wherein the MRI scanner (1) has a calibration element (86) in an environment of the MRI scanner (1) and an interference suppression controller (84), wherein the interference suppression controller (84) is designed to detect a field strength in a frequency range of an excitation pulse at the location of the calibration element (86) by means of the calibration element (86) and as a function of the field strength detected to set the transmit interference suppression parameter in such a way that a field strength of the excitation pulse is reduced in a predetermined environment of the calibration element (86).

18. The MRI scanner as claimed in claim 16 or 17, wherein the interference suppression transmitter (80) is designed to generate the signals for the interference suppression antenna (81) or interference suppression antennas (81) by phase displacement and/or amplitude adaptation as a function of one or more transmit interference suppression parameters.

19. The MRI scanner as claimed in one of claims 16 to 18, wherein the interference suppression antenna (81) has a radio frequency power amplifier.

20. The MRI scanner as claimed in one of the preceding claims, wherein the MRI scanner (1) has a calibration element (86) in an environment of the MRI scanner (1), wherein the receiver (70) is designed to measure a first transfer function between the first receiving antenna and the calibration element (86) and also a second transfer function between the second receiving antenna (60) and the calibration element (86) and, as a function of the measured first transfer function and the second transfer functions, to set the interference suppression parameter or parameters in such a way that an interference signal received with the second receiving antenna (60) is reduced in a magnetic resonance signal received by the first receiving antenna.

21. A method for operation of an MRI scanner (1), wherein the MRI scanner (1) has a patient tunnel (16), a first receiving antenna for receiving a magnetic resonance signal from a patient (100) in the patient tunnel (16), a second receiving antenna (60) for receiving a signal with the Larmor frequency of the magnetic resonance signal and a receiver (70), wherein the second receiving antenna (60) is arranged outside the patient tunnel (16) or in the vicinity of an opening of the patient tunnel (16) and wherein the method has the steps: (S10) Receipt of an interference signal by the receiver (70) via the second receiving antenna (60);(S20) Receipt of a magnetic resonance signal by the receiver (70) via the first receiving antenna;(S30) Processing of the magnetic resonance signal as a function of the interference signal by the receiver (70) to a receive signal, wherein the dependency is a function of a parameter;(S40) Setting of the parameter by the receiver (70), so that a portion of the interference signal is reduced in the receive signal.

22. A method for operation of an MRI scanner (1), wherein the MRI scanner (1) has a patient tunnel (16), a first receiving antenna for receiving a magnetic resonance signal from a patient (100) in the patient tunnel (16), a second receiving antenna (60) for receiving a signal close to the Larmor frequency of the magnetic resonance signal and a receiver (70), wherein the second receiving antenna (60) is arranged outside the patient tunnel (16) or in the vicinity of an opening of the patient tunnel (16) and wherein the method has the steps: (S10) Receipt of a frequency portion of the interference signal close to the Larmor frequency by the receiver (70) via the second receiving antenna (60);(S20) Receipt of a magnetic resonance signal by the receiver (70) via the first receiving antenna;(S30) Processing of the magnetic resonance signal as a function of the frequency portion of the interference signal by the receiver (70) to a receive signal, wherein the dependency is a function of a parameter;(S40) Setting of the parameter by the receiver (70), so that a portion of the interference signal is reduced in the receive signal.

23. The method as claimed in claim 21 or 22, wherein the step (S40) of setting the parameter has the step (S41) of temporal averaging with the formation of a temporal average value as a function of the interference signal.

24. A method for operation of a MRI scanner (1) as claimed in claim 20, wherein the method has the steps: (S80) Measurement of a transfer function between a first receiving antenna and the calibration element (86);(S81) Measurement of a transfer function between second receiving antenna (60) and the calibration element (86);(S82) Setting of the interference suppression parameter as a function of the measured transfer functions in such a way that a portion of an interference signal received by the second receiving antenna (60) is reduced in a signal received by the receiver (70) via the first receiving antenna.

25. The method as claimed in claim 21 or 22, wherein the step (S10) of receipt of the interference signal is undertaken at a time of a sequence at which no magnetic resonance signal for imaging is being received.

26. The method as claimed in one of claims 21 to 25, wherein the receiver (70) has a memory and the method has a step (S25) of storage, in which the receiver (70) stores the interference signal as well as the magnetic resonance signal in the memory, wherein the step (S30) of processing is undertaken with a delay relative to the receipt of the interference signal and/or magnetic resonance signal.

27. The method as claimed in one of claims 21 to 26, wherein the receiver (70) has an autocorrelation device and in the step (S40) of setting the parameter the autocorrelation device determines a portion of the interference signal in the magnetic resonance signal and the parameter is set as a function of the portion of the interference signal determined.

28. The method as claimed in one of claims 21 to 26, wherein the receiver (70) has an estimation device and in the step (S40) of setting the parameter the estimation device determines a portion of the interference signal in the magnetic resonance signal and the parameter is set as a function of the portion of the interference signal determined.

29. The method as claimed in one of claims 21 to 26, wherein the step (S40) of setting the parameter the has the sub-steps: (S42) Transforming the received magnetic resonance signals into an image space;(S43) Separating the interference signals from the magnetic resonance data;(S44) Transforming the interference signals into a raw data space;(S45) Determining the parameters from the transformed interference signals in the raw data space.

30. The method as claimed in claim 29, wherein the steps of the transforming (S42), of separating (S43), of back transforming (S44) and of determination of the parameter are undertaken (S45) on rows of data of the received magnetic resonance signals in the raw data space.

31. The method as claimed in one of claims 21 to 30, wherein the receiver (70) monitors the interference signal for changes in a step (S50) and if there is a change, adapts the parameter in a step (S51).

32. The method as claimed in one of claims 21 to 31, wherein the receiver (70) stores a first received magnetic resonance signal in a memory in a step (S21); stores a second received magnetic resonance signal in a step (S22) and compares the first received magnetic resonance signal and the second received magnetic resonance signal in a step (S23) and if there is a deviation which is attributable to external interference, performs an interference suppression measure.

33. The method as claimed in claim 32, wherein the interference suppression measure is a discarding (S60) of the first and/or second received magnetic resonance signal, a repetition of the acquisition of the first and/or second magnetic resonance signal or setting (S40) of the parameter.

34. A method for operation of an MRI scanner (1), wherein the MRI scanner (1) has a patient tunnel (16), a first receiving antenna for receiving a magnetic resonance signal from a patient (100) in the patient tunnel (16), a second receiving antenna (60) for receiving a signal having the Larmor frequency of the magnetic resonance signal and a receiver (70), wherein the second receiving antenna (60) is arranged outside the patient tunnel (16) or in the vicinity of an opening of the patient tunnel (16) and wherein the method has the steps: (S10) Receipt of an interference signal by the receiver (70) via the second receiving antenna (60);(S20) Receipt of a magnetic resonance signal by the receiver (70) via the first receiving antenna;(S60) Discarding of the magnetic resonance signal as a function of the interference signal received by the second receiving antenna (60).

35. A method for operation of an MRI scanner (1) having a Larmor frequency in an ISM band, wherein the method has the steps: (S110) Determination of an excitation pulse for excitation of nuclear spins in an examination object;(S120) Transmission of the excitation pulse;(S130) Receiving a magnetic resonance signal;(S140) Determination of a mapping of a distribution of nuclear spins in the examination object;wherein, in the step (S110) of determination of the excitation pulse, the pulse is determined as a function of predetermined frequency limits of the ISM band.

36. The method as claimed in claim 35, wherein the step (S110) of determination of an excitation pulse has the sub-steps: (S111) Establishing of an excitation pulse for exciting nuclear spins in a slice of the examination object as a function of a position of the slice relative to a magnet unit (10), a predetermined gradient strength, a thickness of the slice and the type of measurement;(S112) Checking whether the established excitation pulse lies within the predetermined frequency limits of the ISM band;Repetition of the step (S111) of establishing while varying a pulse parameter, which on establishing of the excitation pulse has an effect on a spectral frequency distribution of the excitation pulse if the excitation pulse does not lie within the predetermined frequency limits or

37. The method as claimed in claim 36, wherein the pulse parameter that affects the establishing of the excitation pulse is one of the parameters duration of the excitation pulse, thickness of the slice, relative position of the slice or strength of the gradients.

38. The method as claimed in claim 35, wherein the step (S120) of transmission has the sub-step (S121) of changing the position of the examination object relative to the magnet unit (10) before the step (S122) of emitting the pulse.

39. The MRI scanner as claimed in one of claims 1 to 20 with a control unit (20) for controlling the image acquisition and an interface connected to the control unit (20) for signaling, wherein the control unit (20) is designed to synchronize an image acquisition as a function of a signal received via the interface from a second MRI scanner (101).

40. The MRI scanner as claimed in one of claims 1 to 20 with a control unit (20) for controlling the image acquisition and an interface connected to the control unit (20) for signaling, wherein the control unit (20) is designed to transmit a signal with information about an impending image acquisition to a second MRI scanner (101).

41. The MRI scanner as claimed in claim 39 or 40, wherein the interface is designed for the exchange of data, wherein the control unit (20) is designed, by means of information exchanged via the interface, to synchronize an image acquisition with a second MRI scanner (101).

42. The MRI scanner as claimed in one of claim 40 or 41, wherein the signal has information about a time and/or frequency of a transmission process.

43. The MRI scanner as claimed in one of claim 40 to 42, wherein the signal has information about a time and/or frequency of a receive process.

44. A computer program product, which is able to be loaded directly into a processor of a programmable controller (23), with program code means for carrying out all steps of a method as claimed in one of claim 21 to 38 when the program product is executed at the controller (23).

45. A computer-readable storage medium with electronically-readable control information stored thereon, which is designed in such a way that, when the storage medium is used in a controller (23) of an MRI scanner (1) as claimed in claim 1 to 20, it carries out the method as claimed in one of claim 21 to 38.