METHOD AND MAGNETIC RESONANCE APPARATUS FOR ACQUIRING MAGNETIC RESONANCE DATASET WITH REDUCED SUSCEPTIBILITY ARTIFACTS IN THE RECONSTRUCTION IMAGE

Abstract

In a method and apparatus for recording a magnetic resonance dataset of a volume of interest of an object, at least one gradient moment is calculated as a function of at least one jump in susceptibility that is present in the volume of interest, between two sections of the volume of interest. An excitation pulse is radiated and at least one compensation moment is activated in a part volume of the volume of interest, for the at least partial compensation of a gradient moment caused by the jump in susceptibility. The signal generated by the excitation pulse is read out.

Claims

1. A method for acquiring a magnetic resonance (MR) dataset of volume of interest of a subject, said method comprising: providing a processor with an electronic input that designates at least one jump in susceptibility that exists in said volume of interest between two sections of said volume of interest; in said processor, calculating at least one gradient moment dependent on said at least one jump in susceptibility; from said processor, operating an MR data acquisition scanner to execute an MR data acquisition sequence that includes radiation of an excitation pulse that excites nuclear spins in said volume of interest; during execution of said sequence, operating said MR data acquisition scanner to activate at least one compensation moment that is effective in a portion of said volume of interest to at least partially compensate said gradient moment caused by said jump in susceptibility; from said processor, operating said MR data acquisition scanner in said sequence to read out signals produced by said nuclear spins resulting from said excitation pulse; and from said processor, making the read out signal available from the processor in electronic form, as a data file.

2. A method as claimed in claim 1 comprising operating said MR data acquisition scanner to activate a gradient that generates said compensation moment.

3. A method as claimed in claim 1 comprising operating said MR data acquisition scanner to radiate a radio-frequency pulse that generates said compensation moment.

4. A method as claimed in claim 1 comprising operating said MR data acquisition scanner to apply said compensation moment only in one sub-region of said region of interest.

5. A method as claimed in claim 4 wherein said one sub-region is selected as a sub-region of said region of interest in which said at least one jump in susceptibility occurs.

6. A method as claimed in claim 1 comprising using a gradient-echo sequence as said magnetic resonance data acquisition sequence.

7. A method as claimed in claim 6 comprising using a gradient echo imaging sequence as said gradient echo sequence.

8. A method as claimed in claim 1 wherein said subject is a patient, and comprising operating said MR data acquisition scanner to apply said gradient moment in a head region of the patient.

9. A method as claimed in claim 8 wherein said head region comprises at least one of the nose of the patient, the frontal sinus of the patient, or an auditory canal of the patient.

10. A method as claimed in claim 1 wherein the subject is a patient, and comprising operating said MR data acquisition scanner to apply said compensation moment in a region of the upper body of the patient.

11. A method as claimed in claim 10 comprising applying said compensation moment in a region containing the lungs of the patient.

12. A method as claimed in claim 1 comprising providing said computer with a further electronic input that describes a condition in said MR data acquisition scanner that has an effect on said at least one jump in susceptibility, and, in said processor, calculating said gradient moment using said electronic input and said at least one further electronic input.

13. A method as claimed in claim 12 wherein said MR data acquisition scanner comprises a basic field magnet that, during said sequence, generates a basic magnetic field (B.sub.0 field), and wherein said further electronic input is an electronic designation of a B.sub.0 map that depicts said B.sub.0 field in at least a portion of said volume of interest.

14. A method as claimed in claim 12 wherein said excitation pulse produces a B field in said MR data acquisition scanner, and wherein said further electronic input is an electronic designation of a B.sub.1 map that depicts said B.sub.1 field in at least a portion of said volume of interest.

15. A method as claimed in claim 12 wherein said further electronic input is a navigator echo.

16. A non-transitory, computer-readable data storage medium encoded with programming instructions, said storage medium being loaded into a computer system of a magnetic resonance (MR) apparatus, that comprises an MR data acquisition scanner, said programming instructions causing said computer system to: receive an electronic input that designates at least one jump in susceptibility that exists in a volume of interest between two sections of said volume of interest; calculate at least one gradient moment dependent on said at least one jump in susceptibility; operate said MR data acquisition scanner to execute an MR data acquisition sequence that includes radiation of an excitation pulse that excites nuclear spins in said volume of interest; during execution of said sequence, operate said MR data acquisition scanner to activate at least one compensation moment that is effective in a portion of said volume of interest to at least partially compensate said gradient moment caused by said jump in susceptibility; operate said MR data acquisition scanner in said sequence to read out signals produced by said nuclear spins resulting from said excitation pulse; and make the read out signal available from the computer system in electronic form, as a data file.

17. A magnetic resonance (MR) apparatus comprising: an MR data acquisition scanner adapted to receive a subject therein, said subject comprising a volume of interest from which MR signals are to be acquired; a processor provided with an electronic input that designates at least one jump in susceptibility that exists in said volume of interest between two sections of said volume of interest; said processor being configured to calculate at least one gradient moment dependent on said at least one jump in susceptibility; said processor being configured to operate said MR data acquisition scanner to execute an MR data acquisition sequence that includes radiation of an excitation pulse that excites nuclear spins in said volume of interest; said processor being configured to, during execution of said sequence, operate said MR data acquisition scanner to activate at least one compensation moment that is effective in a portion of said volume of interest to at least partially compensate said gradient moment caused by said jump in susceptibility; said processor being configured to operate said MR data acquisition scanner in said sequence to read out signals produced by said nuclear spins resulting from said excitation pulse; and said processor being configured to make the read out signal available from the processor in electronic form, as a data file.

Description

BRIEF DESCRIPTION OF THE DRAWINGS

[0055] FIG. 1 is a block diagram of a magnetic resonance apparatus constructed and operating in accordance with the present invention.

[0056] FIG. 2 shows a first embodiment of a sequence diagram in accordance with the present invention.

[0057] FIG. 3 shows a second embodiment of a sequence diagram in accordance with the present invention.

[0058] FIG. 4 shows a third embodiment of a sequence diagram in accordance with the present invention.

[0059] FIG. 5 is a flowchart of a first embodiment of the present invention.

[0060] FIG. 6 is a flowchart of a second embodiment of the present invention.

DESCRIPTION OF THE PREFERRED EMBODIMENTS

[0061] FIG. 1 schematically illustrates a magnetic resonance scanner 1. This scanner 1 has a radio-frequency coil 2 embodied as a body coil, a coil array 3 with coils 4, 5, 6 and 7, and a control computer 8. The coil 2 is used for the excitation of nuclear spins so as to deflect their magnetization, and accordingly functions as a transmitter coil. The coil array 3 is used to read out the scan signal and represents the receiver coil unit. The coils 4, 5, 6 and 7 of the coil array 3 read out the scan signal simultaneously. Instead of the coil array 3, it is also possible to use an individual coil as a detection coil.

[0062] Also known are coils that function simultaneously as excitation and detection coils. These can also be used to carry out the method described below.

[0063] The magnetic resonance scanner 1 further comprises a data storage medium 9 as part of the control computer 8 or independently thereof on which computer code for carrying out magnetic-resonance scans are stored.

[0064] The only precondition for this are the gradient coils 10, 11 and 12, which are depicted schematically, but these are necessarily present in all magnetic-resonance devices. The gradient coils 10, 11 and 12 generate gradient fields in three directions. These are usually designated x, y and z. These are superimposed in order to generate the gradients used in a recording sequence, which lie in the read-out, phase and slice direction. This means that, depending upon their position, the gradients used in a sequence are made up of the gradients in the x, y and z directions or in any combination.

[0065] The gradient coils 10, 11 and 12 and a corresponding scan sequence can be used to compile spatially resolved B.sub.0 or B.sub.1 maps that can be used to calculate the magnitude of susceptibility jumps. A compensation or balancing moment can then be determined from this.

[0066] In this context, it is assumed that, without the susceptibility jumps, the B.sub.0 or B.sub.1 field would be constant. Alternatively, it is also possible for B.sub.1 correction maps that are dependent on the pulse shape to be taken into account.

[0067] In the B.sub.0 or B.sub.1 map, it is possible for all noise-induced fluctuations to be filtered out using a threshold value in order then to determine the magnitude and position of susceptibility jumps.

[0068] If the position of the susceptibility jumps is to be tracked, the B.sub.0 or B.sub.1 map can also be used to define the parameters for navigator echoes.

[0069] FIG. 2 shows a first embodiment of the sequence diagram of an EPI scan sequence 27. EPI enables image datasets to be recorded in one train and so EPI is frequently used as an imaging module according to a T2 or diffusion-preparation module. Due to the numerous gradient echoes, EPI is particularly susceptible to susceptibility artifacts.

[0070] In this context, as in the following sequence diagrams, the axes 13, 14, 15 and 16 stand for a temporal sequence, the axis 13 for the radio-frequency pulses, also known as RF pulses and the scan signal, the axis 14 for the read direction, the axis 15 for the phase direction and the axis 16 for the slice direction. Generally, and not only with reference to the axes, the same reference numbers are used for the same subject matter without this being explicitly stated with respect to FIG. 3 or FIG. 4.

[0071] Also depicted in addition to the radio-frequency pulse 17 as an excitation pulse for the EPI-scan sequence 27 are a slice-selection gradient 18, a slice-rephasing gradient 19, a phase-encoding gradient 20 and a read-dephasing gradient 21.

[0072] The read-gradient train 22 and the phase-encoding gradients 23 for encoding the k-space lines embodied as so-called blips are known and do not therefore require more detailed explanation. The omission indicates the gradient circuits that are not shown.

[0073] In FIG. 2, the embodiment of the compensation moment is shown as a moment generated via a gradient. This gradient is the compensation gradient 24. In this context, the magnitude and duration of the compensation gradient is, as described, determined automatically. In this context, the compensation gradient at least partially generates a compensation moment for the moment that forms due to the gradient □B induced by susceptibility jumps.

[0074] In this context, the compensation gradient 24 is implemented as a coherent gradient circuit.

[0075] FIG. 2 shows purely by way of example a compensation moment in the direction of the Z-axis. However, as described above, the compensation moment can be applied in any directions desired.

[0076] FIG. 3 shows an alternative implementation of the compensation moment, which is again generated via gradients. In this context, the compensation moment is obtained as the sum of a plurality of compensation gradients 25, which overall, i.e. in the moment, correspond to the compensation gradient 24. Once again, these can be used in any directions desired; here, they are shown purely by way of example in the read-out direction.

[0077] The read-out gradients 25 are formed in that the gradients of the read-gradient train 22, and to be more precise, every second one, remain switched after the reading out until the desired moment is achieved. This additional time is to be taken into account when calculating the recording parameters.

[0078] The compensation gradients 25 can preferably generate the same or even different moments.

[0079] In particular, in one sequence, the gradients 24 and 25 for generating the compensation moments can be generated differently in different directions, for example coherently in the slice direction as in FIG. 2 and with a plurality of gradients in the read-out and/or phase directions as in FIG. 3.

[0080] FIG. 4 shows an EPI-scan sequence 27, with which the compensation moment is generated via a radio-frequency pulse 26. In this context, a time shift in the channels of the transmitter coil 2 is used to maintain the desired compensation moment. Therefore, the scan sequence 27 in FIG. 4 should not be considered to differ from a known EPI scan sequence.

[0081] FIG. 5 shows a flow diagram for recording a magnetic resonance scanner.

[0082] In step S1, the object to be examined is positioned in the magnetic resonance device.

[0083] Following this, adjustment scans are performed as step S2 with which a B.sub.0 map is also compiled.

[0084] In step S3, it is determined in an automated way from the B.sub.0 map whether a, and if so which, compensation moment is required in order to compensate any gradients □B present and generated by susceptibility jumps. In this context, it is possible to determine the position and magnitude of the compensation moment required.

[0085] It is also possible for the position of the slices or slabs to be extracted automatically.

[0086] The magnitude and direction of the compensation moment can be used in step S4 to determine as a function of the scan sequence whether one or more compensation gradients 24 or 25 or a radio-frequency pulse 26 is used. For example, compensation gradients 24 can be used in the read-out and/or phase and/or slice directions. As described above, in different directions, it is also possible to use a compensation gradient 25 once in one direction and a compensation gradient 24 in another direction. If only one alternative is possible on a magnetic resonance device 1, step S4 can be omitted.

[0087] If a compensation gradient is used, the position and magnitude of the compensation gradient 24 or 25 is determined as step S5. In this context, it is possible to use preset scan sequences and for example, to use a threshold value of the compensation moment to select the scan sequence according to FIG. 2 or FIG. 3.

[0088] During the performance of the scan sequence as step S6, at least one excitation pulse is applied, a compensation moment is applied at least once in the form of a compensation gradient 24 or several times in the form of the compensation gradients 25 in a part volume of the volume of interest for the at least partial compensation of the moment □B caused by the jump in susceptibility and the signal generated by the excitation pulse is read out.

[0089] During sequences such as EPI, if all k-space lines are recorded in one train, a compensation gradient 24 can be switched once, in the case of waiting times between the recording of k-space lines as with a spin echo, the compensation gradients 25 can be applied on each recording of a k-space line. In this context, the magnitude or duration can be greater or longer than with an EPI since, due to the waiting time, there is no summation or a different summation of the moments.

[0090] In the case of segmented sequences, such as TSE, it is either possible to apply an individual compensation gradient 25 to each k-space line or to each segment. Then, the number of compensation gradients 25 corresponds to the number of excitation pulses; the refocusing pulses do not then count.

[0091] Therefore, typically step b) is performed once to N.sub.pe times, step c) once to N.sub.pe times and step d) N.sub.pe times in order to record an image dataset. Claim 1 should be understood as meaning that the steps b) and c) are performed at least once. In this context, N.sub.pe corresponds to the number of k-space lines to be recorded.

[0092] In this context, the description is aimed at two-dimensional image datasets with Cartesian k-space sampling. The modifications required to achieve three-dimensional image datasets and/or radial sampling are known.

[0093] FIG. 6 shows a flow diagram for recording a magnetic resonance dataset with which, in addition to the method depicted in FIG. 5, the susceptibility jumps are tracked.

[0094] In this context, the steps with the same numbering correspond to the steps described for FIG. 5.

[0095] Additionally to the steps S1 to S5, in step S7 after step S3 and before step S8, at least one reference navigator echo is recorded. Preferably, there are then three navigator echoes. This corresponds to the number of spatial axes. Three navigator echoes can be used to track the movement of the object to be examined thus enabling conclusions to be drawn regarding the position of the susceptibility jumps.

[0096] Step S9 represents the repeat recording of the navigator echoes with the determination of a change to the position of the susceptibility jumps and is performed before step S8.

[0097] In step S8, one or more k-space lines are recorded, but not an entire dataset. Therefore, before the recording of each k-space line or a segment, a check is performed in step S10 to determine whether the compensation moment, and hence the compensation gradients 25, are to be adapted.

[0098] This check with respect to the compensation moment can obviously also be performed when a radio-frequency pulse is used to generate the compensation moment.

[0099] Following the recording of the magnetic resonance dataset, the data is to be subjected to a plurality of processing steps such as a Fourier transformation in order to obtain an image dataset.

[0100] The image generated from the magnetic resonance dataset can also be used to form combination images.

[0101] The position of the susceptibility jumps is also possible with other methods apart from navigator echoes. Additionally or alternatively, it is also possible for field sensors or navigators to be used to identify and take account of changes to a field, for example a thermally-induced field change.

[0102] Furthermore, it is additionally or alternatively possible to take account of a movement phase. This can be a respiratory phase or a heartbeat of a test subject. In particular, the compensation moments can be determined and applied as a function of the movement phase.

[0103] Furthermore, it is additionally or alternatively possible, as described above, to use recording mechanisms or sensors in order to identify or take account of patient movements.

[0104] Although modifications and changes may be suggested by those skilled in the art, it is the intention of the Applicant to embody within the patent warranted hereon all changes and modifications as reasonably and properly come within the scope of the Applicant's contribution to the art.