Patent Description:
Magnetic resonance imaging (MRI) methods which utilize the interaction between magnetic fields and nuclear spins in order to form two-dimensional or three-dimensional images are widely used nowadays, notably in the field of medical diagnostics, because for the imaging of soft tissue they are superior to other imaging methods in many respects, do not require ionizing radiation and are usually not invasive.

According to the MRI method in general, the body of the patient to be examined is arranged in a strong, uniform magnetic field B<NUM> whose direction at the same time defines an axis (normally the z-axis) of the co-ordinate system to which the measurement is related. The magnetic field B<NUM> causes different energy levels for the individual nuclear spins in dependence on the magnetic field strength which can be excited (spin resonance) by application of an electromagnetic alternating field (RF field) of defined frequency (so-called Larmor frequency, or MR frequency). From a macroscopic point of view the distribution of the individual nuclear spins produces an overall magnetization which can be deflected out of the state of equilibrium by application of an electromagnetic pulse of appropriate frequency (RF pulse) while the corresponding magnetic field B<NUM> of this RF pulse extends perpendicular to the z-axis, so that the magnetization performs a precession motion about the z-axis. The precession motion describes a surface of a cone whose angle of aperture is referred to as flip angle. The magnitude of the flip angle is dependent on the strength and the duration of the applied electromagnetic pulse. In the example of a so-called <NUM>° pulse, the magnetization is deflected from the z axis to the transverse plane (flip angle <NUM>°).

After termination of the RF pulse, the magnetization relaxes back to the original state of equilibrium, in which the magnetization in the z direction is built up again with a first time constant T<NUM> (spin lattice or longitudinal relaxation time), and the magnetization in the direction perpendicular to the z-direction relaxes with a second and shorter time constant T<NUM> (spin-spin or transverse relaxation time). The transverse magnetization and its variation can be detected by means of receiving RF antennae (coil arrays) which are arranged and oriented within an examination volume of the magnetic resonance examination system in such a manner that the variation of the magnetization is measured in the direction perpendicular to the z-axis. The decay of the transverse magnetization is accompanied by dephasing taking place after RF excitation caused by local magnetic field inhomogeneities facilitating a transition from an ordered state with the same signal phase to a state in which all phase angles are uniformly distributed. The dephasing can be compensated by means of a refocusing RF pulse (for example a <NUM>° pulse). This produces an echo signal (spin echo) in the receiving coils.

In order to realize spatial resolution in the subject being imaged, such as a patient to be examined, constant magnetic field gradients extending along the three main axes are superposed on the uniform magnetic field B<NUM>, leading to a linear spatial dependency of the spin resonance frequency. The signal picked up in the receiving antennae (coil arrays) then contains components of different frequencies which can be associated with different locations in the body. The signal data obtained via the receiving coils correspond to the spatial frequency domain of the wave-vectors of the magnetic resonance imaging signals and are called k-space data. The k-space data usually include multiple lines acquired of different phase encoding. Each line is digitized by collecting a number of samples. A set of k-space data is converted to an MR image by means of Fourier transformation.

The transverse magnetization dephases also in presence of constant magnetic field gradients. This process can be reversed, similar to the formation of RF induced (spin) echoes, by appropriate gradient reversal forming a so-called gradient echo. However, in case of a gradient echo, effects of main field inhomogeneities, chemical shift and other off-resonances effects are not refocused, in contrast to the RF refocused (spin) echo.

A magnetic resonance examination system comprising a field probe system with field probes is known from the European patent application <CIT>.

The known magnetic resonance examination system comprises a main magnet to generate a stationary magnetic field. Magnetic resonance signals are acquired from an object to be examined. To that end, gradient magnetic fields and radiofrequency fields are generated according to an MR sequence. Further, additional data are acquired from field probes positioned in the vicinity of the object. The additional data represent variations of the magnetic field distribution due to gradient switching. These variations as a function of gradient switching are characterized by the so-called gradient impulse response function (GIRF) which constitutes a response relation between the gradient switching and the ensuing magnetic field variations. These additional data are used for adjusting the MR sequence to correct for imperfections in the field distribution. The additional data are also used with the acquired magnetic resonance signal for reconstruction of the magnetic resonance images.

An object of the invention is to provide a method using a field probe system for a magnetic resonance examination system that is more accurate or subject to less restrictions, compared to the known probe system, as to the configuration of the magnetic resonance examination system and the position of the patient to be examined in the examination zone. Notably, an object of the invention is to provide a method wherein the field probe system is less subject to available space to accommodate the field probes.

This object is achieved by the subject-matter of the independent claim, with further embodiments according to the dependent claims.

The Figure shows diagrammatically a magnetic resonance imaging system in which the method according to the invention can be used, which system is not part of the invention.

The method is usable in a magnetic resonance examination system having an examination zone and comprising.

An insight of the present invention is that in the known magnetic resonance examination system the field probe system can only function properly when there is sufficient space in the examination zone for both the (part of) the object to be examined, e.g. a patient as well as for the field probes. An insight of the present invention is further that a drawback of the known correction by the additional data e.g. via the GIRF, from the field probes, is that either the additional data may be outdated or that the additional data are acquired more often in separate calibrations which is time consuming. It is also known per se to incorporate field probes in a head coil, so that the additional data may be acquired while the patient is positioned in the head coil; that approach appears to be applicable only in imaging of the patient's head.

Both the current and previous configurations are arranged to acquire magnetic resonance imaging signals from a patient to be examined. That is, in both previous and current configurations high-spatial resolution MR image data (as represented by the magnetic resonance imaging signals) may be acquired. From these, MR-image data (of a patient to be examined) may be reconstructed. These MR-image data have clinical relevance in that a diagnostic quality magnetic resonance image can be reconstructed from the MR image data. In the earlier configuration, the MR-image data is acquired simultaneously and in the same or parallel data stream(s) with the acquisition of data by the field probes. The switching operation of the gradient fields and/or magnetic field disturbance originating externally in the current configuration may be available from the way the gradient system is operated in the current configuration and by measurement of the magnetic fields originating externally in the current configuration. In the framework of the invention this simultaneous measurement acquisition encompasses that the measurements by the field probe are done in a time span that at least partly overlaps with the time span in which magnetic resonance image signals are acquired This simultaneous acquisition may or may not be mutually synchronized in that the measurements intervals coincide in time. Further, the actual intake of data bits of the respective data streams may or may not be mutually offset or alternating on the level of individual (groups of) bits as long as the measurement intervals that span the measurement by the probes and acquisition of magnetic resonance imaging signals overlap in time to some extent. The measurement of the magnetic field distribution by the field probes and the determination of the response relation in the earlier configuration may be more often repeated than the known separate calibration of the GIRF. As the probes may measure the magnetic field distribution and the response relation may be determined from these measurements during the acquisition of clinically relevant MR image data, updating the response relation can be done in a time efficient manner.

The magnetic field distribution represents the spatial variations in the examination zone of the main stationary magnetic field and of the gradient magnetic fields that are temporarily applied for selecting spins to be manipulated by radiofrequency pulses and for spatially encoding of the magnetic resonance imaging signals. The gradient system executes switching operations in that electrical currents supplied by a gradient amplifier to the one or several gradient coils are switched so that the temporary gradient magnetic fields are changed. Notably, the gradient amplifier is controlled by applying a gradient waveform representing the desired temporary gradient magnetic fields in the form of gradient pulses. Changes in the applied gradient waveform cause the temporary gradient magnetic field to change. Due to gradient switching and external causes such as external magnetic field disturbances or mechanical vibrations, a resultant magnetic field arises. This resultant magnetic field is a temporal and spatial variation of the magnetic field distribution that ensues from the gradient switching or external causes. It appears that the resultant magnetic field occurs of the main magnetic field as well as of the gradient magnetic field due to switching of the gradient system or from external causes. This resultant magnetic field is in the form of a transient field-settling of the main magnetic field and gradient magnetic fields. Notably, this transient field settling includes concomitant electromagnetic fields and electromagnetic fields caused by eddy-currents that are generated by the switching of the gradient system.

The response relation represents the relationship between (a) gradient switching operations and/or magnetic field disturbances originating externally and (b) the resultant magnetic field distributions. The response relation thus may also be termed a field response as the response relation represents how the magnetic (gradient) fields respond to gradient switching operations and magnetic field disturbances originating externally. An insight of the invention may be that the response relation as determined in the earlier configuration is also valid in the current configuration in which the resultant magnetic field distribution can be determined from the response relation and the gradient switching operations and or the magnetic field disturbances originating externally in the current configuration. Because in this way the resultant magnetic field distribution is available in the current configuration, disturbances may be compensated or corrected for.

The resultant magnetic field distribution, may be stored in a data-compressed version in the memory. Thus, a database may be constructed of data-compressed versions of the resultant magnetic field distributions which may be stored in relation to switching operations of the gradient fields and/or magnetic field disturbances originating externally in the earlier configuration. This database forms an implementation of the response relation between gradient-switchings and magnetic field disturbances originating externally and their resultant magnetic field distributions. The response relation may also be represented as a correlation between the gradient switching or external cause and the ensuing resulting magnetic field. Other ways to form the response relation are the impulse response function, step response function or modulation transfer function of the resultant magnetic field that ensues from the gradient switching or said external causes. The response relation may also be formed as a parameterized function of time. The function represents the time evolution of the resultant magnetic field and its parameters are for example the gradient switching or the external course to which the resultant magnetic field is due.

Restrictions caused by the presence in the examination zone of the patient to be examined no longer apply to positioning the field probes in the examination zone, and vice versa. The spatial field distributions of the stationary and gradient magnetic fields, are measured by the field probes in an earlier configuration in which the field probes are positioned at suitable, preferably optimal locations for measuring the magnetic field distributions in the examination zone. Notably, in practice the field probe system includes a number of <NUM>, or preferably <NUM> to <NUM> field probes. The field probes are preferably positioned at about <NUM>-<NUM> from the magnet's iso-center. At closer distance to the iso-center, the probes are rather insensitive to spatially higher order variations of the magnetic field distribution. At larger distance from the iso-center, measurement of the spatial distribution of the magnetic field is dominated by higher order spatial variations. This makes an estimate of the lower order spatial variations unreliable. Moreover, at larger distances from the iso-center, interferences between the RF transmit antenna (e.g. the RF body coil) and the field probes become stronger. These interferences make the measurements by the field probe unreliable. The present invention enables to measure the magnetic field distribution in the earlier configuration in which the field probes are properly, preferably optimally, positioned to accurate measure the magnetic field distribution. In the current configuration the field probes are not needed. The resulting magnetic field required in the current configuration is accessed by a close approximation, measured from the earlier configuration and available from the memory. The earlier configuration in which the magnetic field distribution is measured is a configuration in which the same or a different object is imaged, and the field probes are positioned and employed to measure the magnetic field distribution.

The magnetic field distribution measured in the earlier configuration and represented by its response relation with gradient switching or magnetic fields originating externally, appears to be useful to be employed as an estimate or fair approximation of the magnetic field distribution in the current configuration. In particular, the earlier configuration represents the geometric arrangements of the field probes for measuring the magnetic field distribution in the examination zone as well as the geometric arrangement of one or more objects in the form of at least one body part of a subject the examination zone and the electromagnetic properties, such as the magnetic susceptibility distribution of these objects. These resultant magnetic fields due to gradient switching or external disturbances are independent from field distortions due to magnetic susceptibility of an object. Such an object in the earlier configuration may be a body part of a patient to be examined or healthy volunteer. The body part in the earlier configuration may be a body part of the same patient to be examined in the current configuration or may be a body part of an other individual. The body part in the earlier configuration and in the current configuration may be different body parts of the same patient to be examined. Hence, only in the earlier configuration, there needs to be sufficient space to accommodate the field probes and in the current configuration there may be no space available to place any field probes. It appears quite practical to use an MR imaging configuration with a patient's head in a (e.g. birdcage, or antenna-array) head-coil as the earlier configuration. Then, in the current configuration formed by the patient's abdomen and a local RF coil array, the magnetic field distribution from the earlier configuration appears quite useful to compensate gradient field or to apply correction in reconstruction in the current configuration.

The resultant magnetic field due to gradient switching occurs typically at a time scale of <NUM>-<NUM>, typically <NUM>. The field probe system is able to measure the magnetic field distribution due to gradient switching at a temporal resolution of <NUM>-<NUM>. In order to measure the magnetic field effects to gradient-switching, then a sampling resolution of <NUM>-<NUM>, preferable <NUM>-<NUM> is useful. In order to measure magnetic field-disturbances by moving objects and power-lines, a temporal resolution of <NUM> is sufficient. The field probe system is able to measure variations of magnetic field strength of <NUM>-10µT or gradient strengths of <NUM>-200µT/m. A field probe system having such capabilities is known per se from the paper '<NPL>.

The measured magnetic field distribution or, according to the invention, its response relation is employed to account for the current resultant magnetic field. That is, the resultant magnetic field associated with the earlier measured magnetic field distribution is an adequate approximation of the resultant magnetic field of the current configuration. It appears that the measured magnetic field distribution in the earlier (i.e. reference) configuration often is a close representation of the resultant magnetic field in the current configuration. Further, the earlier measured magnetic field distribution can, by way of its response relation, be employed to adapt transmit frequencies and demodulation frequencies to account for the resultant magnetic field in the current configuration. In reconstruction of the magnetic resonance image the earlier measured magnetic field distribution, or, according to the invention, the response relation, can be used to correct for errors due to the current resultant magnetic field. Alternatively, the earlier measured magnetic field distribution, i.e. its response relation, may be employed to control the gradient system to compensate for the resultant magnetic field formed by transient effects due to gradient switching. This is achieved by activating the gradient coils, i.e. applying electrical currents to the gradient coils, on the basis of the earlier measured field distribution. In other words, the electrical currents to the gradient coils are adjusted while accounting for the earlier measured magnetic field distribution, i.e. the response relation that represents it, so as to compensate for the resultant magnetic fields in the current configuration in the form of the transient effects of notably concomitant electromagnetic fields and eddy current responses due to the gradient switching in the examination zone.

The field probe system in the magnetic resonance examination system is able to provide data to account for the resultant main magnetic field and gradient magnetic field in situations even if there is no sufficient space in the examination zone for both the part of the body of the patient to be examined as well as the field probes. This is based on the insight that the responses of the field distributions due to gradient switching or other causes are well reproducible. Accordingly, the magnetic field distribution measured in the earlier configuration in dependence of switching the gradient system can be employed to compensate the application of the gradient magnetic field for the resultant magnetic field in the current configuration. Also, the magnetic field distributions measured in the earlier configuration in the form of the response relation representing the resultant magnetic field, in dependence of switching the gradient system can be employed to correct for the resultant magnetic fields in reconstruction.

A magnetic resonance examination system is disclosed comprising a field probe system to measure the magnetic field distribution of the main magnetic field and gradient magnetic field. The measurements are made in an earlier configuration and yield the resultant magnetic field due to gradient switching or external causes. From the measured resultant magnetic field the response relation is derived and stored in the memory. The response relation from the memory is available for compensating activation of the gradient fields or correction in reconstruction for the response relation in reconstruction. This compensation or correction can be carried-out in the current configuration. Thus in the current configuration no field probes are needed.

In a preferred embodiment of the method successively measuring the magnetic field distribution in various earlier configurations is performed as a function of (i) the switching operation of the gradient system and/or (ii) the magnetic field disturbance originating externally. Measurements of the magnetic field distribution from several successive different earlier configurations may be employed to build-up an accurate representation of the resultant magnetic field depending on various gradient switching and/or originating from externally from the magnetic resonance examination system, magnetic field disturbances. This may be implemented in that each time the field probe system is activated, the response relation is stored for that earlier configuration. The field probe system may be configured to automatically measure the magnetic field distribution. Alternatively, the field probe system may be prompted to activate measurement of the magnetic field distribution in the earlier configuration. This may be done e.g. when the content of the memory is outdated, in that the latest entry was made earlier than a pre-set time span before the current date. The measurements of the magnetic field distribution by the field probes are made in the earlier configurations simultaneously with acquisition of MR imaging data. These examples of the field probe system have self-learning capability in that from the measurements of the magnetic field distribution in the earlier configurations a collection of response relations is built-up which can be used to account for resultant magnetic fields in the current configuration. Further, because in the current configuration, the response relation is available from the memory, the field probes are not needed in the current configuration.

In another example the field probe system is configured to determine a correlation between the measured magnetic field distribution from the probes and (i) the switching operation of the gradient system, and/or (ii) a magnetic field disturbance originating externally and store the determined correlation as the representation of said measured magnetic field distribution. As only the correlation of the gradient switching operation or the external magnetic field disturbance needs to be stored as the representation of the resultant magnetic field, a modest memory capacity is required. This representation can be implemented as the impulse response function. The impulse response function can be computed from the measured magnetic field distribution and the applied gradient switching or a detected external disturbance. In one very simple example the correlation or the response relationship is formed as a simple scale factor. That is, e.g. the actual resultant magnetic field simply scales with the gradient switching demand or with the external magnetic field disturbance. For example, in the earlier configuration a gradient field of <NUM>. 2mT/m is measured in response to an applied gradient demand of <NUM>. 0mT/m, then the scale factor is <NUM> which can be employed in the current configuration the compensate in the applied gradient demand or to correct for in reconstruction. In a more intricate situation, the may be a linear relationship between the resultant magnetic fields and external causes , such as magnetic field disturbances originating externally that may be represented by a matrix.

Usually, the measurement of the magnetic field distribution in the earlier configuration is at an earlier instant in time than the acquisition of magnetic resonance imaging signals in the current configuration. However, the measurement of the magnetic field distribution may be done even after the acquisition of the magnetic resonance imaging signals and the response relation may be employed to correct for in reconstruction of the magnetic resonance image from the magnetic resonance imaging signals.

In a further example one or more additional magnetic field sensors are provided to measure the external field disturbances. Then on the basis of the measured external field disturbances, the field resultant field is retrieved from the memory that corresponds with the measured magnetic field disturbance in the current configuration.

These magnetic field sensors detect magnetic field disturbances to which the main magnetic field and the gradient magnetic fields may respond. For example, such magnetic field disturbances may be caused by external causes such as passing vehicles or electrical power lines. Internal causes, such as the magnetic resonance examination system's cryostatic cooling system, additional electrical equipment such as fans, may as well cause magnetic field disturbances. The magnetic field distribution in the examination zone is measured by the field probe system in dependence of the detected magnetic field disturbances. It appears that the resultant magnetic field strongly and reproducibly correlates with the detected magnetic field disturbances. Thus, the earlier measured resultant magnetic field are generated in dependence of the detected magnetic field disturbance and the response relation that represent it is derived, notably in the earlier configuration. When, subsequently, in a current configuration a magnetic field distribution is detected, the application of the gradient magnetic field and/or the reconstruction of the magnetic resonance image can be corrected for the response of the magnetic field distribution, e.g. using the response relation associated with it, that was measured earlier in the corresponding earlier configuration for the detected magnetic field disturbance.

In another example, motion sensors are provided, notably to detect vibrations of the structural components, notably the gradient coils and main magnetic field coils. It appears that such vibrations generate a resultant magnetic field distribution. The field probe system is arranged to measure the magnetic field distribution and its associated response relation is derived in the earlier configuration in dependence of the detected vibrations. Subsequently, when in the current configuration a vibration is detected, then the application of the gradient magnetic field and/or the reconstruction of the magnetic resonance image can be corrected for the resultant magnetic field distribution, e.g. using the response relation associated with it, for the detected vibration that was measured earlier in the earlier configuration.

In another example, temperature sensors are provided, notably to detect the structural components' temperature, notably of the gradient coils and main magnetic field coils. It appears that such resultant magnetic field distributions due to gradient switching are temperature dependent. The field probe system is arranged to measure the magnetic field distribution in the earlier configuration in dependence of the measured temperature. The field probe system derives the response relation in dependence of the measured temperature. Subsequently, when in the current configuration the temperature of e.g. the gradient coil, is detected, then the application of the gradient magnetic field and/or the reconstruction of the magnetic resonance image can be corrected for the resultant magnetic field for the measured temperature. In other words, the earlier measured magnetic field distribution is measured in dependence of the measured temperature in the earlier configuration. In the current configuration, the response relation is retrieved from the measured temperature in the current configuration. Thus, temperature dependencies of the response relation are adequately taken into account. In an example, in the earlier configuration a reference part of the patient's body is placed in the examination zone or, in the earlier configuration a currently examined (different) part of the patient's body is placed in the examination zone. Even in the earlier and current configurations respectively, body parts of different patients being imaged may be used. When imaging the current body part, there is no need for the field probes since the current resultant magnetic field is calculated from the stored response relation from the earlier measured magnetic field distribution. Thus, for imaging of the current body part, the field probes may be removed. In a typical example, the earlier measured magnetic field distribution may be measured with the patient's head placed in the examination zone and the field probes arranged around the patient's head. For example, the field probes may be integrated in an RF transmit/receive head-coil (array, TEM or bird-cage type) that is employed to acquire the magnetic resonance imaging signals from the patient's head. Then in the current configuration the patient's abdomen or thorax is placed in the examination zone and the field probes removed. As the patient's abdomen or thorax may take up most of the space of the examination zone, or even only fits tightly in the main magnet's bore of the magnetic resonance examination system, there may be no space left to arrange the field probes. An insight of the present invention is that the magnetic field distribution measured from the patient's head (i.e. in the earlier configuration) will still be valid to correct for resultant magnetic fields of the stationary main magnetic field and of the gradient magnetic field when acquiring magnetic resonance imaging signals from the patient's abdomen or thorax (i.e. in the current configuration). Notably, the main magnetic field and/or the gradient magnetic field, or the response relations representing the resulting magnetic fields, (i) as measured while the patient's head is imaged and (ii) as applied when the patient's abdomen is imaged are at most marginally different.

These and other aspects are further elucidated with reference to the accompanying drawing in the Figure, which shows diagrammatically a magnetic resonance imaging system in which the method according to the invention can be used. The magnetic resonance imaging system includes a main magnet with a set of main coils <NUM> whereby the steady, uniform magnetic field is generated. The main coils are constructed, for example in such a manner that they from a bore to enclose a tunnel-shaped examination space. The patient to be examined is placed on a patient carrier which is slid into this tunnel-shaped examination space. The magnetic resonance imaging system also includes a number of gradient coils <NUM>, <NUM> whereby magnetic fields exhibiting spatial variations, notably in the form of temporary gradients in individual directions, are generated so as to be superposed on the uniform magnetic field. The gradient coils <NUM>, <NUM> are connected to a gradient control <NUM> which includes one or more gradient amplifiers and a controllable power supply unit. The gradient coils <NUM>, <NUM> are energized by application of an electric current by means of the power supply unit <NUM>; to this end the power supply unit is fitted with electronic gradient amplification circuit that applies the electric current to the gradient coils so as to generate gradient pulses (also termed 'gradient waveforms') of appropriate temporal shape. The strength, direction and duration of the gradients are controlled by control of the power supply unit. The magnetic resonance imaging system also includes transmission and receiving antennae (coils or coil arrays) <NUM>, <NUM> for generating the RF excitation pulses and for picking up the magnetic resonance imaging signals, respectively. The transmission coil <NUM> is preferably constructed as a body coil <NUM> whereby (a part of) the object to be examined can be enclosed. The body coil is usually arranged in the magnetic resonance imaging system in such a manner that the patient to be examined is enclosed by the body coil <NUM> when he or she is arranged in the magnetic resonance imaging system. The body coil <NUM> acts as a transmission antenna for the transmission of the RF excitation pulses and RF refocusing pulses. Preferably, the body coil <NUM> involves a spatially uniform intensity distribution of the transmitted RF pulses (RFS). The same coil or antenna is generally used alternately as the transmission coil and the receiving coil. Typically, a receiving coil includes a multiplicity of elements, each typically forming a single loop. Various geometries of the shape of the loop and the arrangement of various elements are possible The transmission and receiving coil <NUM> is connected to an electronic transmission and receiving circuit <NUM>.

It is to be noted that is that there is one (or a few) RF antenna elements that can act as transmit and receive; additionally, typically, the user may choose to employ an application-specific receive antenna that typically is formed as an array of receive-elements. For example, surface coil arrays <NUM> can be used as receiving and/or transmission coils. Such surface coil arrays have a high sensitivity in a comparatively small volume. The receiving coil is connected to a preamplifier <NUM>. The preamplifier <NUM> amplifies the RF resonance signal (MS) received by the receiving coil <NUM> and the amplified RF resonance signal is applied to a demodulator <NUM>. The receiving antennae , such as the surface coil arrays, are connected to a demodulator <NUM> and the received pre-amplified magnetic resonance imaging signals (MS) are demodulated by means of the demodulator <NUM>. The pre-amplifier <NUM> and demodulator <NUM> may be digitally implemented and integrated in the surface coil array The demodulated magnetic resonance imaging signals (DMS) are applied to a reconstruction unit. The demodulator <NUM> demodulates the amplified RF resonance signal. The demodulated resonance signal contains the actual information concerning the local spin densities in the part of the object to be imaged. Furthermore, the transmission and receiving circuit <NUM> is connected to a modulator <NUM>. The modulator <NUM> and the transmission and receiving circuit <NUM> activate the transmission coil <NUM> so as to transmit the RF excitation and refocusing pulses. In particular the surface receive coil arrays <NUM> are coupled to the transmission and receive circuit by way of a wireless link. Magnetic resonance imaging signal data received by the surface coil arrays <NUM> are transmitted to the transmission and receiving circuit <NUM> and control signals (e.g. to tune and detune the surface coils) are sent to the surface coils over the wireless link.

The reconstruction unit derives one or more image signals from the demodulated magnetic resonance imaging signals (DMS), which image signals represent the image information of the imaged part of the object to be examined. The reconstruction unit <NUM> in practice is constructed preferably as a digital image processing unit <NUM> which is programmed so as to derive from the demodulated magnetic resonance imaging signals the image signals which represent the image information of the part of the object to be imaged. The signal on the output of the reconstruction is applied to a monitor <NUM>, so that the reconstructed magnetic resonance image can be displayed on the monitor. It is alternatively possible to store the signal from the reconstruction unit <NUM> in a buffer unit <NUM> while awaiting further processing or display.

The magnetic resonance imaging system is also provided with a control unit <NUM>, for example in the form of a computer which includes a (micro)processor. The control unit <NUM> controls the execution of the RF excitations and the application of the temporary gradient fields. To this end, the computer program is loaded, for example, into the control unit <NUM> and the reconstruction unit <NUM>.

The magnetic resonance examination system is provided with several (e.g. <NUM>, <NUM> or <NUM>) field probes <NUM>, which are preferably mounted in the head coil <NUM>. The field probes measure the magnetic field distribution due to gradient switching and/or due to external magnetic field disturbances. The field probes <NUM> are connected to the field probe control module <NUM>. The field probe control module controls the field probes to carry-out the measurements of the magnetic field distribution when the head-coil <NUM> is in position in the earlier configuration. The measurement results are provided to the field probe control module <NUM> to determine the magnetic field distribution due to the gradient switching or external magnetic field disturbance. In an example outside the scope of the invention, in this earlier configuration no object, other than the head coil <NUM> with the field probes is positioned in the examination zone of the magnetic resonance examination system. In an implementation according to the invention, the magnetic field distribution is measured while a body part of a subject, e.g. the head of a patient to be examined is imaged. From the measured magnetic field distribution, the response relation, e.g. in the form of the impulse response function, is computed by an arithmetic unit <NUM> and then saved in the memory <NUM>. The field probes <NUM>, the field probe control <NUM> with the arithmetic unit <NUM> and the memory <NUM> make up the field probe system. The field probe control <NUM> with the arithmetic unit <NUM> and the memory <NUM> may be integrated, notably as software modules, in the magnetic resonance examination system's processing unit <NUM>. Also the gradient control <NUM> is integrated in the processing unit <NUM>. The gradient control <NUM> generates the gradient waveforms that are fed to the power amplifier <NUM> to activate the gradient coils <NUM> in accordance with the gradient waveforms.

The saved representation of the response relation, notably the impulse response function, can be employed to control the gradient control <NUM> to compensate for the response relation in activation of the gradient coils <NUM>. The saved representation of the response relation may also be employed to correct for the response field in the reconstruction of the magnetic resonance image from the acquired magnetic resonance imaging signals. Because the representation of the response relation is available from the memory <NUM>, in the current configuration there is no need for the measurements by the field probes of the response field. Thus in the current configuration the head coil <NUM> with the field probes may be removed and e.g. replaced by a local anterior coil array <NUM> to acquire magnetic resonance imaging signals from the patient's abdominal region. In the current configuration, magnetic resonance imaging signals may also be acquired by the RF body coil <NUM>.

The magnetic resonance examination system is further provided with one or several magnetic field sensors <NUM> to measure magnetic field disturbances. Such magnetic field disturbances may have an external cause, such as a passing vehicle, or due to activity of nearby electrical power lines. Other magnetic field disturbances may be caused by the magnetic resonance examination system cryostat system (not shown). The magnetic field disturbances are measured by the field probes <NUM> in the head coil <NUM> (that is in the earlier configuration). On the basis of detected magnetic field disturbance in the current configuration (where the field probes are not available) the response relation, e.g. impulse response function, of the resultant magnetic field due to the magnetic disturbance, is available from the memory. The gradient control <NUM> may compensate for the response field on the basis of the representation available from the memory <NUM>. Further, the representation may be employed to account for the resultant magnetic field in the reconstruction by the reconstruction unit <NUM>.

The magnetic resonance examination system is also provided with one or several motion sensors <NUM>, notably to measure motion, e.g. vibrations of the gradient coils <NUM>. The detected vibrations are fed to the field probe control unit and the ensuing magnetic field distribution is measured in the earlier configuration with the field probes <NUM> in the head coil <NUM>. In the current configuration, i.e. without the field probes available, the vibrations are also measured and on the basis of these measurements and the response relation is available from the memory <NUM>. The available response relation is then used to compensate the activation of the gradient coil <NUM> for the resultant magnetic fields due to the detected vibrations. Correction for the resultant magnetic field due to the detected vibrations may also be carried-out in the reconstruction in the reconstruction unit <NUM>.

Claim 1:
A method of correcting resultant magnetic fields in a magnetic resonance examination system based on a field probe system, wherein the field probe system comprises several field probes and is configured to measure a magnetic field distribution of a main magnetic field and/or a gradient magnetic field in an examination zone of the magnetic resonance examination system due to a switching operation of a gradient system of the magnetic resonance examination system and/or due to a magnetic field disturbance originating externally, the method comprising the steps of
- by a control module configured to control the field probe system, activating the field probe system to measure the magnetic field distribution in an earlier configuration simultaneously with an acquisition of magnetic resonance imaging signals from the examination zone in the earlier configuration;
- by the control module, determining a response relation representing the measured magnetic field distribution in the earlier configuration due to said switching operation of the gradient system and/or due to said magnetic field disturbance originating externally, and storing the response relation in a memory;
- acquiring magnetic resonance imaging signals from the examination zone in a current configuration;
- performing a compensating activation of gradient coils of the gradient system in the current configuration based on
the response relation representing the measured magnetic field distribution in the earlier configuration; and/or
- applying corrections in reconstruction of a magnetic resonance image from the magnetic resonance imaging signals acquired in the current configuration based on the response relation representing the measured magnetic field distribution in the earlier configuration; wherein
in the earlier configuration, the field probes and a body part of a subject are positioned in the examination zone, and
in the current configuration, a different body part of the same subject or a body part of another subject is positioned in the examination zone.