Magnetic resonance imaging apparatus and image generating method

Abstract

To generate a magnetic resonance image with improved image quality.SOLUTION: An MRI device according to an embodiment acquires a plurality of MR signals corresponding to a plurality of lead-out directions including a first lead-out direction and a second lead-out direction intersecting with the first lead-out direction. The MRI device includes a specification unit, a setting unit, a low-pass filter, and a generation unit. The specification unit specifies a signal region related to generation of an MR signal in a subject. The setting unit sets a cut-off frequency related to a passband of the MR signal on the basis of the signal region. The low-pass filter filters a plurality of MR signals obtained by scanning the subject in the plurality of lead-out directions by using the cut-off frequency. The generation unit generates an MR image on the basis of MR data generated by A / D conversion for the MR signal output from the low-pass filter.SELECTED DRAWING: Figure 4

Description

[Technical field]

[0001] The embodiments disclosed in this specification and the drawings relate to a magnetic resonance imaging apparatus and an image generating method. [Background technology]

[0002] A common problem in imaging with magnetic resonance imaging (MRI) devices is image aliasing caused by an insufficient sampling rate for the received magnetic resonance (MR) signal (in other words, an insufficient field of view, which corresponds to the reciprocal of the sampling interval). Techniques to address this problem include setting a low-pass filter in accordance with the sampling rate and oversampling the MR signal.

[0003] However, in a scan in which the readout direction changes, such as a radial scan, when the low-pass filter in the technology is used on MR signals, the amount of signals cut by the low-pass filter varies depending on the readout direction. As a result, the consistency of MR data arranged in k-space between different readout directions is lost. This causes a problem that noise such as line-shaped artifacts called streaks occurs in MR images generated in association with a scan in which the readout direction changes, resulting in a deterioration in image quality. [Prior art documents] [Patent documents]

[0004] [Patent Document 1] JP 2020-115967 A Summary of the Invention [Problem to be solved by the invention]

[0005] One of the problems to be solved by the embodiments disclosed in this specification and the drawings is to generate a magnetic resonance image with improved image quality. However, the problems to be solved by the embodiments disclosed in this specification and the drawings are not limited to the above problem. Problems corresponding to the effects of each configuration shown in the embodiments described later can also be positioned as other problems. [Means for solving the problem]

[0006] A magnetic resonance imaging apparatus according to an embodiment acquires a plurality of magnetic resonance signals corresponding to a plurality of readout directions including a first readout direction and a second readout direction intersecting the first readout direction. The magnetic resonance imaging apparatus includes an identifying unit, a setting unit, a low-pass filter, and a generating unit. The identifying unit identifies a signal region related to generation of a magnetic resonance signal in a subject. The setting unit sets a cutoff frequency related to a passband of the magnetic resonance signal based on the signal region. The low-pass filter filters the plurality of magnetic resonance signals acquired by scanning the subject in the plurality of readout directions using the cutoff frequency. The generating unit generates a magnetic resonance image based on magnetic resonance data generated by A / D conversion of the magnetic resonance signal output from the low-pass filter. [Brief description of the drawings]

[0007] [Figure 1] FIG. 1 is a block diagram showing an example of a magnetic resonance imaging apparatus according to a first embodiment. [Diagram 2] FIG. 2 is a diagram showing an example of a configuration of a receiving circuit according to the first embodiment. [Diagram 3] FIG. 3 is a diagram showing an example of a trajectory in k-space regarding readout of MR signals in a main scan according to the first embodiment. [Figure 4] FIG. 4 is a flowchart showing an example of a procedure of an image generation process according to the first embodiment. [Diagram 5] FIG. 5 is a diagram showing an example of a signal region in a locator image according to the first embodiment. [Figure 6] FIG. 6 is a diagram showing an example of readout directions and sampling points in k space, and signal regions in image space, various FOVs, reconstruction regions, stopbands, and cutoff positions corresponding to cutoff frequencies according to the first embodiment. [Figure 7] FIG. 7 is a diagram showing an example of readout directions and sampling points in k space, and signal regions in image space, various FOVs, reconstruction regions, stopbands, and cutoff positions corresponding to cutoff frequencies according to the first embodiment. [Figure 8] FIG. 8 is a diagram showing an example of readout directions and sampling points in k space, and signal regions in image space, various FOVs, reconstruction regions, stopbands, and cutoff positions corresponding to cutoff frequencies according to the first embodiment. [Figure 9] FIG. 9 relates to the first embodiment and is a diagram for explaining effects in the first embodiment. [Figure 10] FIG. 10 is a block diagram showing an example of a magnetic resonance imaging apparatus according to the second embodiment. [Figure 11] FIG. 11 is a diagram showing an example of readout directions and sampling points in k space, and signal regions in image space, various FOVs, reconstruction regions, stopbands, and cutoff positions corresponding to cutoff frequencies according to the second embodiment. [Figure 12] FIG. 12 is a diagram showing an example of readout directions and sampling points in k space, and signal regions in image space, various FOVs, reconstruction regions, stopbands, and cutoff positions corresponding to cutoff frequencies according to the second embodiment. DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

[0008] Hereinafter, embodiments of a magnetic resonance imaging (hereinafter referred to as MRI) device and an image generating method will be described in detail with reference to the drawings. Note that the technical concept of the present embodiment may be applied to various modalities combined with an MRI device, such as a PET (Positron Emission Tomography)-MRI device and a SPECT (single photon emission computed tomography)-MRI device.

[0009] (First embodiment) Fig. 1 is a diagram showing an example of an MRI apparatus 100 according to this embodiment. As shown in Fig. 1, the MRI apparatus 100 includes a static magnetic field magnet 101, a gradient magnetic field coil 103, a gradient magnetic field power supply 105, a bed 107, a bed control circuit 109, a transmission circuit 113, a transmission coil 115, a reception coil 117, a reception circuit 119, an imaging control circuit (imaging control circuit) 121, a system control circuit (system control circuit) 123, a memory 125, an input interface 127, a display 129, and a processing circuit 131.

[0010] The static magnetic field magnet 101 is a magnet formed in a hollow, approximately cylindrical shape. The static magnetic field magnet 101 generates a substantially uniform static magnetic field in the internal space. As the static magnetic field magnet 101, for example, a superconducting magnet or the like is used.

[0011] The gradient coil 103 is a coil formed in a hollow, approximately cylindrical shape, and is disposed on the inner surface side of a cylindrical cooling vessel. The gradient coil 103 receives currents individually from a gradient power supply 105 to generate gradient magnetic fields whose magnetic field strength changes along each of the mutually orthogonal X, Y, and Z axes. The gradient magnetic fields of the X, Y, and Z axes generated by the gradient coil 103 form, for example, a slice selection gradient magnetic field, a phase encoding gradient magnetic field, and a frequency encoding gradient magnetic field. The slice selection gradient magnetic field is used to arbitrarily determine an imaging cross section. The phase encoding gradient magnetic field is used to change the phase of a magnetic resonance signal (hereinafter referred to as an MR (Magnetic Resonance) signal) according to a spatial position. The frequency encoding gradient magnetic field is used to change the frequency of an MR signal according to a spatial position.

[0012] The gradient magnetic field power supply 105 is a power supply device that supplies a current to the gradient magnetic field coil 103 under the control of the imaging control circuit 121 .

[0013] The bed 107 is a device including a top plate 1071 on which the subject P is placed. The bed 107 inserts the top plate 1071 on which the subject P is placed into the bore 111 under the control of a bed control circuit 109.

[0014] The bed control circuit 109 is a circuit that controls the bed 107. The bed control circuit 109 drives the bed 107 in response to an instruction from an operator via the input / output interface 17, thereby moving the tabletop 1071 in the longitudinal direction, the up-down direction, and in some cases, the left-right direction.

[0015] The transmission circuit 113 supplies a radio frequency pulse modulated at the Larmor frequency to the transmission coil 115 under the control of the imaging control circuit 121. For example, the transmission circuit 113 has an oscillation unit, a phase selection unit, a frequency conversion unit, an amplitude modulation unit, an RF amplifier, and the like. The oscillation unit generates an RF pulse of a resonance frequency specific to a target atomic nucleus in a static magnetic field. The phase selection unit selects the phase of the RF pulse generated by the oscillation unit. The frequency conversion unit converts the frequency of the RF pulse output from the phase selection unit. The amplitude modulation unit modulates the amplitude of the RF pulse output from the frequency conversion unit according to, for example, a sinc function. The RF amplifier amplifies the RF pulse output from the amplitude modulation unit and supplies it to the transmission coil 115.

[0016] The transmission coil 115 is an RF (Radio Frequency) coil disposed inside the gradient magnetic field coil 103. In response to the output from the transmission circuit 113, the transmission coil 115 generates an RF pulse that corresponds to a high frequency magnetic field.

[0017] The receiving coil 117 is an RF coil disposed inside the gradient magnetic field coil 103. The receiving coil 117 receives an MR signal emitted from the subject P by a high frequency magnetic field. The receiving coil 117 outputs the received MR signal to a receiving circuit 119. The receiving coil 117 is, for example, a coil array having one or more, typically a plurality of coil elements. For the sake of concrete explanation, the receiving coil 117 will be described below as a coil array having a plurality of coil elements.

[0018] The receiving coil 117 may be composed of one coil element. Although the transmitting coil 115 and the receiving coil 117 are shown as separate RF coils in Fig. 2, the transmitting coil 115 and the receiving coil 117 may be implemented as an integrated transmitting / receiving coil. The transmitting / receiving coil corresponds to an imaging region of the subject P, and is, for example, a local transmitting / receiving RF coil such as a head coil.

[0019] The receiving circuit 119 generates a digital MR signal (hereinafter referred to as MR data) based on the MR signal output from the receiving coil 117 under the control of the imaging control circuit 121. Specifically, the receiving circuit 119 performs signal processing such as detection and filtering on the MR signal output from the receiving coil 117, and then performs analog / digital (A / D (Analog to Digital)) conversion (hereinafter referred to as A / D conversion) on the data subjected to the signal processing to generate MR data. The receiving circuit 119 outputs the generated MR data to the imaging control circuit 121. For example, the MR data is generated for each coil element and output to the imaging control circuit 121 together with a tag that identifies the coil element.

[0020] 2 is a diagram showing an example of the receiving circuit 119. The receiving circuit 119 has, for example, a low pass filter 191 and an A / D converter 193. Note that in addition to the low pass filter 191 and the A / D converter 193, the receiving circuit 119 may also be equipped with various circuits, such as a detector, that correspond to the above signal processing.

[0021] A cutoff frequency set by the setting function 35 is input to the low-pass filter 191 via the imaging control circuit 121. That is, the pass band of the low-pass filter 191 is set by the setting function 35. Note that the cutoff frequency may be input directly from the processing circuit 131 to the low-pass filter 191. The low-pass filter 191 filters the MR signal using the input cutoff frequency.

[0022] The sampling frequency set by the setting function 35 is input to the A / D converter 193 via the imaging control circuit 121. That is, the sampling interval in the low-pass filter 191 is set by the setting function 35. The A / D converter 193 samples the MR signal that has passed through the low-pass filter 191 at a sampling timing according to the sampling frequency. In this way, the A / D converter 193 generates MR data.

[0023] The imaging control circuit 121 controls the gradient magnetic field power supply 105, the transmission circuit 113, the reception circuit 119, etc. according to the imaging protocol output from the processing circuit 15, and performs imaging of the subject P. The imaging protocol has a pulse sequence according to the type of examination. The imaging protocol defines the magnitude of the current supplied to the gradient magnetic field coil 103 by the gradient magnetic field power supply 105, the timing at which the gradient magnetic field power supply 105 supplies the current to the gradient magnetic field coil 103, the magnitude and time width of the high frequency pulse supplied to the transmission coil 115 by the transmission circuit 113, the timing at which the high frequency pulse is supplied to the transmission coil 115 by the transmission circuit 113, the timing at which the MR signal is received by the reception coil 117, etc. When the imaging control circuit 121 drives the gradient magnetic field power supply 105, the transmission circuit 113, the reception circuit 119, etc. to image the subject P, and receives MR data from the reception circuit 119, the imaging control circuit 121 transfers the received MR data to the processing circuit 131.

[0024] The imaging control circuit 121 executes a pulse sequence related to imaging to collect MR data. The imaging executed in this embodiment corresponds to a scan for acquiring a plurality of MR signals corresponding to a plurality of readout directions including a first readout direction and a second readout direction intersecting the first readout direction. As a result, the MRI apparatus 100 acquires a plurality of MR signals corresponding to a plurality of readout directions including the first readout direction and the second readout direction intersecting the first readout direction.

[0025] Fig. 3 is a diagram showing an example of a trajectory kTra in k-space related to the readout of MR signals in the main scan. The main scan may be, for example, a two-dimensional radial acquisition R2D, a three-dimensional radial acquisition (stack-of-stars Sos, koosh-ball KB), a PROPELLER (periodically rotated overlapping parallel lines with enhanced reconstruction) acquisition PRP, or another acquisition BL2 using, for example, two blades, as shown in Fig. 3.

[0026] For the sake of specificity, the following description will be given assuming that the main scan is a two-dimensional radial acquisition R2D. The two-dimensional radial acquisition R2D will be simply referred to as radial acquisition below. The number of readouts in the radial acquisition performed as the main scan for the subject P, that is, the number of trajectories kTra in the readout direction, is set in advance prior to the main scan.

[0027] The imaging control circuit 121 may also collect MR data (hereinafter referred to as coil sensitivity data) related to the generation of an image (hereinafter referred to as a coil sensitivity map) showing the distribution of sensitivity of the receiving coil 117 used to image the subject P by any imaging method. The coil sensitivity map is expressed by complex number data. The collection of the coil sensitivity data is executed by the imaging control circuit 121 in a pre-scan including a locator scan, for example, prior to a radial collection R2D as a main scan. The imaging control circuit 121 is realized by, for example, a processor.

[0028] The term "processor" refers to circuits such as a CPU, a graphics processing unit (GPU), an application specific integrated circuit (ASIC), a programmable logic device (e.g., a simple programmable logic device (SPLD), a complex programmable logic device (CPLD), and a field programmable gate array (FPGA)).

[0029] The system control circuit 123 has a processor, memories such as a ROM (Read-Only Memory) and a RAM (Random Access Memory), etc., which are not shown as hardware resources, and uses a system control function to control the MRI apparatus 100. Specifically, the system control circuit 123 reads out a system control program stored in the memory, expands it on the memory, and controls each circuit of the MRI apparatus 100 according to the expanded system control program.

[0030] For example, the system control circuit 123 reads out an imaging protocol from the memory 125 based on imaging conditions input by an operator via the input interface 127. The system control circuit 123 transmits the imaging protocol to the imaging control circuit 121 and controls imaging of the subject P. The system control circuit 123 is realized by, for example, a processor. The system control circuit 123 may be incorporated in the processing circuit 15. In this case, the system control function is executed by the processing circuit 15, and the processing circuit 15 functions as a substitute for the system control circuit 123. The processor that realizes the system control circuit 123 is similar to that described above, and therefore a description thereof will be omitted.

[0031] The memory 125 stores various programs related to the system control function executed in the system control circuit 123, various imaging protocols, imaging conditions including a plurality of imaging parameters that define the imaging protocols, etc. The memory 125 also stores the specific function 33, the setting function 35, and the generating function 37 realized by the processing circuit 15 in the form of a program executable by a computer.

[0032] The memory 125 also stores MR images generated by the generating function 37 and prescan images generated by a prescan such as a locator scan. The prescan images are, for example, positioning images (also called locator images) for setting an imaging field of view (hereinafter called FOV (Field of view)) in a main scan, and coil sensitivity maps used for reconstructing MR images in a main scan. That is, the memory 125 stores a plurality of coil sensitivity maps respectively corresponding to a plurality of coil elements. The memory 125 also stores the FOV set in the locator image, which is a prescan image.

[0033] The memory 125 stores the sampling frequency (or sampling rate, sampling interval) used in the A / D converter 193 for the main scan executed after the prescan. The memory 125 also stores the cutoff frequency used in the low-pass filter 191 for the main scan. The memory 125 stores MR data related to the main scan and an algorithm for reconstructing an MR image based on the MR data.

[0034] The memory 125 may store various data received via a communication interface (not shown). For example, the memory 125 stores information on the examination order of the subject P (such as a region to be imaged, a purpose of the examination, etc.) received from an information processing system in the medical institution, such as a Radiology Information System (RIS).

[0035] The memory 125 is realized by, for example, a semiconductor memory element such as a ROM, a RAM, or a flash memory, a hard disk drive (HDD), a solid state drive (SSD), an optical disk, etc. The memory 125 may also be realized by a drive device that reads and writes various information between the memory 125 and a portable storage medium such as a compact disc (CD)-ROM drive, a digital versatile disc (DVD) drive, or a flash memory.

[0036] The input interface 127 accepts various instructions (e.g., a power-on instruction) and information input from an operator. The input interface 127 is realized by, for example, a trackball, a switch button, a mouse, a keyboard, a touch pad that performs an input operation by touching an operation surface, a touch screen in which a display screen and a touch pad are integrated, a non-contact input circuit using an optical sensor, and a voice input circuit. The input interface 127 is connected to a processing circuit 131, and converts an input operation received from an operator into an electric signal and outputs it to the processing circuit 131. Note that, in this specification, the input interface 127 is not limited to only those having physical operation parts such as a mouse and a keyboard. For example, an electric signal processing circuit that receives an electric signal corresponding to an input operation from an external input device provided separately from the MRI apparatus 100 and outputs the electric signal to a control circuit is also included as an example of the input interface 127.

[0037] The input interface 127 inputs an FOV in response to a user instruction for a pre-scan image displayed on the display 129. Specifically, the input interface 127 inputs an FOV in response to a user instruction to set a range in a locator image displayed on the display 129. In addition, the input interface 127 inputs various imaging parameters related to the main scan in response to a user instruction based on an examination order.

[0038] The display 129 displays various GUIs (Graphical User Interfaces), MR images generated by the processing circuitry 131, prescan images such as locator images, etc., under the control of the processing circuitry 131 or the system control circuitry 123. The display 129 also displays various information related to imaging parameters related to the main scan and prescan, and image processing, etc. The display 129 is realized by, for example, a display device such as a CRT display, a liquid crystal display, an organic EL display, an LED display, a plasma display, or any other display or monitor known in the art.

[0039] The processing circuit 131 is realized by, for example, the above-mentioned processor. The processing circuit 131 includes the identifying function 33, the setting function 35, and the generating function 37. The processing circuit 131 that realizes the identifying function 33, the setting function 35, and the generating function 37 corresponds to the identifying unit, the setting unit, and the generating unit, respectively. Each function such as the identifying function 33, the setting function 35, and the generating function 37 is stored in the memory 125 in the form of a program executable by a computer. For example, the processing circuit 131 realizes a function corresponding to each program by reading and executing the program from the memory 125. In other words, the processing circuit 131 in a state in which each program is read has each function such as the identifying function 33, the setting function 35, and the generating function 37.

[0040] In the above description, an example in which the "processor" reads out and executes a program corresponding to each function from the memory 125 has been described, but the embodiment is not limited to this. When the processor is, for example, a CPU, the processor realizes the function by reading out and executing a program stored in the memory 125. On the other hand, when the processor is an ASIC, instead of storing a program in the memory 125, the function is directly incorporated as a logic circuit in the circuit of the processor. Note that each processor in this embodiment is not limited to being configured as a single circuit for each processor, but may be configured as one processor by combining multiple independent circuits to realize the function. Also, although a single storage circuit has been described as storing a program corresponding to each processing function, multiple storage circuits may be distributed and arranged, and the processing circuit 131 may read out the corresponding program from each storage circuit.

[0041] The processing circuitry 131 uses the identification function 33 to identify a signal region related to the generation of MR signals in the subject P. The signal region corresponds to a region in the imaging space where protons such as water molecules exist. The identification function 33 identifies, as the signal region, a region in the pre-scan image where the subject P is imaged (hereinafter referred to as the imaging region). Specifically, the identification function 33 identifies the imaging region corresponding to the region of the subject P by detecting the image of the subject P in the pre-scan image or by user designation on the pre-scan image.

[0042] For example, the identification function 33 identifies the signal region by applying an area detection process for detecting an imaging area to the prescan image. The area detection process can appropriately use existing image recognition processes such as edge detection in the prescan image, and therefore a description thereof will be omitted. Note that the identification function 33 may identify the signal region in the prescan image displayed on the display 129 according to an area identification instruction input by the user via the input interface 127. The area identification instruction is, for example, an instruction to input a figure (e.g., a rectangle such as a rectangle or an ellipse) for specifying a range in the prescan image.

[0043] The processing circuitry 131 sets a cutoff frequency for the passband of the MR signal based on the signal region identified by the setting function 35. Specifically, the setting function 35 sets the cutoff frequency by further using the FOV in the main scan, which is a scan of the subject P in a plurality of readout directions, and the strength of the gradient magnetic field in the main scan. The setting function 35 may also set the cutoff frequency so as to include a signal region related to the generation of the MR signal. The setting function 35 may also set the cutoff frequency for each readout direction based on the identified signal region. The processing content of the setting of the cutoff frequency by the setting function 35 will be described in detail in the processing of imaging the subject P by the main scan and generating an MR image (hereinafter referred to as image generation processing).

[0044] The processing circuitry 131 acquires MR data generated by a prescan on the subject P (hereinafter referred to as prescan data) from the receiving circuitry 119 using the generating function 37, arranges the data in k-space, and generates a prescan image based on the prescan data arranged in the k-space. The generating function 37 stores the generated prescan image in the memory 125.

[0045] For example, the generating function 37 acquires MR data generated by a scan related to the generation of a locator image from the receiving circuitry 119, arranges it in k-space, and generates (reconstructs) the locator image based on the MR data arranged in the k-space. The generating function 37 also acquires coil sensitivity data generated by a scan related to the generation of a coil sensitivity map from the receiving circuitry 119, arranges it in k-space, and generates (reconstructs) the coil sensitivity map based on the coil sensitivity data arranged in the k-space. Since the generation of the locator image, the coil sensitivity map, etc. can be performed using an existing reconstruction method, a description thereof will be omitted.

[0046] The processing circuitry 131 generates an MR image (hereinafter referred to as a main scan image) based on MR data generated by A / D conversion of the MR signal output from the low-pass filter 191 in the main scan using the generation function 37. For example, the generation function 37 generates the main scan image by sensitivity encoding (hereinafter referred to as SENSE (SENSitivity Encoding)) using the MR data generated by the main scan and a coil sensitivity map. Note that the generation of the main scan image is not limited to SENSE, and for example, a reconstruction method related to compressed sensing (CS) or super-resolution may be used. The generation function 37 stores the main scan image in the memory 125. The processing content related to the generation of the main scan image will be described in detail in the image generation processing.

[0047] The image generating process executed by the MRI apparatus 100 of this embodiment configured as above will be described with reference to Fig. 4 to Fig. 9. Fig. 4 is a flow chart showing an example of the procedure of the image generating process.

[0048] (Image generation processing) (Step S401) The imaging control circuitry 121 executes a prescan on the subject P. The processing circuitry 131 generates a prescan image based on the prescan data using the generation function 37. The generation function 37 stores the generated prescan image, for example, a locator image and a coil sensitivity map, in the memory 125. The system control circuitry 123 displays the locator image on the display 129.

[0049] Input interface 127 inputs an FOV (hereinafter referred to as user FOV) in the locator image in response to a user instruction. The user FOV input by the user is stored in memory 125. Setting function 35 sets a sampling frequency according to the user FOV, and outputs the set sampling frequency to A / D converter 193. For example, setting function 35 sets a sampling frequency corresponding to oversampling, in other words, a sampling interval, by multiplying the reciprocal of the size of the user FOV by a constant.

[0050] (Step S402) Processing circuitry 131 executes area detection processing on the locator image using identification function 33, and identifies a signal area in the locator image. Note that identification of a signal area in the locator image is not limited to area detection processing. The signal area may be identified by, for example, a user instruction via input interface 127.

[0051] At this time, system control circuit 123 causes display 129 to display the prescan image. That is, display 129 displays the locator image under the control of system control circuit 123. Input interface 127 inputs an input instruction for identifying a signal region for the displayed locator image by a user's operation. As a result, processing circuit 131 identifies the signal region using identification function 33.

[0052] 5 is a diagram showing an example of a signal area SA in a locator image LI. When a signal area SA is specified via input interface 127, a figure for specifying a range in locator image LI (for example, a rectangle such as a rectangle or an ellipse) is input by a user instruction.

[0053] (Step S403) The processing circuitry 131 sets the cutoff frequency of the low-pass filter 191 to be applied to the MR signals received by the main scan by the setting function 35. Specifically, the setting function 35 sets a provisional cutoff frequency (hereinafter referred to as provisional cutoff frequency) based on the strength of the gradient magnetic field in the main scan and the user FOV. For example, the setting function 35 sets the provisional cutoff frequency by using the band of the low-pass filter 191 in the following formula: User FOV [cm] = (2 × low-pass filter bandwidth [Hz]) / readout gradient magnetic field strength [Hz / cm] In the above equation, the readout gradient magnetic field strength corresponds to the strength of the gradient magnetic field in the main scan.

[0054] Next, the setting function 35 converts the tentative cutoff frequency into image space and compares it with the identified signal region. Hereinafter, the tentative cutoff frequency converted into image space is referred to as the tentative cutoff position. The setting function 35 identifies the position (hereinafter, referred to as the furthest position) farthest from the tentative cutoff position among the signal regions that are outside the passband of the low-pass filter 191 defined by the tentative cutoff position in each of a plurality of readout directions in the main scan. The setting function 35 sets the frequency corresponding to the furthest position (hereinafter, referred to as the furthest frequency) as the cutoff frequency. The setting function 35 may set the frequency obtained by adding a predetermined margin frequency to the furthest frequency as the cutoff frequency.

[0055] That is, the setting function 35 sets the cutoff frequency so as to include a signal region related to the generation of the MR signal. For example, the setting function 35 sets the cutoff frequency for each readout direction so as to include a signal region related to the generation of the MR signal. Setting the cutoff frequency corresponds to, for example, expanding the passband of the MR signal by the temporary cutoff frequency. Note that the setting of the cutoff frequency so as to include a signal region related to the generation of the MR signal may be set by a user's instruction via the input interface 127. As a result, the signal amount of each of the multiple MR signals received by the main scan becomes constant regardless of the multiple readout directions in the main scan. In other words, the setting function 35 sets the cutoff frequency so that the signal amount of each of the multiple MR signals becomes constant regardless of the multiple readout directions. The setting function 35 outputs the set cutoff frequency to the low-pass filter 191.

[0056] (Step S404) The imaging control circuit 121 executes radial acquisition as a main scan for the subject P. Specifically, the imaging control circuit 121 executes imaging along one readout direction in the main scan. As a result, the receiving coil 117 receives an MR signal in the readout direction. The MR signal received by the receiving coil 117 is output to the receiving circuit 119. At this time, the MR signal is detected by a detector.

[0057] (Step S405) The low-pass filter 191 filters the detected MR signal using a set cutoff frequency. The filtering of the MR signal by the low-pass filter 191 reduces unnecessary signals outside the user FOV. This improves the S / N ratio of the MR signal, etc. The filtered MR signal is output to the A / D converter 193.

[0058] (Step S406) The A / D converter 193 samples the MR signal output from the low-pass filter 191 using the set sampling frequency. As a result, the A / D converter 193 generates MR data. That is, the A / D converter 193 performs A / D conversion on the MR signal that has passed through the low-pass filter 191 at the sampling frequency to generate MR data. The MR data is stored in the memory 125 via the imaging control circuit 121.

[0059] (Step S407) If the acquisition of MR signals has been completed for all readout directions (i.e., all trajectories kTra in the readout directions) preset in the main scan (Yes in step S407), the process of step S408 is executed. If the acquisition of MR signals has not been completed for all readout directions in the main scan (No in step S408), the processes of steps S404 to S406 are repeated.

[0060] FIG. 6 is a diagram showing the readout direction ROD and sampling points SP in the k-space ks, and the signal area SA, various FOVs, reconstruction area RR, stop band SB, and cutoff position CP corresponding to the cutoff frequency in the image space IS. As shown in FIG. 6, the readout direction ROD passes through the center of the k-space ks and is parallel to the kx direction. Furthermore, UF in the image space IS indicates the user FOV set via the input interface 127. Furthermore, SF in the image space IS indicates the FOV of sampling defined by oversampling, that is, adjacent point sampling SP. As shown in FIG. 6, the cutoff position CP corresponding to the cutoff frequency is located outside SF, which is the FOV of sampling. That is, the passband PB of the MR signal in the low-pass filter 191 is expanded compared to SF, which is the FOV of sampling.

[0061] Fig. 7 is a diagram showing the readout direction ROD and sampling points SP in the k-space ks, and the signal area SA, various FOVs, reconstruction area RR, stop band SB, and cutoff position CP corresponding to the cutoff frequency in the image space IS. The difference between Fig. 6 and Fig. 7 is that the readout direction ROD in Fig. 7 passes through the center of the k-space ks and is parallel to the ky direction. As shown in Fig. 7, the cutoff position CP corresponding to the cutoff frequency is located outside the sampling FOV SF. That is, the passband PB of the MR signal in the low-pass filter 191 is expanded compared to the sampling FOV SF.

[0062] FIG. 8 is a diagram showing the readout direction ROD and sampling points SP in the k-space ks, and the signal area SA, various FOVs, the reconstruction area RR, the stop band SB, and the cutoff position CP corresponding to the cutoff frequency in the image space IS. The difference between FIG. 6 and FIG. 7 and FIG. 8 is that the readout direction ROD in FIG. 8 passes through the center of the k-space ks and is inclined at 45° with respect to the kx direction or the ky direction. As shown in FIG. 8, the cutoff position CP corresponding to the cutoff frequency is located outside the sampling FOV SF. That is, the passband PB of the MR signal in the low-pass filter 191 is expanded compared to the sampling FOV SF. As shown in FIG. 8, the signal area SA is included in the passband PB. As shown in FIG. 8, the low -Pa Since the passband PB of the filter is larger than the signal area SA, the total amount of MR signals in each of all readout directions in the main scan is constant.

[0063] (Step S408) The processing circuitry 131 generates an actual scan image based on the MR data using the generation function 37. For example, the generation function 37 generates the actual scan image using SENSE as shown in the following equation.

[0064]

number

[0065] In the above formula, x is the data of the image space in the expanded FOV, i.e., the FOV by oversampling (the original scanned image), F k is the Fourier transform for the kth readout direction, y k is the MR data in the kth readout direction, S is the coil sensitivity matrix corresponding to all the coil sensitivity maps, and R(x) is the regularization term for the actual scan image x. If no coil sensitivity maps are used, S in the above formula is omitted, and formulas corresponding to various assumptions regarding the actual scan image are incorporated into the regularization term R(x). The generation function 37 generates the actual scan image by determining x to satisfy formula (1).

[0066] The reconstruction of the main scan image by the generating function 37 is not limited to the above-mentioned SENSE, and may be, for example, a reconstruction method related to compressed sensing (CS) or super-resolution. When the main scan is a propeller acquisition PRP or another method such as acquisition BL2 using two blades, the generating function 37 can also generate the main scan image by a reconstruction method using GRAPPA (Generalized Auto calibrating Partially Parallel Acquisition).

[0067] Furthermore, the generating function 37 may generate the main scan image using frame correlation for use in moving image reconstruction in addition to the coil sensitivity maps, as shown in the following equation:

number

[0068] According to the first embodiment described above, in the MRI apparatus 100 that acquires a plurality of MR signals corresponding to a plurality of readout directions including a first readout direction and a second readout direction intersecting the first readout direction, a signal region SA related to the generation of a plurality of MR signals is identified in a pre-scan image (locator image LI) of the subject P, a cutoff frequency related to a passband PB of the MR signals is set based on the identified signal region SA, the plurality of MR signals acquired by scanning (main scan) the subject P in the plurality of readout directions is filtered using the set cutoff frequency, and an MR image (main scan image) is generated based on MR data generated by A / D conversion of the MR signals output from the low-pass filter 191.

[0069] Furthermore, according to the MRI apparatus 100, the signal region SA is identified by detecting an image of the subject P in the pre-scan image (locator image LI) or by user specification of the pre-scan image (locator image LI), and the cutoff frequency is set further using the imaging field of view FOV in the main scan and the strength of the gradient magnetic field in the main scan.

[0070] From these facts, the MRI apparatus 100 according to the first embodiment can set the cutoff frequency so as to include the signal area SA related to the generation of the MR signal. At this time, the MRI apparatus 100 can set the cutoff frequency for each readout direction. As a result, the MRI apparatus 100 can set the cutoff frequency so that the signal amount of each of the multiple MR signals corresponding to the multiple readout directions is constant regardless of the multiple readout directions.

[0071] From the above, according to the MRI apparatus 100 of the first embodiment, even in a scan in which the readout direction changes, as shown in Fig. 6 to Fig. 8, the MR signal generated in the signal region SA is not filtered by the low-pass filter 191, that is, the MR signal is not blocked (suppressed) depending on the readout direction, so that it is possible to acquire data that is consistent in the k-space. As a result, according to the present MRI apparatus 100, it is possible to obtain high-quality images with few streaks.

[0072] 9 is a diagram showing an example of an MR image (1) in a comparative example in which the cutoff frequency of the low-pass filter is a tentative cutoff frequency, and an MR image (2) generated by the image generation process in this embodiment. As shown in FIG. 9, the MR image (2) generated by the image generation process has reduced streak artifacts and has improved image quality compared to the MR image (1) in which the cutoff frequency is the tentative cutoff frequency. Therefore, according to the MRI apparatus 100 of this embodiment, an MR image with improved image quality can be generated for the main scan.

[0073] Second embodiment Fig. 10 is a diagram showing an example of an MRI apparatus 200 according to the second embodiment. The MRI apparatus 200 according to the second embodiment does not have a specific function 33, unlike the MRI apparatus 100 according to the first embodiment shown in Fig. 1. Hereinafter, the image generation process according to this embodiment will be described with respect to the processes of steps S403 and S405 which are different from those of the first embodiment.

[0074] (Image generation processing) (Step S403) The processing circuitry 131 sets cutoff frequencies for the passbands PB of the MR signals corresponding to the plurality of readout directions for each readout direction based on the user FOV for the main scan of the subject P in the plurality of readout directions by the setting function 35. That is, in the first embodiment, the cutoff frequencies in all readout directions in the main scan are constant, but in the present embodiment, the cutoff frequencies are set for each readout direction.

[0075] For example, the setting function 35 sets the cutoff frequency according to the angle θ (radian) of the readout direction with respect to the kx direction. The set cutoff frequency is output to the low-pass filter 191 in correspondence with the readout direction. Specifically, when 0≦θ≦π / 4, 3π / 4≦θ≦5π / 4, and 7π / 4≦θ≦2π, the setting function 35 sets the value obtained by multiplying the provisional cutoff frequency by 1 / |cosθ| as the cutoff frequency. When π / 4≦θ≦3π / 4 and 5π / 4≦θ≦7π / 4, the setting function 35 sets the value obtained by multiplying the provisional cutoff frequency by 1 / |sinθ| as the cutoff frequency. When the cutoff frequency is set in this manner, FIG. 6 becomes as shown in FIG. 11 when θ=0 and θ=π, and FIG. 7 becomes as shown in FIG. 12 when θ=π / 2 and θ=3π / 2. Moreover, when θ=π / 4 and θ=5π / 4, FIG. 8 also applies to this embodiment.

[0076] (Step S405) The low-pass filter 191 receives a cutoff frequency associated with the readout direction in the radial acquisition executed in step S404. The low-pass filter 191 filters the detected MR signal (for example, a difference signal between the received MR signal and the carrier frequency) using the cutoff frequency associated with the readout direction. The filtered MR signal is output to the A / D converter 193.

[0077] FIG. 11 is a diagram showing the readout direction ROD and sampling points SP in the k-space ks, and the signal area SA, various FOVs, reconstruction area RR, stop band SB, and cutoff position CP corresponding to the cutoff frequency in the image space IS. As shown in FIG. 11, the readout direction ROD passes through the center of the k-space ks and is parallel to the kx direction. Also, UF in the image space IS indicates the user FOV set via the input interface 127. Also, SF in the image space IS indicates the FOV of oversampling, that is, sampling defined by adjacent sampling points SP. As shown in FIG. 11, the cutoff position CP corresponding to the cutoff frequency is at the same position as the end of SF, which is the FOV of sampling. That is, the passband PB of the MR signal in the low-pass filter 191 is the same as SF, which is the FOV of sampling.

[0078] Fig. 12 is a diagram showing the readout direction ROD and sampling points SP in the k-space ks, and the signal area SA, various FOVs, reconstruction area RR, stop band SB, and cutoff position CP corresponding to the cutoff frequency in the image space IS. The difference between Fig. 11 and Fig. 12 is that the readout direction ROD in Fig. 7 passes through the center of the k-space ks and is parallel to ky. As shown in Fig. 12, the cutoff position CP corresponding to the cutoff frequency is at the same position as the end of SF, which is the sampling FOV. That is, the passband PB of the MR signal in the low-pass filter 191 is the same as SF, which is the sampling FOV.

[0079] As a modification of the second embodiment, when the technical idea of ​​the second embodiment is applied to the first embodiment, the MRI apparatus 100 has a specification function 33 as shown in FIG. 1. At this time, the processing circuitry 131 specifies the furthest position in each of the multiple readout directions by the specification function 33. Next, the processing circuitry 131 may set the furthest frequency corresponding to the furthest position or the furthest frequency plus a frequency of a predetermined margin as the cutoff frequency by the setting function 35 in each of the multiple readout directions. At this time, the cutoff frequency may be higher or lower than the tentative cutoff frequency as shown in FIG. 8.

[0080] According to the second embodiment described above, in the MRI apparatus 200 that acquires a plurality of MR signals corresponding to a plurality of readout directions including a first readout direction and a second readout direction intersecting the first readout direction, a cutoff frequency for the passband PB of the MR signals is set for each readout direction based on a user FOV for the main scan of the subject P in the plurality of readout directions, and the plurality of MR signals acquired by the main scan in the plurality of readout directions are filtered using the cutoff frequency set for each readout direction, and an MR image is generated based on MR data generated by A / D conversion of the MR signals output from the low-pass filter 191.

[0081] Thus, according to the MRI apparatus 200 of the present embodiment, a cut-off frequency including a signal area SA related to the generation of MR signals, that is, a cut-off frequency that makes the signal amount of each of the multiple MR signals corresponding to the multiple read-out directions constant regardless of the multiple read-out directions, can be set for each read-out direction. The effects of the present embodiment are the same as those of the first embodiment, so the description will be omitted.

[0082] (Third embodiment) The configuration of the MRI apparatus according to the third embodiment is similar to that of the MRI apparatus 200 as the second embodiment. Hereinafter, the image generating process in this embodiment will be described with respect to the process of step S403 that is different from the first embodiment.

[0083] (Image generation processing) (Step S403) The processing circuitry 131 sets a cutoff frequency for the passband PB of the magnetic resonance signals corresponding to the multiple readout directions by multiplying a constant by a frequency (tentative cutoff frequency) determined based on the user FOV for the main scan of the subject P in the multiple readout directions and the strength of the gradient magnetic field in the main scan, using the setting function 35. For example, the setting function 35 sets the constant according to the sequence of the main scan.

[0084] Specifically, when the sequence of the main scan is performed as shown in FIG. 3, such as two-dimensional radial acquisition R2D, three-dimensional radial acquisition (stack-of-stars Sos), propeller acquisition PRP, or other acquisition by, for example, two blades BL2, the setting function 35 is set to a constant value of 2 1 / 2 (For example, when the number of significant digits is 3, 1.41) is set. In this case, the setting function 35 sets the cutoff frequency by multiplying the provisional cutoff frequency by 1.41. Also, when the sequence of the main scan is executed for three-dimensional imaging of a cush ball KB, as shown in FIG. 3, the setting function 35 sets the constant, 1 / 2 (For example, when the number of significant digits is 3, 1.73 is set.) At this time, the setting function 35 sets the cutoff frequency by multiplying the provisional cutoff frequency by 1.73.

[0085] According to the MRI apparatus 200 of the third embodiment described above, a cutoff frequency for the passband PB of MR signals is set by multiplying a tentative cutoff frequency determined based on the user FOV for the main scan of the subject P in multiple readout directions and the strength of the gradient magnetic field in the main scan by a constant, and the MR signals acquired by the main scan in multiple readout directions are filtered using the set cutoff frequency, and a magnetic resonance image is generated based on MR data generated by A / D conversion of the MR signals output from the low-pass filter 191. Moreover, according to the MRI apparatus 200 of the third embodiment, a constant is set according to the sequence of the main scan.

[0086] As a result, the cutoff frequency can be easily set according to the sequence of the main scan according to the MRI apparatus 200 of this embodiment. The effects of this embodiment are similar to those of the first embodiment, and therefore a description thereof will be omitted.

[0087] When the technical idea of ​​the first embodiment is realized by an image generating method, the image generating method specifies a signal region SA related to the generation of multiple MR signals in a prescan image (locator image LI) of the subject P for multiple readout directions including a first readout direction and a second readout direction intersecting the first readout direction, sets a cutoff frequency related to a passband PB of the MR signals based on the specified signal region SA, filters multiple MR signals acquired by main scans of the subject P in multiple readout directions by a low-pass filter 191 using the set cutoff frequency, generates MR data by A / D conversion of the MR signals output from the low-pass filter 191, and generates an MR image based on the generated MR data. The procedure and effects of the image generating process of this image generating method are similar to those described in the first embodiment, and therefore will not be described again.

[0088] According to at least one of the embodiments etc. described above, it is possible to generate a magnetic resonance image with improved image quality. That is, according to at least one of the embodiments etc., it is possible to acquire data that is consistent in k-space even in a scan in which the readout direction changes, and it is possible to obtain a high-image-quality MR image with few streaks.

[0089] Although some embodiments have been described, these embodiments are presented as examples and are not intended to limit the scope of the invention. These embodiments can be implemented in various other forms, and various omissions, substitutions, modifications, and combinations of embodiments can be made without departing from the spirit of the invention. These embodiments and their modifications are included in the scope of the invention and its equivalents as described in the claims, as well as in the scope and spirit of the invention. [Explanation of symbols]

[0090] 33 Specific Functions 35 Setting Function 37 Generation function 100 Magnetic resonance imaging device 101 Static magnetic field magnet 103 Gradient magnetic field coil 105 Gradient magnetic field power supply 107 Bed 109 Bed Control Circuit 111 Boa 113 Transmitting circuit 115 Transmitting Coil 117 Receiving coil 119 Receiving circuit 121 Imaging control circuit 123 System Control Circuit 125 Memory 127 Input Interface 129 Display 131 Processing circuit 191 Low-pass filter 193 A / D Converter 200 MRI machine

Claims

1. 1. A magnetic resonance imaging apparatus for radially acquiring a plurality of magnetic resonance signals corresponding to a plurality of readout directions including a first readout direction and a second readout direction intersecting the first readout direction, comprising: An identification unit that identifies a signal region related to generation of a magnetic resonance signal in a subject; A setting unit that sets a cutoff frequency for a passband of the magnetic resonance signal so as to be different for each readout direction so as to include the signal region; a low-pass filter that filters the plurality of magnetic resonance signals acquired by scanning the subject in the plurality of readout directions using the cutoff frequency; a generating unit that generates a magnetic resonance image based on magnetic resonance data generated by A / D conversion of the magnetic resonance signal output from the low-pass filter; A magnetic resonance imaging apparatus comprising:

2. The setting unit sets the cutoff frequency by further using an imaging field of view in the scan and a strength of a gradient magnetic field in the scan.

2. A magnetic resonance imaging apparatus according to claim 1.

3. The identification unit identifies the signal region by detecting an image of the subject or by a user's designation.

3. A magnetic resonance imaging apparatus according to claim 1.

4. The setting unit is setting a tentative cutoff frequency based on an imaging field of view in the scan and a strength of a gradient magnetic field in the scan; A tentative cutoff position obtained by transforming the tentative cutoff frequency into an image space is compared with the specified signal region; setting the cutoff frequency based on a signal region that is outside the passband defined by the temporary cutoff position among the identified signal regions; 4. A magnetic resonance imaging apparatus according to claim 1.

5. 1. A magnetic resonance imaging apparatus for radially acquiring a plurality of magnetic resonance signals corresponding to a plurality of readout directions including a first readout direction and a second readout direction intersecting the first readout direction, comprising: a setting unit that sets a cutoff frequency related to a passband of the magnetic resonance signal so as to be different for each readout direction so as to include an imaging field of view related to scanning of the subject in the plurality of readout directions; a low-pass filter that filters the magnetic resonance signals acquired by the scan in the readout directions using the cutoff frequency; a generating unit that generates a magnetic resonance image based on magnetic resonance data generated by A / D conversion of the magnetic resonance signal output from the low-pass filter; A magnetic resonance imaging apparatus comprising:

6. 1. A magnetic resonance imaging apparatus for radially acquiring a plurality of magnetic resonance signals corresponding to a plurality of readout directions including a first readout direction and a second readout direction intersecting the first readout direction, comprising: a setting unit that sets a cutoff frequency for a passband of the magnetic resonance signal so as to be different for each readout direction, by multiplying a frequency determined based on an imaging field of view for the scan of the subject in the plurality of readout directions and the strength of a gradient magnetic field in the scan by a constant, so as to include a signal region related to the generation of the magnetic resonance signal in the subject; a low-pass filter that filters the magnetic resonance signals acquired by the scan in the plurality of readout directions using the cutoff frequency; a generating unit that generates a magnetic resonance image based on magnetic resonance data generated by A / D conversion of the magnetic resonance signal output from the low-pass filter; A magnetic resonance imaging apparatus comprising:

7. the setting unit sets the constant in accordance with the sequence of the scan.

7. A magnetic resonance imaging apparatus according to claim 6.

8. the setting unit sets the cutoff frequency so that a signal amount of each of the plurality of magnetic resonance signals is constant regardless of the plurality of readout directions.

8. A magnetic resonance imaging apparatus according to claim 1.

9. The setting unit sets the cutoff frequency so as to include a signal region related to generation of the magnetic resonance signal.

9. A magnetic resonance imaging apparatus according to any one of the preceding claims.

10. Identifying a signal region related to generation of a magnetic resonance signal in the subject with respect to a plurality of readout directions in radial acquisition including a first readout direction and a second readout direction intersecting the first readout direction; A cutoff frequency for a passband of a magnetic resonance signal is set to be different for each readout direction so as to include the signal region; filtering magnetic resonance signals acquired by scanning the subject in the plurality of readout directions with a low-pass filter using the cutoff frequency; generating magnetic resonance data by A / D conversion of the magnetic resonance signal output from the low-pass filter; generating a magnetic resonance image based on the magnetic resonance data; An image generating method comprising:

Images