Reconfigurable local coil, device for reconfiguration and method for operation

Abstract

The invention relates to a device with a field control material for placement between a local coil and a patient, as well as a local coil, a magnetic resonance imaging (MRI) scanner with the local coil, and a method for operating the MRI scanner. The device has a control input, and the field control material is designed to change the spatial propagation of an alternating electric and / or magnetic field depending on a control signal at the control input. The MRI scanner acquires images with different settings of the field control material.

Description

[0001] Regardless of the grammatical gender of a particular term, persons with male, female or other gender identities are included.

[0002] The invention relates to a device comprising a field control material for placement between a local coil and a patient, as well as to a local coil and a magnetic resonance imaging scanner comprising the device. The device has a control input for modifying electric and / or magnetic fields through the field control material. The invention further relates to a method for operating the magnetic resonance imaging scanner.

[0003] Magnetic resonance imaging scanners are imaging devices that, to create an image of a subject, align the nuclear spins of the subject with a strong external magnetic field and then excite them to precess around this alignment using an alternating magnetic field. The precession, or return, of the spins from this excited state to a lower-energy state, in turn generates a response alternating magnetic field, which is received via antennas.

[0004] Using magnetic gradient fields, a spatial coding is imprinted on the signals, which subsequently allows the received signal to be assigned to a volume element. The received signal is then evaluated, and a three-dimensional image of the object under examination is provided. Local receiving antennas, so-called local coils, are preferably used to receive the signal. These antennas are positioned directly on the object under examination to achieve a better signal-to-noise ratio.

[0005] Magnetic resonance imaging is relatively slow compared to other modalities because of the weak signals of the nuclear spins caused by the high temperature and thus the small deviation of the nuclear spins from thermal equilibrium, the signal-to-noise ratio is low and long integration times are required.

[0006] This can be remedied by scanning multiple slices in parallel. To do this, the signals from different volumes must be received by separate antenna coils to enable parallel analysis without crosstalk. The smaller the antenna coils, the more volumes can be acquired in parallel. However, with the size of the coils, the signal and thus the signal-to-noise ratio decrease, requiring longer integration times.

[0007] From the document US 10324152 B2 an arrangement of passive resonators is known which improves the signal-to-noise ratio of radio signals emitted by an examination object and received by the magnetic resonance imaging device.

[0008] It is an object of the present invention to provide an apparatus and a method for accelerating image acquisition with a magnetic resonance imaging scanner.

[0009] This object is achieved by a device according to claim 1, a magnetic resonance tomograph according to claim 7 and by a method according to claim 10.

[0010] The device according to the invention comprises a field control material. A field control material, within the meaning of the invention, refers to a synthetically produced structure that exhibits propagation properties for alternating electric and / or magnetic fields, at least for a predetermined frequency of the alternating fields, that differ from the properties of natural, homogeneous materials. Such materials are also referred to as metamaterials. Metamaterials are known, for example, from the publication US 10324152 B2.

[0011] However, it is also conceivable that the field-control material could exhibit controllable properties similar to liquid crystals or other optically active media in the radio frequency range, and thus in the magnetic resonance range. For example, materials whose dielectric constant or permeability depends on external parameters such as an external static electric field, pressure, or other variable macroscopic quantities would be conceivable.

[0012] Such materials are known from the documents WO 2002059059 A2 and US 7852176 B2.

[0013] The device is intended for placement between a local coil matrix and a patient. Preferably, the device has a planar configuration, i.e., the dimensions of the device, when arranged as intended, are larger in directions parallel to the surface of the patient and / or the local coil than in a direction perpendicular thereto. Preferably, the device is flexible or divided into segments that are flexibly connected to one another, allowing the device to conform to a surface of the patient.

[0014] The device further comprises a control input. The field control material is designed to change the spatial propagation of an alternating electric and / or magnetic field in response to a control signal via the control input. In other words, the field control material can be brought into at least two different states by the control signal, in which an alternating electric and / or magnetic field propagates differently through the field control material and thus leads to different field strengths on the side of the field control material facing away from the field source for the at least two states. This applies both to a transmission case, in which the local coil, acting as a transmitting antenna, emits an excitation pulse into the patient, and to the reception case, in which alternating magnetic fields emitted by the nuclear spins are picked up by the antenna coil(s).

[0015] The different states of the field control material can, for example, be caused by electromagnetic resonance elements in the material, whose resonance behavior is altered by the control signal, such as a voltage. Different polarization states or mechanical configurations induced by the control signal are also conceivable. Different designs are explained below.

[0016] Advantageously, the device enables the controlled modification of the field profiles and thus the spatial transmission and reception properties of a local coil, thus enabling the controlled acquisition of different volumes. This makes image acquisition more variable and also enables acceleration, as will be explained in the following examples. Homogenization of the field strength of an excitation pulse is also conceivable in this way.

[0017] The local coil according to the invention comprises a local coil matrix with a plurality of antenna coils for detecting magnetic resonance signals and / or for transmitting an excitation pulse. Furthermore, the local coil comprises a device according to the invention. The device is arranged on a surface of the local coil such that, when the local coil is arranged on a patient as intended, the device is arranged on the patient's surface. The device can also be protected by a sheath, either a separate sheath or the sheath of the local coil; in other words, the device can also be arranged within the local coil.

[0018] The magnetic resonance imaging scanner according to the invention has a local coil according to the invention with a device according to the invention. The magnetic resonance imaging scanner further comprises a controller that has a signal connection with the control input of the device. The signal connection can be electrical, but optical signal connections via fiber optics or hydraulic or pneumatic signal connections are also conceivable. If the device has a plurality of segments made of field control material, the signal connection can also have a plurality of channels in order to control the segments independently of one another. A control unit or multiplexer that further distributes the channels as signals for the respective segment is also conceivable. The signal connection can also be wireless.

[0019] The control system of the magnetic resonance imaging scanner is designed to adjust the states of the field control material or the segments depending on a sequence. Various examples of how the local coil can improve image acquisition with the device and the magnetic resonance imaging scanner are given in the subclaims.

[0020] The local coil according to the invention and the magnetic resonance imaging device according to the invention share the advantages of the device.

[0021] The method according to the invention is carried out on a magnetic resonance imaging system according to the invention with a local coil and device according to the invention.

[0022] In one step of the magnetic resonance imaging scanner, an excitation pulse is emitted by the radio-frequency unit. The radio-frequency pulse depends on the selected image acquisition sequence. It is also conceivable for the excitation pulse to be emitted via the local coil instead of a body coil. A conceivable use of the device for coupling out the excitation pulse is specified below in the subclaims. In the simplest case, the field control material of the device is in a first state transparent to the alternating electric and / or magnetic fields during the emission of the excitation pulse.

[0023] In a further step of the method according to the invention, the control system of the magnetic resonance imaging system sets a second state of the field control material, in which the field strength of an incident electric and / or magnetic wavefront of an alternating field is increased in a predetermined first volume relative to the transparent state. In other words, in the second state of the field control material, the propagation conditions of the magnetic resonance signals are changed so that the antenna coil(s) preferentially detect signals from a predetermined volume.

[0024] In a further step, the focused magnetic resonance signals are captured with the local coil and forwarded to a receiver of the high-frequency unit of the magnetic resonance imaging scanner for further evaluation.

[0025] In another step of the process, an image is reconstructed from the acquired magnetic resonance signal, which is then output to a user in another step.

[0026] Advantageously, the method according to the invention enables accelerated and / or improved image acquisition in the magnetic resonance imaging device by changing the sensitivity range through the field control material.

[0027] In another embodiment of the method according to the invention, a B1 + -field map provided. With a B1 + A field map is a map that indicates the intensity of the excitation of the nuclear spins of the examination subject in a predetermined excitation pulse emitted via the local coil in a predetermined state of the field control material at a plurality of locations in an image acquisition field (FoV) of the magnetic resonance imaging scanner. Such a B1 +-Field map can be determined, for example, by a measurement or image acquisition with a homogeneous phantom with the predetermined excitation pulse in the predetermined state of the field control material. The B1 + -Field map can be determined, for example, in a calibration measurement and then stored in the control system of the magnetic resonance imaging system for future image acquisition. The B1 + -field map can also be obtained by convolving a local coil-specific B1 + -field map and a map for the magnetic resonance imaging scanner, which capture the influence of different positions of the local coil in the magnetic resonance imaging scanner, are provided in order to obtain a B1 + -Field map for different relative positions of the local coil without generating a new calibration measurement.

[0028] In a further step, a fourth state of the field control material is determined, which then homogenizes the excitation of the nuclear spins in the object under investigation upon emission of the predetermined excitation pulse. The fourth state differs in particular from the first state of the field control material, which is characterized in that the field control material is transparent in the first state and does not alter the propagation of the fields, in particular, does not homogenize them.

[0029] Homogenization is particularly important when the variation options for the predetermined excitation pulse are limited, e.g., because the number of transmission channels is restricted to a small number, such as one, two, four, or fewer than ten channels. Homogenization can be achieved by creating a dispersion or broader spatial distribution of the field in areas of high field strength, as explained below, and a focusing in areas of lower field strength. The fourth state can be determined, for example, using an optimization method in which the deviation of the field strengths from a mean value is minimized in the image acquisition area or a subset thereof.

[0030] The further steps are or will already be explained in more detail in connection with another embodiment of the method. The fourth state of the field control material is set by the controller. Subsequently, the predetermined excitation pulse is output by the radio-frequency unit, preferably by the local coil. A magnetic resonance signal is then acquired with the local coil. A reconstruction of an image is generated from the acquired magnetic resonance signal and output to a user.

[0031] Advantageously, the field control material can be used to homogenize the excitation of the nuclear spins and thus improve the image quality even with a small number of independent transmission channels of the radio-frequency unit.

[0032] Further advantageous embodiments are specified in the subclaims.

[0033] In one conceivable embodiment, the field control material is designed to be transparent to the alternating electric and / or magnetic field in a first state. Transparent is understood in particular to mean that the propagation or spatial distribution of the alternating electric and / or magnetic field remains unchanged by the field control material in the first state. In other words, the field strength is not altered by the field control material in the first transparent state, or is altered only in a spatially homogeneous manner outside the field control material, e.g., reduced to a small extent, for example, attenuated by less than 3 dB or 1 dB.

[0034] In a second state, the field control material increases the field strength of an incident electric and / or magnetic wavefront of an alternating field in a predetermined first volume relative to the transparent state. In other words, the field control material focuses the electric and / or magnetic alternating field in a predetermined manner in a predetermined volume in the second state.

[0035] In an advantageous manner, the change in the properties of the field control material allows the propagation condition of the fields to be varied, for example, to favor a certain volume in the reception case and to avoid a hazard caused by field peaks in the transmission case.

[0036] In one conceivable embodiment, the field control material has a third state. In this third state, the field control material is configured to increase the field strength of an incident electric and / or magnetic wavefront of an alternating field in a predetermined second volume relative to the transparent state. The second volume is different or disjoint from the first volume. In other words, in addition to the transparent state, which is used, for example, for the excitation of nuclear spins, a local coil matrix can achieve at least two predetermined different sensitivity patterns when receiving magnetic resonance signals using the field control material.

[0037] These different sensitivity patterns can be advantageously used to independently scan different areas for acceleration through parallelization. Image acquisition using compressed sensing, in which the same volume is captured with different sensitivity patterns, is also conceivable.

[0038] For this purpose, the field control material preferably has a plurality of predetermined states, each with different sensitivity patterns. This can be achieved, for example, by the field control material having a plurality of segments, each of whose at least two states can be controlled independently of one another. The combination or permutation of the states then results in a corresponding plurality of overall states or sensitivity patterns.

[0039] In one possible embodiment of the device according to the invention, the predetermined first volume or second volume is a cone, a wedge, or a layer parallel to a surface of the device. It is also conceivable that both the first volume and the second volume have the same shape, for example, in the form of layers or wedges, but have a different position or orientation.

[0040] Advantageously, cones, wedges or layers allow a spatial separation of the signals and thus an acceleration through parallelization.

[0041] In one conceivable embodiment of the local coil according to the invention, the device has a plurality of segments made of the field control material. The segments can be physically separate elements that are arranged adjacent to one another on the local coil in order to completely or partially cover the surface facing the patient. However, it is also conceivable for the segments to be merely logically distinguished in that the state or properties of an entire segment are each influenced by a common control input. The control input can also be viewed as a logical control input, i.e. several segments are controlled independently of one another via a multiplexed physical control input. A segment is then defined as a region of the field control material that can be set into different states independently of the other regions via a logical control input.In particular, each segment can be set separately to a first state or a second state via the control input.

[0042] Preferably, at least one segment of an antenna coil is located opposite the local coil matrix, and each segment is designed to be separately switched to the first state or the second state via the control input. It is also conceivable for a plurality of segments to be assigned to each antenna coil and arranged opposite one another.

[0043] It is considered to be opposite if a projection of the segment along a normal vector of an area enclosed by the antenna loop onto the surface lies entirely or at least largely, i.e., more than 50%, on the surface. The field control material can, for example, be arranged on a carrier material of the antenna coil or on a shell of the antenna coil or local coil matrix.

[0044] The plurality of segments of the field control material allows for a variety of sensitivity patterns when receiving the magnetic resonance signals and / or transmitting the excitation pulses, which advantageously enable parallelization or image acquisition using compressed sensing. With a plurality of segments located opposite a single antenna coil, it is also conceivable to enable adjustable beamforming or focusing and controlling the direction of the maximum sensitivity of the antenna coil.

[0045] In one possible embodiment of the magnetic resonance imaging system according to the invention, the alternating electric and / or magnetic field has a frequency in a range of a Larmor frequency of the nuclear spins to be imaged in the magnetic resonance imaging system. The Larmor frequency is defined by the magnetic moment of the spins to be imaged and the magnetic field provided by the magnetic resonance imaging system.

[0046] Especially for field-control materials such as metamaterials, which are provided, for example, by macroscopic resonance elements distributed throughout the metamaterial, the achievable frequency range for the states is limited. The precise definition of these effective frequencies by the Larmor frequency enables their effective use. However, it is also conceivable that other field-control materials could cover broad frequency ranges.

[0047] In one conceivable embodiment of the method according to the invention, the controller sets the first state of the field control material in a step prior to the step of emitting the excitation pulse. In the first state, the field control material is transparent to alternating electric and / or magnetic fields, i.e., the field control material changes the field strength and direction of the fields only slightly, for example, the direction of the field vectors by less than 30 degrees, 10 degrees, or 5 degrees, or the field strength by less than 6 dB, 3 dB, or 1 dB.

[0048] Advantageously, the transparent first state during the excitation pulse ensures that the field distribution remains unchanged and thus without new field peaks that could endanger a patient.

[0049] In one possible embodiment of the method according to the invention, the step of emitting the excitation pulse is repeated, the third state of the field control material is set by the controller in a step, and a magnetic resonance signal is again acquired in step . The third state differs from the second state in particular in that the sensitivity pattern for an antenna coil opposite or behind the field control material changes.

[0050] Advantageously, the sensitivity patterns altered by the third and possibly further states enable image acquisition by means of compressed sensing.

[0051] The above-described properties, features and advantages of this invention, as well as the manner in which they are achieved, will become clearer and more clearly understood in connection with the following description of the embodiments, which are explained in more detail in connection with the drawings.

[0052] They show: Fig. 1 a schematic representation of a magnetic resonance imaging apparatus according to the invention; Fig. 2 a schematic representation of a metamaterial usable for the invention; Fig. 3a-d show exemplary sensitivity ranges for a local coil with different states of the device according to the invention; Fig. 4 shows a relative dielectric constant or permeability for an exemplary metamaterial for use in the device according to the invention; Fig. 5a,b show exemplary control schemes for segments of a field control material of a device according to the invention; Fig. 6 shows an example of a field control material composed of a plurality of segments; Fig. 7 schematically shows a single subunit of a segment; Fig. 8a,b Application examples for an exemplary local coil according to the invention with the device according to the invention; Fig. 9 a schematic flow chart of an embodiment of the method according to the invention.

[0053] Fig. 1 shows a schematic representation of an exemplary embodiment of a magnetic resonance imaging device 1 according to the invention.

[0054] The magnet unit 10 has a field magnet 11 that generates a static magnetic field B0 for aligning nuclear spins of samples or patients 100 in a recording area. The recording area is arranged in a patient tunnel 16 that extends in a longitudinal direction 2 through the magnet unit 10. A patient 100 can be moved into the recording area by means of the patient bed 30 and the movement unit 36 ​​of the patient bed 30. The field magnet 11 is typically a superconducting magnet that can generate magnetic fields with a magnetic flux density of up to 3T, and even higher in the latest devices. However, permanent magnets or electromagnets with normally conducting coils can also be used for lower field strengths.

[0055] Furthermore, the magnet unit 10 has gradient coils 12, which are designed to superimpose variable magnetic fields in three spatial directions on the magnetic field B0 for spatial differentiation of the acquired imaging regions in the examination volume. The gradient coils 12 are typically coils made of normally conducting wires that can generate mutually orthogonal fields in the examination volume.

[0056] The magnet unit 10 also has a body coil 14, which is designed to emit a high-frequency signal supplied via a signal line 33 into the examination volume and to receive resonance signals emitted by the patient 100 and transmit them via a signal line. Preferably, however, the body coil 14 for transmitting and / or receiving the high-frequency signal is replaced by local coils 50, which are arranged in the patient tunnel 16 close to the patient 100. However, it is also conceivable that the local coil 50 is designed for both transmitting and receiving, and therefore a body coil 14 can be omitted.

[0057] 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. A controller 23 of the magnetic resonance imaging system 1 coordinates the subunits.

[0058] Thus, the control unit 20 has a gradient control 21 which is designed to supply the gradient coils 12 with variable currents via supply lines, which provide the desired gradient fields in the examination volume in a time-coordinated manner.

[0059] Furthermore, the control unit 20 has a radio-frequency unit 22, which is designed to generate a radio-frequency pulse with a predetermined temporal profile, amplitude, and spectral power distribution for exciting a magnetic resonance of the nuclear spins in the patient 100. Pulse powers in the kilowatt range can be achieved. The individual units are interconnected via a signal bus 25.

[0060] The radio-frequency signal generated by the radio-frequency unit 22 is fed to the body coil 14 via a signal connection and transmitted into the body of the patient 100 to stimulate the nuclear spins there. However, it is also conceivable to transmit the radio-frequency signal via one or more local coils 50.

[0061] The local coil 50 then preferably receives a magnetic resonance signal from the body of the patient 100. Due to the short distance, the signal-to-noise ratio (SNR) of the local coil 50 is better than when received by the body coil 14. The MR signal received by the local coil 50 is processed in the local coil 50 and forwarded to the radio-frequency unit 22 of the magnetic resonance imaging scanner 1 for evaluation and image acquisition. Preferably, the signal connection 33 is used for this purpose, but wireless transmission is also conceivable.

[0062] The local coil 50 has a device 60 with a field control material 70, which, when arranged according to the application, is located between the local coil 50 and the patient 100. The device 60 can, for example, be arranged on a casing of the local coil 50, inside or outside, or can also be designed separately, so that the device 60 can be used with different local coils 50.

[0063] Fig. Figure 2 shows a schematic representation of an exemplary field control material 70 in the form of a metamaterial that can be used for the invention. The metamaterial is intended to influence the fields of the magnetic resonance signals. It therefore has small resonance elements 72 for alternating electric and / or magnetic fields at the Larmor frequency. These can, for example, be provided, as schematically shown, by parallel resonant circuits that have an induction loop with a capacitor. The resonance elements 72 are preferably arranged in a regular grid. In order to be able to set different states of the field control material 70, it is conceivable that, for example, the capacitance is provided by a PIN diode. Via a control terminal that is in Fig. 2 is not shown for reasons of clarity, a variable voltage can be applied, which changes the capacitance and thus the resonant frequency of the resonant element 72. In particular, when the resonant frequency of the resonant element is set close to the Larmor frequency, the properties of the metamaterial change significantly depending on the voltage. The properties are comparable to the refractive properties of optical materials, as long as the resonant elements are significantly smaller than the wavelength of a radio wave at the Larmor frequency.

[0064] It is conceivable that the control connections are interconnected in groups, creating segments 71 in which the states of the metamaterial can be adjusted independently of one another. By appropriately distributing the segments and adjusting the states, configurations similar to an optical lens can be provided that focus the fields or waves, i.e., bundle a sensitivity range of a local coil matrix onto a predetermined volume on a side of the field control material 70 facing away from the patient 100. However, segments 71 can also be provided by physically separate elements of the field control material or metamaterial.

[0065] It is also conceivable that the metamaterial contains a multitude of layers, as in Fig. 2 are shown as examples, stacked on top of each other.

[0066] Furthermore, the metamaterial with electrically adjustable resonance elements 72 is merely one possibility for a field control material. Other materials or metamaterials are also known whose properties can be controlled by the magnetic resonance imaging system 1.

[0067] In addition to the RF metamaterial using varactors or PIN diodes already explained, other electrically tunable materials such as liquid crystals, ferroelectric materials, magnetostrictive materials or electroactive polymers are conceivable.

[0068] Other field-control materials include tunable dielectrics. Tunable dielectrics are materials that change their dielectric properties or permittivity in response to external influences such as electric fields, temperature, or optical excitation. The specific microscopic mechanisms behind these properties depend on the material in question.

[0069] The field control material may, for example, have a negative refractive index for alternating electric and / or magnetic fields at the Larmor frequency and thus cause a focusing of the sensitivity in the vicinity of the local coil on the surface of the patient 100.

[0070] Fig. 3a to 3d show exemplary sensitivity ranges 52 for a local coil 50 without device 60 or with different states of the device 60.

[0071] In Fig. 3a initially shows a sensitivity range 52 for the local coil 50 on the patient 100. The course of the sensitivity range 52 is represented by a line on which a signal source with a constant field strength produces a constant voltage or current in the local coil 50 or its antenna coils 51.

[0072] In Fig. 3b, the device 60 with the field control material 70 is arranged according to the application between the local coil 50 and patient 100. In the Fig. 3b, the field control material 70 is in a first, transparent state, in which the sensitivity range 51 is essentially unchanged. A slight change is caused, for example, by the dielectric or permeable properties of a carrier material or the properties of the metamaterial without external influence. Due to the reversibility of the electromagnetic waves, the sensitivity range 51 also reflects a field strength distribution when the antenna coil 51 is used as a transmitting antenna. The transparent state therefore also allows for anticipating a field strength distribution that would be caused by the body coil during transmission when the local coil 50 is not connected. The transparent first state therefore also enables a reliable determination of the field strengths for the SAR assessment.

[0073] In Fig. 3c shows a sensitivity region 51 in a second state of the field control material 60. In this second state, the sensitivity region 52 is narrower and extends deeper into the interior of the patient 100. Such a sensitivity region can be achieved, for example, by dividing the field control material 70 into separately controllable segments 71. This focusing can be carried out in two dimensions, so that the sensitivity region 71 is wedge-shaped, or in three dimensions, if the peripheral segments 71 surround the central segment 71 in two dimensions, so that the sensitivity region 71 resembles a pointed cone or a lobe. Examples of the segmentation and control are given below. Fig. 4 and Fig. 5 shown.

[0074] In Fig. 3d, however, a sensitivity range 71 is indicated, which concentrates the sensitivity of the local coil 50 on a region near the local coil 50 on the surface of the patient 100. This can be achieved, for example, as already explained, by a control that puts the metamaterial or field control material 70 into a state with a negative refractive index for electromagnetic waves at the Larmor frequency.

[0075] Fig. Figure 4 shows schematically the relative dielectric constant or permeability for a metamaterial with tunable resonance elements 72. On the ordinate is the permeability µ r or relative dielectric constant ε Rof the metamaterial, with the frequency on the abscissa. With different applied voltages (U1, U2, U3) to the variable capacitance, the resonance curve shifts. If one considers the values ​​of the permeability or dielectric constant for a constant frequency, for example, Larmor frequency, these change for this frequency with the voltage. With the voltage, the refractive index for an electromagnetic wave of a predetermined frequency, for example, the Larmor frequency of the nuclear spins to be detected, can be changed in the segment of the field control material 70. With a matrix on segment 71 of the field control material 70, the following can then be Fig. 5 shown

[0076] Fig. Figure 5a shows a control scheme in which two peripheral rows of segments 71 surround the intermediate rows of segments 71. In principle, the rows of segments could also be replaced by corresponding stripes. The numbers in the segments 71 indicate the intensity or level of control.

[0077] For example, the control of the resonant elements 72 with varactors or PIN diodes as variable capacitances can be achieved by adjusting the applied voltage. The capacitance of a diode can also be varied using optical signals.

[0078] For variable dielectrics or materials with variable permeability, it is also conceivable to modify the properties by voltages or applied electric fields or, in the case of optically active materials, to control them with an illumination intensity.

[0079] In Fig. 5 a,b show lines for column control 74 and row control 75, by which a pixel 73 of a segment 71 can be controlled at an intersection point of column control 74 and row control 75. It is conceivable that a segment control is provided for a segment 71, which receives a control command, for example, via a serial line, which is then converted into control signals for the column control 74 and the row control 75 in order to reduce the number of lines.

[0080] The predetermined pattern achieves a focusing of the alternating fields comparable to a cylindrical magnifying glass arranged along the columns, so that the sensitivity area 72 is focused in the center.

[0081] In Fig. 5b, however, the excitation pattern is arranged rotationally symmetrically around the center of the field control element. This also results in a rotationally symmetrical shape of the sensitivity region 52, comparable to a lobe, as in Fig. 3c is shown.

[0082] It is also conceivable to combine the high control values ​​with the low control values ​​in the schemes. Fig. 4a and Fig. 4b. This can result in correspondingly flattened, near-surface sensitivity areas 52 as in Fig. 3d representation can be achieved.

[0083] The different sensitivity ranges can be used, for example, to Fig. 3d, to focus the signal on a near-surface layer in the patient 100 and thus improve the SNR for images of these layers. It is also conceivable to use wedge-shaped sensitivity regions as in Fig. 3c to decouple adjacent layers of a parallel scan and thus accelerate the acquisition.

[0084] Fig. 6 shows by way of example how from a multitude of segments 71, as shown in Fig. 5 a,b, a field control material 70 can be assembled over a large area. The individual segments 71 can be physically separated from one another and assembled like a type of tile to form the field control material 70. However, it is also conceivable that the division into segments 71 and their subunit pixels 73 is merely logical due to the separate controllability of the subunit in a one-piece segment 71 or field control material 70.

[0085] For example, a segment can have dimensions comparable to those of an antenna coil 51 of an antenna matrix of the local coil 50 and can be individually assigned to it.

[0086] Fig. 7, in turn, schematically illustrates a single subunit of a segment 71, referred to as a pixel 73. The pixel 73 can be a single piece of a field control material 70 or a section of a large-area piece of the field control material 70, for example, a segment 71 or the entire field control material 70. The pixel 73 is then defined by the control.

[0087] The control in Fig. Figure 7 shows an example of a field-controlled pixel. Electrodes 77 are located above and below pixel 73. At least one of the electrodes 77 is structured and defines pixel 73 through its lateral extension on the surface of the field-control material 70. The second electrode 77 can be flat, e.g., a ground electrode, or also structured, for example, to allow the polarity of the voltage at a pixel to be independently adjusted.

[0088] Preferably, each pixel 73 is assigned a switching element 76, which maintains the voltage at the electrodes 77, even when the individual pixel 73 is not currently being actively adjusted. For example, it is conceivable that a setting value for a pixel 73 is adopted by the switching element 76 if the signal to be adjusted is not equal to 0 at one of the column control 74 and row control 75 and a selection signal is present at the other. The lines and the switching element 76 are preferably arranged on one or both surfaces of the field control material 70. It is also conceivable that, with a more complex switching element 76, an adjustment could also be made via a common control line for all pixels 73 of the segment 71 or of the entire field control material 70.

[0089] Instead of electrodes, it is also conceivable for the switching element 76 to control a light source such as an LED or an OLED in an optically variable field control material 70. Alternatively, a light intensity can also be achieved using light control elements such as LCD cells, comparable to an LCD matrix on the field control material 70, and a planar illumination.

[0090] In Fig. 8a and Fig. Figure 8b shows another application of variable sensitivity ranges 52, which is used for image acquisition using compressed sensing. In compressed sensing, the volume to be imaged is scanned using different sensitivity patterns.

[0091] In the Fig. 8a and Fig. 8b, a local coil 50 with a plurality of antenna coils 51 is arranged on the patient 100. A field control material 70 is arranged between the local coil 50 and the patient 100, either as part of the local coil 50 or as a separate device 60. The field control material 70 can be formed in one piece or arranged in individual elements as shown. It is essential that the sensitivity range 52 of an antenna coil 51 can be changed by a control signal to the field control material. Depending on the properties of the field control material 70, this change can be achieved by controlling the entire element of field control material 70 beneath the antenna coil 51, or as in Fig. 5a and Fig. 5b by different control of Fig. 8a and Fig. 8b not individually shown segments 71 of the field control material 70 between the antenna coil 51 and the patient 100.

[0092] In Fig. 8a and Fig. Figure 8b shows two different scanning patterns of the sensitivity areas 52 as examples. It is important that each volume element to be imaged is captured by different antenna coils with different sensitivity patterns. The patterns can be achieved by different control of the segments 71, as shown in Fig. 5a and Fig. 5b. Preferably, the sensitivity patterns are orthogonal to each other so that the data required for image reconstruction can be acquired with the smallest possible number of samples.

[0093] Advantageously, the compressed sensing method can also be retrofitted to existing local coils 50 by means of a device 60 separate from the local coil 50.

[0094] Fig. Figure 9 shows a schematic flowchart of an embodiment of the method according to the invention. In a step S20, the radio-frequency unit 22 outputs an excitation pulse. This can be done, for example, via the body coil 14, but also via the local coil 50 if this is designed as a transmit coil. The excitation pulse can be accompanied by other signals within the scope of a selected imaging sequence, for example, by magnetic gradient fields generated by the gradient controller 21 with the gradient coils 12.

[0095] In a further step S30, the controller 30 sets a second state of the field control material 70. The second state differs from a transparent state by different sensitivity ranges 52. The state can, for example, be one of the sensitivity patterns associated with Fig. 3. It is also conceivable that the local coil 50 comprises a matrix of antenna coils 51 with elements or regions of the field control material 70 assigned to the antenna coils, as for example in Fig. 8a, Fig. 8b, and the controller 23 sets a different second state, which differs from the transparent first state, in each element or region of the field control material 70. This can be done, for example, in the context of image acquisition with compressed sensing, as in Fig. 8a, Fig. 8b, can be used to scan the volume with different sensitivity patterns. However, an identical state of all areas or elements of the field control material 70 with the same relative sensitivity range for each antenna coil is also conceivable, for example, to Fig. 3 d explains how to improve the SNR when imaging a near-surface volume.

[0096] In a step S50, the controller 23 then acquires a magnetic resonance signal using the radio frequency unit 22 and the local coil 50 with the sensitivity pattern set in the second state of the field control material.

[0097] In a step S60, the controller 23 or a dedicated image reconstruction computer reconstructs an image from the magnetic resonance data. Preferably, steps S20, S30, and S50 are repeated with different settings, for example, an excitation pulse with a different frequency, amplitude, and / or phase and / or different gradient fields, to ensure sufficient sampling in k-space.

[0098] The reconstructed image can then, for example, be output to a user on an output device or further evaluated automatically.

[0099] In a preferred embodiment of the method according to the invention, in a step S10, before the excitation pulse is emitted in step S20, a first state of the field control material 70 is set by the controller 23, in which the field control material 70 is essentially transparent to the excitation pulse, in particular, its fields are not amplified or focused in a volume. In this way, it can be ensured that the SAR limits are also adhered to with the device 60 without having to change the excitation pulses or adapt the SAR monitoring.

[0100] In one embodiment of the method according to the invention, step S20 of emitting the excitation pulse is repeated, i.e. the nuclear spins are excited again.

[0101] In step S40, a third state of the field control material is set by the controller 23. The third state has a different sensitivity range than the second state, but in particular, it is also not the transparent first state. Using this modified sensitivity range, the controller 23 then acquires magnetic resonance signals with the radio-frequency unit 22 and the local coil 50.

[0102] Preferably, further excitation pulses are applied, further different states of the field control material 70 are set with further different sensitivity patterns, and the magnetic resonance signals are acquired with these different states. In this way, the volume to be imaged is scanned in different ways using the same local coil, which is ultimately used to reconstruct an image from these magnetic resonance signals using the compressed sensing method.

[0103] In an advantageous manner, imaging by compressed sensing can be used with an existing local coil 50 by means of the device 60.

[0104] In a possible embodiment of the method according to the invention for operating a magnetic resonance imaging apparatus (1), the field control material 70 is used to homogenize an excitation of the nuclear spins to be detected.

[0105] To do this, it is first necessary to determine how the excitation occurs without homogenization. This can be done, for example, by excitation and measurement with the local coil using a phantom with a homogeneous nuclear spin distribution. In this case, the field control material 70 is not adjusted or adjusted homogeneously, so that the properties of the fields do not depend on the location in relation to the field control material. Using a subsequent image, the excitation can be recorded and stored as B1. +-card can be provided. The card can then be stored in the controller 23 for future image acquisition. For image acquisition, the B1 + -Card can be provided by the controller 23 from the memory.

[0106] In a further step, the controller 23 determines a fourth state of the field control material 70 depending on the B1 + -Field map is determined in such a way that the excitation is homogenized with a predetermined excitation pulse. The fourth state is therefore particularly different from the first state in which the field control material 70 is configured transparently or homogeneously. For this purpose, settings for the individual areas of the field control material 70 must homogenize the field strength in a region of the examination object to be detected. For locations with higher field strength, a distribution or defocusing of the fields can be used, as already described. Fig.5 a,b, while focusing is required for areas with low field strength. The controller 23 can determine a fourth state by simulating the fields in an optimization process under the boundary condition that a mean square deviation does not exceed a limit.

[0107] However, it is also conceivable that a fourth state of the field control material 70 is determined by the controller 23, in which the excitation fields are focused on a predetermined partial area of ​​the examination subject or the patient 100. This is also referred to as zoomed MRI, in which the image acquisition zooms into the partial area.

[0108] Finally, the determined fourth state in the field control material 70 is set by the controller 23 in a step S10 before the excitation pulse is output by the radio frequency unit 22.

[0109] Further image acquisition is carried out as already described for the other embodiments.

[0110] Although the invention has been illustrated and described in detail by the preferred embodiment, the invention is not limited to the disclosed examples and other variations may be derived therefrom by those skilled in the art without departing from the scope of the invention. QUOTES CONTAINED IN THE DESCRIPTION

[0000] This list of documents submitted by the applicant was generated automatically and is included solely for the convenience of the reader. This list is not part of the German patent or utility model application. The DPMA assumes no liability for any errors or omissions. Cited patent literature

[0000] US 10324152 B2 [0007, 0010] WO 2002059059 A2

[0012] US 7852176 B2

[0012]

Claims

[1] Device with a field control material (70) for arranging between a local coil (50) and a patient (100), wherein the device (60) has a control input and the field control material (70) is designed to change the spatial propagation of an alternating electric and / or magnetic field in dependence on a control signal at the control input. [2] Device according to claim 1, wherein the field control material (70) is designed to be transparent to the alternating electric and / or magnetic field in a first state and to increase the field strength of an incident electric and / or magnetic wavefront of an alternating field in a predetermined first volume relative to the transparent state in a second state. [3] The device of claim 2, wherein the field control material (70) is configured to increase, in a third state, the field strength of an incident electric and / or magnetic wavefront of an alternating field in a predetermined second volume relative to the transparent state, the second volume being different or disjoint from the first volume. [4] The device of claim 2 or 3, wherein the predetermined first volume and / or second volume is a cone, a wedge or a layer parallel to a surface of the device. [5] Local coil with a local coil matrix and a device (60) according to one of the preceding claims, wherein the device is arranged on a surface of the local coil (50) such that the device is arranged on a patient (100) on the surface of the patient when the local coil (50) is arranged according to the application. [6] Local coil according to claim 5, wherein the device (60) comprises a plurality of segments (71) made of the field control material (70), wherein at least one segment (71) is opposite an antenna coil (51) of the local coil matrix and each segment (1) is designed to be set separately to the first state or the second state via the control input. [7] Magnetic resonance imaging apparatus with a local coil (50) according to claim 5 or 6, wherein the magnetic resonance imaging apparatus has a controller (23) which is in signal connection with the control input of the device (60), wherein the controller (23) is designed to adjust the states of the field control material (70) as a function of a sequence. [8] Magnetic resonance tomograph according to claim 7, wherein the alternating electric and / or magnetic field has a frequency in a range of a Larmor frequency of nuclear spins to be imaged in the magnetic resonance tomograph (1). [9] Magnetic resonance imaging apparatus according to claim 7 or 8, wherein the controller (23) is designed to place the field control material (70) into the first state during an excitation pulse and into the second state during reception of a magnetic resonance signal. [10] Method for operating a magnetic resonance imaging apparatus (1) according to one of claims 7 or 8, wherein the method comprises the steps Outputting an excitation pulse (S20) by the high-frequency unit (22); Setting the second state (S30) of the field control material (70) by the controller (23); Acquiring a magnetic resonance signal (S50) with the local coil (50); Reconstructing an image (S60) from the acquired magnetic resonance signal; Output the reconstructed image to a user. [11] Method according to claim 10, wherein before the step (S20) of emitting the excitation pulse in a step (S10) the controller (23) sets the first state (S10) of the field control material (70). [12] Method according to claim 10 or 11 and a device (60) according to claim 3, wherein the step (S20) of emitting the excitation pulse is repeated, in a step (S40) the third state of the field control material (70) is set by the controller (23), and in step (S50) a magnetic resonance signal is again acquired. [13] Method for operating a magnetic resonance imaging apparatus (1) according to claim 7, wherein the method comprises the steps: Providing a B1 + -field map; Determining a fourth state of the field control material depending on the B1 + -field map; Setting the fourth state (S10) of the field control material (70) by the controller (23); Outputting a predetermined excitation pulse (S20) by the high-frequency unit (22); Acquiring a magnetic resonance signal (S50) with the local coil (50); Reconstructing an image (S60) from the acquired magnetic resonance signal; Output the reconstructed image to a user. [14] Computer program product which can be loaded into a memory unit of a controller (23) of a magnetic resonance tomograph (1) according to one of claims 7 to 9, comprising program code means for executing a method according to one of claims 10 to 13 when the computer program product is executed in the controller (23) of the magnetic resonance tomograph (1). [15] Computer-readable medium on which program code means are stored which can be read by a controller (23) of a magnetic resonance imaging apparatus (1) according to one of claims 7 to 9 and can be executed by the controller (23) in order to carry out a method according to one of claims 10 to 13.

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