Magnetic resonance imaging apparatus and method thereof

A magnetic resonance imaging (MRI) apparatus for obtaining a magnetic resonance (MR) image, based on a multi-echo sequence, and a method of the MRI apparatus are provided. The MRI apparatus includes a data obtainer configured to obtain first echo data, based on an echo that is generated at a first echo time, and obtain second echo data, based on an echo that is generated at a second echo time later than the first echo time, the first echo data including a part overlapping a part included in the second echo data in a k-space. The MRI apparatus further includes an image processor configured to reconstruct the MR image, based on the first echo data and the second echo data.

CROSS-REFERENCE TO RELATED APPLICATION

This application claims priority from Korean Patent Application No. 10-2016-0018549, filed on Feb. 17, 2016, in the Korean Intellectual Property Office, the disclosure of which is incorporated herein by reference in its entirety.

BACKGROUND

Apparatuses and methods consistent with exemplary embodiments relate to magnetic resonance imaging (MRI) apparatuses and methods thereof, and more particularly, to MRI apparatuses for obtaining magnetic resonance (MR) images by using multi-echo sequences and methods of the MRI apparatuses.

2. Description of the Related Art

Magnetic resonance imaging (MRI) apparatuses for imaging subjects by using magnetic fields may show stereoscopic images of bones, lumbar discs, joints, nerve ligaments, hearts, etc. at desired angles.

An MRI apparatus is advantageous in that the MRI apparatus is noninvasive, exhibits an excellent tissue contrast as compared to a computerized tomography (CT) apparatus, and does not have artifacts due to bone tissue. Also, because the MRI apparatus may capture various cross-sectional images in desired directions without moving an object, the MRI apparatus is widely used with other imaging apparatuses.

An MRI apparatus may obtain k-space data by using a multi-echo sequence. In detail, when a multi-echo sequence is used, a time taken to capture an image may be reduced by exciting one radio frequency (RF) pulse and then obtaining an MR signal by using a plurality of generated echoes.

When an MRI apparatus uses a multi-echo sequence, the MRI apparatus may use a method of obtaining a plurality of pieces of k-space data respectively corresponding to a plurality of echo times by applying a gradient magnetic field for phase encoding only once during one repetition time (TR).

Alternatively, the MRI apparatus may use a method of obtaining one piece of k-space data by using a plurality of echoes that are generated during one TR. This method is referred to as an echo-planar imaging (EPI) method.

A multi-echo sequence may be based on gradient echoes or spin echoes. If a multi-echo sequence is based on gradient echoes, because a sign of a readout gradient magnetic field has to be continuously reversed, an MRI apparatus may have high performance to generate a gradient magnetic field. As the performance of an MRI apparatus has recently been improved, not only a TR may be reduced when gradient echoes are used but also an image having a desired contrast ratio may be obtained.

SUMMARY

Exemplary embodiments may improve the quality of a reconstructed final image by obtaining additional data about an overlapping part between first echo data and second echo data, which are obtained at different echo times, in a k-space to obtain a magnetic resonance (MR) image.

Exemplary embodiments may reduce the effects of blur or aliasing that may occur in a final image as pieces of data obtained at different echo times are used by performing phase correction on first echo data and second echo data obtained at different echo times.

According to an aspect of an exemplary embodiment, there is provided a magnetic resonance imaging (MRI) apparatus for obtaining a magnetic resonance (MR) image, based on a multi-echo sequence, the MRI apparatus including a data obtainer configured to obtain first echo data, based on an echo that is generated at a first echo time, and obtain second echo data, based on an echo that is generated at a second echo time later than the first echo time, the first echo data including a part overlapping a part included in the second echo data in a k-space. The MRI apparatus further includes an image processor configured to reconstruct the MR image, based on the first echo data and the second echo data.

The image processor may be further configured to perform phase correction on either one or both of the first echo data and the second echo data, and reconstruct the MR image, based on either one or both of the first echo data and the second echo data on which the phase correction is performed.

Either one or each of the first echo data and the second echo data may include data of a central part of the k-space.

The image processor may be further configured to perform phase correction, based on a phase of the data of the central part of the k-space among the first echo data and the second echo data.

The MRI apparatus may further include a gradient magnetic field controller configured to control a gradient magnetic field that is applied, based on the multi-echo sequence, and a sign of a readout gradient magnetic field that is applied at the first echo time may be the same as a sign of a readout gradient magnetic field that is applied at the second echo time.

The data obtainer may be further configured to, in response to the first echo data including data of a central part of the k-space and the second echo data not including the data of the central part of the k-space, obtain additional data of the overlapping part included in the first echo data, based on the echo generated at the first echo time.

The data obtainer may be further configured to, in response to the second echo data including data of a central part of the k-space and the first echo data not including the data of the central part of the k-space, obtain additional data of the overlapping part included in the second echo data, based on the echo generated at the second echo time.

The data obtainer may be further configured to determine characteristics of the MR image to be obtained, and determine that the first echo data or the second echo data is to include data of a central part of the k-space, based on the determined characteristics of the MR image.

The image processor may be further configured to generate a B0 map, based on third echo data and fourth echo data that are obtained based on an echo that is generated at a third echo time and an echo that is generated at a fourth echo time, respectively, and perform phase correction on either one or both of the first echo data and the second echo data, based on the generated B0 map.

The MRI apparatus may further include a gradient magnetic field controller configured to control a gradient magnetic field that is applied, based on the multi-echo sequence, and a sign of a readout gradient magnetic field that is applied at the third echo time may be the same as a sign of a readout gradient magnetic field that is applied at the fourth echo time.

The first echo time, the second echo time, the third echo time, and the fourth echo time may be included in a repetition time period.

The image processor may be further configured to reconstruct k-space data, based on another part of the first echo data other than the overlapping part included in the first echo data in the k-space, and the second echo data, perform phase correction on the second echo data included in the reconstructed k-space data, and re-reconstruct the k-space data, based on the overlapping part included in the first echo data, and the second echo data on which the phase correction is performed.

According to an aspect of another exemplary embodiment, there is provided a method of a magnetic resonance imaging (MRI) apparatus for obtaining a magnetic resonance (MR) image, based on a multi-echo sequence, the method including obtaining first echo data, based on an echo that is generated at a first echo time, and obtaining second echo data, based on an echo that is generated at a second echo time later than the first echo time, the first echo data including a part overlapping a part included in the second echo data in a k-space. The method further includes reconstructing the MR image, based on the first echo data and the second echo data.

The method may further include performing phase correction on either one or both of the first echo data and the second echo data, and the reconstructing may include reconstructing the MR image, based on either one or both of the first echo data and the second echo data on which the phase correction is performed.

Either one or each of the first echo data and the second echo data may include data of a central part of the k-space.

The performing may include performing the phase correction, based on a phase of the data of the central part of the k-space among the first echo data and the second echo data.

The method may further include controlling a gradient magnetic field that is applied, based on the multi-echo sequence, and a sign of a readout gradient magnetic field that is applied at the first echo time may be the same as a sign of a readout gradient magnetic field that is applied at the second echo time.

The method may further include, in response to the first echo data including data of a central part of the k-space and the second echo data not including the data of the central part of the k-space, obtaining additional data of the overlapping part included in the first echo data, based on the echo generated at the first echo time.

The method may further include, in response to the second echo data including data of a central part of the k-space and the first echo data not including the data of the central part of the k-space, obtaining additional data of the overlapping part included in the second echo data, based on the echo generated at the second echo time.

The method may further include determining characteristics of the MR image to be obtained, and determining that the first echo data or the second echo data is to include data of a central part of the k-space, based on the determined characteristics of the MR image.

The method may further include generating a B0 map, based on third echo data and fourth echo data that are obtained based on an echo that is generated at a third echo time and an echo that is generated at a fourth echo time, respectively, and performing phase correction on either one or both of the first echo data and the second echo data, based on the generated B0 map.

The method may further include controlling a gradient magnetic field that is applied, based on the multi-echo sequence, and a sign of a readout gradient magnetic field that is applied at the third echo time may be the same as a sign of a readout gradient magnetic field that is applied at the fourth echo time.

The first echo time, the second echo time, the third echo time, and the fourth echo time may be included in a repetition time period.

The reconstructing may include reconstructing k-space data, based on another part of the first echo data other than the overlapping part included in the first echo data in the k-space, and the second echo data, performing phase correction on the second echo data included in the reconstructed k-space data, and re-reconstructing the k-space data, based on the overlapping part included in the first echo data, and the second echo data on which the phase correction is performed.

A non-transitory computer-readable storage medium may store a program for causing a computer to execute the method.

According to an aspect of another exemplary embodiment, there is provided a magnetic resonance imaging (MRI) apparatus for obtaining a magnetic resonance (MR) image, based on a multi-echo sequence, the MRI apparatus including a data obtainer configured to obtain first echo data, based on an echo that is generated at a first echo time, obtain second echo data, based on an echo that is generated at a second echo time later than the first echo time, and obtain third echo data, based on an echo that is generated at a third echo time later than the second echo time, the second echo data including a part overlapping a part included in the third echo data in a k-space. The MRI apparatus further includes an image processor configured to reconstruct the MR image, based on the first echo data, the second echo data, and the third echo data.

The image processor may be further configured to perform phase correction on the third echo data, obtain k-space data, based on the second echo data and the third echo data on which the phase correction is performed, the first echo data including a part overlapping a part included in the k-space data in the k-space, perform phase correction on the k-space data, and reconstruct the k-space data, based on the first echo data and the k-space data on which the phase correction is performed.

The image processor may be further configured to perform phase correction on the first echo data, obtain k-space data, based on the second echo data and the first echo data on which the phase correction is performed, the third echo data including a part overlapping a part included in the k-space data in the k-space, perform phase correction on the k-space data, and reconstruct the k-space data, based on the third echo data and the k-space data on which the phase correction is performed.

DETAILED DESCRIPTION

Hereinafter, the terms used in the specification will be briefly described, and then the present disclosure will be described in detail.

The terms used in this specification are those general terms currently widely used in the art in consideration of functions regarding the present disclosure, but the terms may vary according to the intention of one of ordinary skill in the art, precedents, or new technology in the art. Also, some terms may be arbitrarily selected by the applicant, and in this case, the meaning of the selected terms will be described in detail in the detailed description of the present specification. Thus, the terms used herein have to be defined based on the meaning of the terms together with the description throughout the specification.

When a part “includes” or “comprises” an element, unless there is a description contrary thereto, the part can further include other elements, not excluding the other elements. Also, the term “unit” in the exemplary embodiments means a software component or hardware component such as a field-programmable gate array (FPGA) or an application-specific integrated circuit (ASIC), and performs a specific function. However, the term “unit” is not limited to software or hardware. The “unit” may be formed to be in an addressable storage medium, or may be formed to operate one or more processors. Thus, for example, the term “unit” may refer to components such as software components, object-oriented software components, class components, and task components, and may include processes, functions, attributes, procedures, subroutines, segments of program code, drivers, firmware, micro codes, circuits, data, a database, data structures, tables, arrays, or variables. A function provided by the components and “units” may be associated with the smaller number of components and “units,” or may be divided into additional components and “units.”

Reference will now be made in detail to embodiments, examples of which are illustrated in the accompanying drawings. In the following description, well-known functions or constructions may not be described in detail so as not to obscure the exemplary embodiments with unnecessary detail.

Throughout the specification, an “image” may denote multi-dimensional data composed of discrete image elements (for example, pixels in a two-dimensional (2D) image and voxels in a three-dimensional (3D) image). For example, the image may be a medical image of an object captured by an X-ray apparatus, a computed tomography (CT) apparatus, a magnetic resonance imaging (MRI) apparatus, an ultrasound diagnosis apparatus, or another medical imaging apparatus.

Furthermore, in the present specification, an “object” may be a human, an animal, or a part of a human or animal. For example, the object may be an organ (e.g., the liver, the heart, the womb, the brain, a breast, or the abdomen), a blood vessel, or a combination thereof. The object may be a phantom. The phantom means a material having a density, an effective atomic number, and a volume that are approximately the same as those of an organism. For example, the phantom may be a spherical phantom having properties similar to the human body.

Furthermore, in the present specification, a “user” may be, but is not limited to, a medical expert, such as a medical doctor, a nurse, a medical laboratory technologist, or a technician who repairs a medical apparatus.

Furthermore, in the present specification, an “MR image” refers to an image of an object obtained by using the nuclear magnetic resonance principle.

Furthermore, in the present specification, a “pulse sequence” refers to continuity of signals repeatedly applied by an MRI apparatus. The pulse sequence may include a time parameter of a radio frequency (RF) pulse, for example, repetition time (TR) or echo time (TE).

Also, the term ‘pulse sequence diagram’ used herein may refer to a diagram for explaining a sequence of signals applied in an MRI system. For example, the pulse sequence schematic diagram may be a diagram showing a radio frequency (RF) pulse, a gradient magnetic field, an MR signal, or the like according to time.

An MRI system is an apparatus for acquiring a sectional image of a part of an object by expressing, in a contrast comparison, a strength of an MR signal with respect to an RF signal generated in a magnetic field having a strength. For example, if an RF signal that only resonates an atomic nucleus (for example, a hydrogen atomic nucleus) is emitted for an instant toward the object placed in a strong magnetic field and then such emission stops, an MR signal is emitted from the atomic nucleus, and thus the MRI system may receive the MR signal and acquire an MR image. The MR signal denotes an RF signal emitted from the object. An intensity of the MR signal may be determined according to a density of a predetermined atom (for example, hydrogen) of the object, a relaxation time T1, a relaxation time T2, and a flow of blood or the like.

MRI systems include characteristics different from those of other imaging apparatuses. Unlike imaging apparatuses such as CT apparatuses that acquire images according to a direction of detection hardware, MRI systems may acquire 2D images or 3D volume images that are oriented toward an optional point. MRI systems do not expose objects or examiners to radiation, unlike CT apparatuses, X-ray apparatuses, position emission tomography (PET) apparatuses, and single photon emission CT (SPECT) apparatuses, may acquire images having high soft tissue contrast, and may acquire neurological images, intravascular images, musculoskeletal images, and oncologic images that are used to precisely capture abnormal tissues.

FIG. 1is a diagram illustrating a process performed by an MRI apparatus to obtain an MR image, based on a multi-echo sequence, according to an exemplary embodiment.

In detail, referring toFIG. 1, an MRI apparatus according to an exemplary embodiment performs a process of reconstructing a final image based on first echo data E1corresponding to a first echo time TE1and second echo data E2corresponding to a second echo time TE2.

The MRI apparatus according to an exemplary embodiment may obtain an MR signal generated based on a multi-echo sequence.

The multi-echo sequence refers to a pulse sequence used for the MRI apparatus to obtain an image by using a plurality of echoes generated after an RF pulse is applied once. That is, the multi-echo sequence may have at least two echo times during one TR.

The MR signal obtained by using the multi-echo sequence may be represented as k-space data.

The k-space data refers to a signal generated by placing an MR signal, which is an RF signal received from each of coils according to channels included in a high frequency multi-coil, in a k-space.

The k-space data may be 2D k-space data or 3D k-space data. For example, the 2D k-space data has a 2D spatial frequency domain and is formed by a kx-axis corresponding to frequency encoding and a ky-axis corresponding phase encoding. Also, the 3D k-space data is formed by the kx-axis, the ky-axis, and a kz-axis corresponding to a progress direction in a space. The kz-axis corresponds to a slice selection gradient.

The k-space data may be reconstructed into an MR image by using a fast Fourier transform (FFT) or a Fourier transform (FT).

When the multi-echo sequence is used as described above, the MRI apparatus may use a method of obtaining a plurality of pieces of k-space data corresponding to a plurality of echo times by applying a gradient magnetic field for phase encoding only once during one TR.

The MRI apparatus using the multi-echo sequence may use another method of obtaining one piece of k-space data by using a plurality of echoes generated during one TR. This method is referred to as an echo planar imaging (EPI) method.

FIG. 1is a diagram illustrating a case where the MRI apparatus uses a method of obtaining a plurality of pieces of k-space data respectively corresponding to a plurality of echo times according to an exemplary embodiment. A square block shown inFIG. 1indicates a k-space.

Referring toFIG. 1, the first echo data E1may be data obtained by using an echo generated at the first echo time TE1among a plurality of echo times included in one TR. The first echo data E1may include data of a central part of the k-space, as shown inFIG. 1. Also, the first echo data E1may include data whose ky-coordinate in the k-space is 0.

The second echo data E2may be data obtained by using an echo generated at the second echo time TE2, which is later than the first echo time TE1, among the plurality of echo times included in the one TR. The second echo data E2may not include the data of the central part of the k-space, as shown inFIG. 1. Also, the second echo data E2may not include the data whose ky-coordinate in the k-space is 0.

The first echo data E1and the second echo data E2may refer to raw data or k-space data.

The raw data may be an MR signal that is an RF signal received from each of a plurality of channel coils included in a high frequency multi-coil through an MRI process.

The k-space data may be data obtained by sampling an obtained MR signal in the k-space. The k-space data may be data obtained by performing full sampling on an obtained MR signal at all points of the k-space, or may be data obtained by performing, on an obtained MR signal, under-sampling by which sampling is performed at some points and not performed at other points. Signals at non-obtained points among pieces of incomplete k-space data obtained by using under-sampling may be reconstructed by using a generalized autocalibrating partially parallel acquisition (GRAPPA) method or a simultaneous acquisition of spatial harmonics (SMASH) method using a map having additional coil information (e.g., a coil sensitivity map).

For convenience,FIG. 1is explained on the assumption that the first echo data E1and the second echo data E2are k-space data that are sampled in the k-space. An arrangement of the first echo data E1and the second echo data E2in the k-space is not limited to that inFIG. 1, and may be modified in various ways.

Referring back to a process of obtaining an MR image ofFIG. 1, the MRI apparatus according to an exemplary embodiment may obtain the first echo data E1corresponding to the first echo time TE1and may obtain the second echo data E2corresponding to the second echo time TE2that is later than the first echo time TE1.

In this case, the first echo data E1and the second echo data E2may include an overlapping part in the k-space. For example, the first echo data E1may further include additional data15about the overlapping part in the k-space. The additional data15may account for, for example, about 10% of the entire k-space. In detail, when the k-space includes 256 lines to reconstruct an image having a resolution of 256*256, the additional data15may be obtained by using about 25 or 26 lines.

The first echo data E1may include the data of the central part of the k-space in the k-space and may include the additional data15, as shown inFIG. 1. In this case, the first echo data E1may be ‘reference echo data’. Also, an echo time of an echo generated in order for the MRI apparatus to obtain the reference echo data may be referred to as a ‘reference echo time’.

Characteristics of a final image to be obtained may be determined based on the reference echo data of the k-space. In other words, the reference echo time may vary according to the characteristics of the final image to be obtained.

For example, when a T1-weighted image is to be obtained, the MRI apparatus according to an exemplary embodiment may determine the first echo time TE1as the reference echo time. Also, when a T2-weighted image is to be obtained, the MRI apparatus according to an exemplary embodiment may determine the second echo time TE2, which is later than the first echo time TE1, as the reference echo time. That is, the MRI apparatus according to an exemplary embodiment may determine the reference echo time, which is an echo time of the data of the central part of the k-space, to be a time of an early echo or a late echo, according to the characteristics of the final image to be obtained.

The MRI apparatus according to an exemplary embodiment may perform phase correction on the second echo data E2. The phase correction refers to a process of correcting a phase of echo data to a phase corresponding to the reference echo time.

When pieces of data obtained at different echo times are used, the MRI apparatus according to an exemplary embodiment may be affected by an echo time shift, magnetic field inhomogeneity, spin dephasing, and eddy current.

In detail, when the MRI apparatus according to an exemplary embodiment uses pieces of data obtained at different echo times, a plurality of echo times may differ from pre-designed echo times. Also, amounts by which the echo times are shifted may differ from one another.

According to an exemplary embodiment, when the MRI apparatus uses a gradient echo pulse sequence, the MRI apparatus may be more severely affected by magnetic field inhomogeneity than an MRI apparatus using a spin echo pulse sequence.

Also, when the MRI apparatus uses a gradient echo pulse sequence, because the MRI apparatus does not use a 180° pulse unlike an MRI apparatus using a spin echo pulse sequence, the MRI apparatus may be more severely affected by spin dephasing than the MRI apparatus using the spin echo pulse sequence.

The MRI apparatus according to an exemplary embodiment may perform phase correction to reduce any one or any combination of the effects of an echo time shift, magnetic field inhomogeneity, and spin dephasing on a signal intensity.

That is, the MRI apparatus according to an exemplary embodiment may reduce the effects of blur or aliasing in the final image that may occur as pieces of data obtained at different echo times are used by performing the phase correction.

Referring toFIG. 1, when the first echo data E1is reference echo data, the MRI apparatus according to an exemplary embodiment may perform phase correction on the second echo data E2and may obtain corrected second echo data E2C whose phase is corrected based on the first echo time TE1.

The MRI apparatus according to an exemplary embodiment may obtain final k-space data101based on the first echo data E1and the corrected second echo data E2C. Also, the MRI apparatus may reconstruct a final image based on the final k-space data101.

The final k-space data101may be data reconstructed in the k-space. For example, when the first echo data E1and the second echo data E2are under-sampled k-space data, the final k-space data101may be data reconstructed by using a GRAPPA method or a SMASH method.

Overlapping data19of the final k-space data101reconstructed by the MRI apparatus according to an exemplary embodiment may be k-space data reconstructed by applying a GRAPPA method or the like to the additional data15of the first echo data E1.

The MRI apparatus according to an exemplary embodiment may obtain a final image by perform an FT on the final k-space data101. The MRI apparatus according to an exemplary embodiment may reconstruct a final image by applying a method such as sensitivity encoding (SENSE) or parallel imaging with localized sensitivity (PILS) to the final k-space data101.

The MRI apparatus according to an exemplary embodiment may improve the quality of the reconstructed final image by obtaining the additional data15about the overlapping part19in the k-space between the first echo data E1and the second echo data E2.

Also, when the MRI apparatus according to an exemplary embodiment uses the first echo data E1and the second echo data E2obtained at different echo times, the MRI apparatus may increase a signal-to-noise ratio (SNR) and a contrast ratio of the final image by combining characteristics of pieces of echo data.

Also, because the MRI apparatus according to an exemplary embodiment obtains the final k-space data101by using the first echo data E1and the second echo data E2obtained at different echo times, the MRI apparatus may reduce a time taken to obtain the final image.

FIG. 2Ais a graph illustrating a process performed by an MRI apparatus to obtain k-space data, based on a multi-echo sequence, according to an exemplary embodiment.

Referring toFIG. 2A, a multi-echo sequence used by the MRI apparatus according to an exemplary embodiment may be, for example, a gradient echo sequence.

The MRI apparatus according to an exemplary embodiment may excite one RF pulse, and then may generate a plurality of gradient echoes by applying readout gradient magnetic fields Gread so that the readout gradient magnetic fields Gread have the same intensity and alternating signs.

A gradient magnetic field for phase encoding is not shown inFIG. 2Afor convenience of explanation of echoes generated according to the readout gradient magnetic field Gread.

Referring toFIG. 2A, the MRI apparatus according to an exemplary embodiment may generate a plurality of echoes during one TR. That is, the MRI apparatus according to an exemplary embodiment may generate echoes at the first echo time TE1, the second echo time TE2, a third echo time TE3, and a fourth echo time TE4during one TR.

Referring toFIG. 2A, the MRI apparatus according to an exemplary embodiment may fill one line of a k-space201with data in a positive direction211by using a readout gradient magnetic field corresponding to the first echo time TE1.

Also, the MRI apparatus according to an exemplary embodiment may fill one line of a k-space203with data in a negative direction213by using a readout gradient magnetic field corresponding to the second echo time TE2.

Also, the MRI apparatus according to an exemplary embodiment may fill one line of a k-space205with data in a positive direction215by using a readout gradient magnetic field corresponding to the third echo time TE3.

Also, the MRI apparatus according to an exemplary embodiment may fill one line of a k-space207with in a negative direction217by using a readout gradient magnetic field corresponding to the fourth echo time TE4.

The MRI apparatus according to an exemplary embodiment may obtain pieces of k-space data having different characteristics by using a plurality of echo times.

For example, when an image is reconstructed by using k-space data obtained at the first echo time TE1that is a short echo time, the MRI apparatus may obtain an image in which a T2 effect or a T2* effect is reduced and a T1 effect is increased.

Also, when an image is reconstructed by using k-space data obtained at the fourth echo time TE4that is a long echo time, the MRI apparatus may obtain an image in which a T1 effect is reduced and a T2 effect or a T2* effect is increased.

The MRI apparatus according to an exemplary embodiment may adjust a tissue contrast, a clarity of venous blood included in a cross-sectional image, an SNR, etc. by reconstructing a final image by combining pieces of k-space data having different echo times.

FIG. 2Bis a graph illustrating a process performed by an MRI apparatus to obtain an MR image, based on a gradient echo sequence, according to an exemplary embodiment.

The MRI apparatus according to an exemplary embodiment may obtain an MR signal having a highest intensity at an echo time. The MR signal may be received through, for example, an RF coil included in the MRI apparatus.

The MRI apparatus according to an exemplary embodiment may place k-space data corresponding to the MR signal having the highest intensity obtained at the echo time at a position whose kx-coordinate in a k-space is 0.

For example, when the MRI apparatus fills one line of the space201with data in the positive direction211by using a readout gradient magnetic field corresponding to the first echo time TE1, as described with reference toFIG. 2A, the k-space data placed at the position whose kx-coordinate in the k-space is 0 may correspond to a highest point of an echo signal.

Referring toFIG. 2B, the MRI apparatus according to an exemplary embodiment may use a gradient echo sequence for obtaining an MR signal corresponding to the highest point of the echo signal at the first echo time TE1, the second echo time TE2, the third echo time TE3, and the fourth echo time TE4.

In this case, as shown inFIG. 2B, an echo time shift may occur in a plurality of echoes obtained by the MRI apparatus according to an exemplary embodiment during one TR. That is, an MR signal corresponding to a point other than a highest point of an echo signal may be obtained at the first echo time TE1, the second echo time TE2, the third echo time TE3, and the fourth echo time TE4that are a plurality of echo times of echoes obtained during one TR.

For example, as shown inFIG. 2B, the first echo time TE1may be shifted leftward by T1and the second echo time TE2may be shifted rightward by T2. Also, the third echo time TE3may be shifted leftward by T3and the fourth echo time TE4may be shifted rightward by T4.

The MRI apparatus according to an exemplary embodiment may correct the obtained k-space data in a one-dimensional (1D) manner by compensating for an amount by which an echo time is shifted. Also, the MRI apparatus according to an exemplary embodiment may perform phase correction on pieces of data in the k-space in a 2D or 3D manner.

For example, the MRI apparatus may use a B0 map to perform phase correction. The B0 map is obtained by placing a phase or frequency difference according to an echo time difference in the k-space. In detail, the MRI apparatus may obtain the B0 map in the k-space by using a phase difference between two pieces of k-space data having an echo time difference therebetween. The MRI apparatus may obtain a frequency difference corresponding to the phase difference mapped to the B0 map. The MRI apparatus may generate the B0 map to which a color corresponding to a frequency according to the echo time difference is mapped. Such a process of performing phase correction by using a B0 map obtained by using a phase difference between two pieces of k-space data having an echo time difference may be referred to as conjugate phase reconstruction. To perform phase correction by using a B0 map, any of various well-known methods such as conjugate phase reconstruction may be used.

The MRI apparatus according to an exemplary embodiment may reduce the effects of an echo time shift of data in a k-space and may reduce the effects of blur or aliasing in an obtained final image by performing phase correction by using a B0 map.

FIG. 3Ais a block diagram of an MRI apparatus300aaccording to an exemplary embodiment.

The MRI apparatus300aofFIG. 3Ais an apparatus for obtaining an MR image by using a multi-echo sequence. In detail, the MRI apparatus300amay be an apparatus for capturing an MR image of an object by using a multi-echo sequence or an apparatus for processing data obtained by capturing an MR image of an object by using a multi-echo sequence.

For example, the MRI apparatus300amay be an apparatus for applying an RF pulse using a multi-echo sequence to an object through a plurality of channel coils included in a high frequency multi-coil and reconstructing an MR image by using an MR signal obtained through the plurality of channel coils.

Also, the MRI apparatus300amay be a server apparatus for providing a multi-echo sequence to be applied to an object and reconstructing an MR image by using an obtained MR signal. The server apparatus may be a medical server apparatus in a hospital or the like in which an MRI process is performed.

Referring toFIG. 3A, the MRI apparatus300amay include a data obtainer310and an image processor320.

The data obtainer310may obtain the first echo data E1by using an echo generated at the first echo time TE1and may obtain the second echo data E2by using an echo generated at the second echo time TE2that is later than the first echo time TE1. The first echo data E1and the second echo data E2may include an overlapping part in a k-space.

According to an exemplary embodiment, the first echo data and the second echo data may be raw data or may be k-space data corresponding to raw data.

The data obtainer310may obtain a plurality of pieces of incomplete k-space data respectively corresponding to a plurality of echoes. The term ‘incomplete k-space data’ refers to k-space data when an MR signal is not sampled at least one point in the k-space and thus is to be reconstructed at the at least one point in the k-space. Non-obtained signals from the ‘incomplete k-space data’ may be reconstructed by using obtained signals.

The data obtainer310according to an exemplary embodiment may obtain additional data about an overlapping part by using an echo generated at a reference echo time of reference echo data.

Reference echo data may refer to echo data including data of a central part of the k-space. Also, the reference echo time may refer to an echo time of an echo generated to obtain the reference echo data.

According to an exemplary embodiment, either one or each of the first echo data and the second echo data may include the data of the central part of the k-space.

The data obtainer310according to an exemplary embodiment may determine characteristics of an MR image to be obtained. Also, the data obtainer310may determine that the first echo data or the second echo data is to include the data of the central part of the k-space according to the determined characteristics of the MR image. The determining of the characteristics of the MR image may include determining whether, for example, the MR image is a T1-weighted image or a T2 (or T2*)-weighted image.

When the T1-weighted image is to be obtained, the data obtainer310may determine a shortest echo time as the reference echo time. In this case, reference echo data may be obtained by using an echo generated at the shortest echo time. For example, when the T1-weighted image is to be obtained, the data obtainer310may determine that the first echo data is to include the data of the central part of the k-space. In this case, the reference echo time may be referred to as corresponding to an early echo.

Also, when the T2 or T2*-weighted image is to be obtained, the data obtainer310may determine a longest echo time as the reference echo time. In this case, reference echo data may be obtained by using an echo generated at the longest echo time. For example, when the T2 or T2*-weighted image is to be obtained, the data obtainer310may determine that the second echo data is to include the data of the central part of the k-space. In this case, the reference echo time may be referred to as corresponding to a late echo.

When the first echo data includes the data of the central part of the k-space and the second echo data does not include the data of the central part of the k-space, the data obtainer310may obtain additional data about the overlapping part by using an echo generated at the first echo time.

When the second echo data includes the data of the central part of the k-space and the first echo data does not include the data of the central part of the k-space, the data obtainer310may obtain the additional data about the overlapping part by using an echo generated at the second echo time.

According to an exemplary embodiment, a case where the first echo data and the second echo data are k-space data obtained by sampling a magnetic MR signal, which is emitted from an object, in the k-space has been explained. However, the data obtainer310may receive only an MR signal from an RF coil and the image processor320may perform a sampling process in the k-space.

The image processor320may reconstruct an MR image based on the first echo data and the second echo data.

For example, the first echo data and the second echo data may be k-space data, that is, incomplete k-space data, obtained by under-sampling an MR signal. In this case, the incomplete k-space data may be reconstructed based on a map having additional coil information (e.g., a coil sensitivity map) such as a SMASH method or an additional calibration signal such as a GRAPPA method.

Also, the image processor320may perform phase correction on either one or both of the first echo data and the second echo data and may reconstruct an MR image by using either one or both of the first echo data and the second echo data on which the phase correction has been performed.

The image processor320may perform phase correction based on a phase of data including the data of the central part of the k-space among the first echo data and the second echo data.

For example, when the first echo data is reference echo data, the image processor320may perform phase correction on the second echo data based on a phase of the first echo data.

FIG. 3Bis a block diagram of an MRI apparatus300baccording to another exemplary embodiment.

The MRI apparatus300bmay include a data obtainer315, an image processor325, a gradient magnetic field controller330, and an output interface340.

The data obtainer315and the image processor325ofFIG. 3Bmay perform the same functions as those of the data obtainer310and the image processor320ofFIG. 3A, and thus a repeated explanation of the data obtainer315and the image processor325will not be given.

The data obtainer315may obtain the first echo data E1by using an echo generated at the first echo time TE1and may obtain the second echo data E2by using an echo generated at the second echo time TE2that is later than the first echo time TE1. The first echo data E1and the second echo data E2may include an overlapping part in a k-space.

The image processor325according to an exemplary embodiment may generate a B0 map by using third echo data and fourth echo data obtained by using echoes generated at a third echo time and a fourth echo time.

According to an exemplary embodiment, the first echo time, the second echo time, the third echo time, and the fourth echo time may be included in one TR of a multi-echo sequence.

Also, the image processor325may perform phase correction on either one or both of the first echo data and the second echo data by using the generated B0 map.

The gradient magnetic field controller330according to an exemplary embodiment may control a gradient magnetic field to be applied according to the multi-echo sequence.

A first readout gradient magnetic field applied by the gradient magnetic field controller330at the first echo time and a second readout gradient magnetic field applied by the gradient magnetic field controller330at the second echo time may have the same sign.

Also, a third readout gradient magnetic field applied by the gradient magnetic field controller330at the third echo time and a fourth readout gradient magnetic field applied by the gradient magnetic field controller330at the fourth echo time may have the same sign.

The output interface340may output image data generated by the image processor325and a reconstructed MR image to a user. Also, the output interface340may output information to be used for the user to manipulate the MRI apparatus300bsuch as a user interface (UI), user information, or object information.

In detail, the output interface340may display a predetermined screen on any of various displays such as a cathode ray tube (CRT) display, a liquid crystal display (LCD), a plasma display panel (PDP) display, an organic light-emitting diode (OLED) display, a field emission display (FED), a light-emitting diode (LED) display, a vacuum fluorescent display (VFD), a digital light processing (DLP) display, a flat panel display (FPD), a 3D display, or a transparent display.

Also, the output interface340may display a UI screen for displaying information about an MRI process of the MRI apparatus300b.

For example, the output interface340may display a UI screen for designing a multi-echo sequence and a screen for displaying an imaging environment of the MRI apparatus300band a multi-echo sequence used in the MRI apparatus300b.

Also, the output interface340may display images generated in a process of reconstructing an MR image, information about an MRI protocol that is being currently performed, and information about an MRI protocol that is to be subsequently performed.

Also, the output interface340may display a screen including a B0 map to which a color is mapped in order for the user to visually recognize the B0 map generated to perform phase correction.

The MRI apparatus300bmay further include an input interface, and may determine information to be used to reconstruct an MR image and a multi-echo sequence to be used in an MRI process based on information input through the UI screen.

In detail, the MRI apparatus300bmay determine a multi-echo sequence to be used in an MRI process based on information about an echo train length (ETL) input through the UI screen. Also, the MRI apparatus300bmay determine reference echo data based on information about reference echo data input through the UI screen.

Also, the MRI apparatus300bmay determine a reconstruction method based on information about a method of reconstructing MR data input through the UI screen.

Also, the MRI apparatus300bmay determine a type of data used to generate the B0 map based on information input through the UI screen.

FIG. 4Ais a pulse sequence diagram410of a pulse sequence with an ETL of 2 applied by the MRI apparatus300aor300b, according to an exemplary embodiment.

Referring toFIG. 4A, the MRI apparatus300aor300bmay apply a gradient magnetic field420according to a multi-echo sequence shown in the pulse sequence diagram410.

In detail, the pulse sequence diagram410may show gradient magnetic fields PE1, PE2, and PE2rewind of a phase encoding direction and a gradient magnetic field420of a readout direction applied by the MRI apparatus300aor300baccording to an exemplary embodiment during one TR. The readout direction may correspond to a kx direction of a k-space and the phase encoding direction may correspond to a ky direction of the k-space.

The pulse sequence diagram410may show the multi-echo sequence. The number of echoes used to obtain data in one TR of the multi-echo sequence may be referred to as an ETL. According to the multi-echo sequence of the pulse sequence diagram410ofFIG. 4A, the MRI apparatus300aand300breconstructs a final k-space by obtaining the first echo data E1and the second echo data E2respectively at the first echo time TE1and the second echo time TE2. That is, in the pulse sequence diagram410, an ETL is 2.

The gradient magnetic fields PE1, PE2, and PE2rewind of the phase encoding direction ofFIG. 4Aindicate time intervals to which gradient magnetic fields of the phase encoding directions are applied. The gradient magnetic fields PE1, PE2, and PE2rewind of the phase encoding direction have different strengths according to TRs.

Referring toFIG. 4A, the MRI apparatus300aor300bmay apply the gradient magnetic field420for generating a plurality of echoes in the readout direction of the k-space, as shown in the pulse sequence diagram410. The MRI apparatus300aor300bmay generate echoes at the first echo time TE1, the second echo time TE2, and third echo time TE1′ during one TR by applying the gradient magnetic field420.

The MRI apparatus300aor300bmay determine a position of the first echo data E1on a ky-axis in the k-space by applying the gradient magnetic field PE of the phase encoding direction before obtaining the first echo data E1.

After the gradient magnetic field PE1of the phase encoding direction is applied, the MRI apparatus300aor300bmay fill one line of data among the first echo data E1of the k-space in a positive direction411by using a readout gradient magnetic field corresponding to the first echo time TE1. The first echo data E1may be data for reconstructing a final k-space data and may be data used to perform phase correction.

The MRI apparatus300aor300bmay fill one line of data among third echo data E1′ of the k-space in a negative direction413by using a readout gradient magnetic field corresponding to the third echo time TE1′ by reversing a sign of the readout gradient magnetic field. According to the exemplary embodiment ofFIG. 4A, the third echo data E1′ may be data used to perform phase correction, instead of data used to reconstruct the final k-space data. According to another exemplary embodiment, the third echo data E1′ may include data used to reconstruct the final k-space data.

The MRI apparatus300aor300bmay determine a position of the second echo data E2on the ky-axis in the k-space by applying the gradient magnetic field PE2of the phase encoding direction before obtaining the second echo data E2.

Referring toFIG. 4A, when the MRI apparatus300aor300bapplies the gradient magnetic field PE2of the phase encoding direction, a position of data in the k-space may be moved away from the origin of the ky-axis.

The MRI apparatus300aor300bmay fill one line of data among the second echo data E2of the k-space in a positive direction415by using a readout gradient magnetic field corresponding to the second echo time TE2by re-reversing a sign of the readout gradient magnetic field. Next, the MRI apparatus300aor300bmay apply the gradient magnetic field PE2rewind of the phase encoding direction, which has the same strength and the opposite direction as and to those of the gradient magnetic field PE2of the phase encoding direction, before entering a next TR. When the MRI apparatus300aor300bapplies the gradient magnetic field PE2rewind of the phase encoding direction, data of the k-space to be obtained in the next TR may be placed at the origin of the ky-axis.

Next, in the next TR, the MRI apparatus300aor300bmay determine a position of the first echo data E1on the ky-axis in the k-space by applying the gradient magnetic field PE1of the phase encoding direction.

Referring toFIG. 4A, the MRI apparatus300aor300bmay obtain the first echo data E1corresponding to the first echo time TE1, the second echo data E2corresponding to the second echo time TE2, and the third echo data E1′ corresponding to the third echo time TE1′ by applying the gradient magnetic field420during several TRs.

The directions411and415, in which pieces of data are placed in the k-space when the first echo data E1and the second echo data E2are obtained by the MRI apparatus300aor300b, are the same. That is, a readout gradient magnetic field applied at the first echo time TE1and a readout gradient magnetic field applied at the second echo time TE2have the same sign.

When readout gradient magnetic fields have the same sign, directions in which echo time shifts occur may be the same, and in this case, the MRI apparatus300aor300bmay reduce an error caused by an echo time shift in a reconstructed final image.

Referring toFIG. 4A, because the MRI apparatus300aor300bdoes not apply a phase encoding gradient magnetic field to obtain the third echo data E1′ after obtaining the first echo data E1, positions of the first echo data E1and the third echo data E1′ on the ky-axis in the k-space may be opposite to each other.

The directions411and413, in which pieces of data are placed in the k-space when the MRI apparatus300aor300bobtains the first echo data E1and the third echo data E1′, differ from each other. If the MRI apparatus300aor300bgenerates a B0 map by using the first echo data E1and the third echo data E1′, the MRI apparatus300aor300bis used to correct an error caused when directions in which echo time shifts occur differ from each other.

As shown inFIG. 4A, the first echo data E1may include data of a central part of the k-space and the second echo data E2may not include the data of the central part of the k-space.

Referring toFIG. 4A, when a T1-weighted image is to be obtained, the MRI apparatus300aor300bmay determine the first echo time TE1as a reference echo time. In this case, the first echo data E1that is reference echo data may include an overlapping part in the k-space with the second echo data E2.

FIG. 4Bis a diagram illustrating a process performed by the MRI apparatus300aor300bto obtain an MR image, according to the pulse sequence diagram410ofFIG. 4A, according to an exemplary embodiment.

Referring toFIG. 4B, the MRI apparatus300aor300bperforms a process of reconstructing a final image based on the first echo data E1corresponding to the first echo time TE1and the second echo data E2corresponding to the second echo time TE2.

Referring toFIG. 4B, the MRI apparatus300aor300baccording to an exemplary embodiment may obtain the first echo data E1corresponding to the first echo time TE1and then may obtain the second echo data E2corresponding to the second echo time TE2that is later than the first echo time TE1. Also, the MRI apparatus300aor300bmay obtain the third echo data E1′ corresponding to the third echo time TE1′.

Referring toFIG. 4B, reference echo data may be the first echo data E1and a reference echo time may be the first echo time TE1. In this case, the first echo data E1may include an overlapping part in the k-space with the second echo data E2. For example, the first echo data E1may further include additional data425about the overlapping part in the k-space with the second echo data E2. The additional data425may account for, for example, about 10% of the entire k-space.

The MRI apparatus300aor300baccording to an exemplary embodiment may perform phase correction on the second echo data E2. The MRI apparatus300aor300bmay generate a B0 map by using the first echo data E1and the third echo data E1′ and may perform phase correction by using the generated B0 map.

As described with reference toFIG. 4A, when the directions411and413, in which pieces of data are placed in the k-space when the MRI apparatus300aor300bobtains the first echo data E1and the third echo data E1′, differ from each other, the MRI apparatus300aor300bis used to correct an error caused when directions in which echo time shifts occur differ from each other, to generate the B0 map.

The MRI apparatus300aor300bmay perform phase correction on the second echo data E2and may obtain second echo data E2C whose phase is corrected based on the first echo time TE1. The MRI apparatus300aor300bmay reduce the effects of blur or aliasing in a final image that may occur as pieces of data obtained at different echo times are used due to the phase correction.

The MRI apparatus300aor300bmay obtain final k-space data E1+E2C based on the first echo data E1and the corrected second echo data E2C. If the first echo data E1and the second echo data E2are under-sampled k-space data, the final k-space data E1+E2C may be data reconstructed by using a GRAPPA method or a SMASH method.

When the final k-space data E1+E2C is reconstructed, the MRI apparatus300aor300bmay reconstruct k-space data based on data of the first echo data E1other than the additional data425and the second echo data E2. The MRI apparatus300aor300bmay use a GRAPPA method or the like to reconstruct the k-space data. Next, the MRI apparatus300aor300bmay re-reconstruct the k-space data based on the first echo data E1including the additional data425and the corrected second echo data E2C. In this case, a GRAPPA method or the like may be re-applied to the additional data425, and the MRI apparatus300aor300bmay obtain the final k-space data E1+E2C.

According to the exemplary embodiment ofFIGS. 4A and 4B, the MRI apparatus300aor300bmay generate a B0 map for performing phase correction and final k-space data by using echo data obtained during one TR. Accordingly, the MRI apparatus300aor300bmay obtain data to be used for phase correction by using only a pulse sequence for obtaining k-space data without additionally using a pulse sequence for phase correction.

FIG. 5Ais a pulse sequence diagram510of another pulse sequence with an ETL of 2 applied by the MRI apparatus300aor300b, according to an exemplary embodiment.

Referring toFIG. 5A, the MRI apparatus300aor300bmay apply a gradient magnetic field520according to a multi-echo sequence shown in the pulse sequence diagram510.

Like inFIG. 4A, the pulse sequence diagram510may show the gradient magnetic fields PE1, PE2, and PE2rewind of a phase encoding direction and a gradient magnetic field520of a readout direction applied by the MRI apparatus300aor300baccording to an exemplary embodiment during one TR.

Referring toFIG. 5A, the MRI apparatus300aor300bmay apply the gradient magnetic field520for generating a plurality of echoes in the readout direction of a k-space as shown in the pulse sequence diagram510.

The MRI apparatus300aor300bmay generate echoes at the first echo time TE1, the second echo time TE2, the third echo time TE1′ and a fourth echo time TE2′ during one TR by applying the gradient magnetic field520. That is, the pulse sequence diagram510ofFIG. 5Ais different from the pulse sequence diagram410ofFIG. 4Ain that an echo corresponding to the fourth echo time TE2′ may be additionally generated.

The MRI apparatus300aor300bmay obtain the first echo data E1and the second echo data E2by using echoes generated at the first echo time TE1and the second echo time TE2included in one TR. The MRI apparatus300aor300breconstructs a final k-space by obtaining the first echo data E1and the second echo data E2.

According to the exemplary embodiment ofFIG. 5A, the third echo data E1′ and fourth echo data E2′ may be data used for phase correction, instead of data used to reconstruct final k-space data. According to another exemplary embodiment, the third echo data E1′ and the fourth echo data E2′ may include data used to reconstruct the final k-space data.

First, the MRI apparatus300aor300bmay determine a position of the first echo data E1on a ky-axis in the k-space by applying the gradient magnetic field PE1of the phase encoding direction before obtaining the first echo data E1.

After the gradient magnetic field PE1of the phase encoding direction is applied, the MRI apparatus300aor300bmay fill one line of data among the first echo data E1of the k-space in a positive direction511by using a readout gradient magnetic field corresponding to the first echo time TE1.

The MRI apparatus300aor300bmay fill one line of data among the third echo data E1′ of the k-space in a negative direction513by using a readout gradient magnetic field corresponding to the third echo time TE1′ by reversing a sign of the readout gradient magnetic field.

The MRI apparatus300aor300bmay determine a position of the second echo data E2on the ky-axis in the k-space by applying the gradient magnetic field PE2of the phase encoding direction before obtaining the second echo data E2.

The MRI apparatus300aor300bmay fill one line of data among the second echo data E2of the k-space in a positive direction515by using a readout gradient magnetic field corresponding to the second echo time TE2by re-reversing a sign of the readout gradient magnetic field.

Next, the MRI apparatus300aor300bmay apply the gradient magnetic field PE2rewind of the phase encoding direction that has the same strength and the opposite direction as and to those of the gradient magnetic field PE2of the phase encoding direction. Next, the MRI apparatus300aor300bmay fill one line of data among the fourth echo data E2′ of the k-space in a negative direction517by using a readout gradient magnetic field corresponding to the fourth echo time TE2′ by re-reversing a sign of the readout gradient magnetic field.

When the MRI apparatus300aor300bapplies the gradient magnetic field PE2rewind of the phase encoding direction, data in the k-space of a next TR may be placed at the origin of the ky-axis.

Next, in the next TR, the MRI apparatus300aor300bmay determine a position of the echo data E1on the ky-axis in the k-space by applying the gradient magnetic field PE1of the phase encoding direction.

Referring toFIG. 5A, the MRI apparatus300aor300bmay obtain the first echo data E1corresponding to the first echo time TE1, the second echo data E2corresponding to the second echo time TE2, the third echo data E1′ corresponding to the third echo time TE1′, and the fourth echo data E2′ corresponding to the fourth echo time TE2′ by applying the gradient magnetic field520during several TRs.

Referring toFIG. 5A, positions of the third echo data E1′ and the fourth echo data E2′ on the ky-axis in the k-space may be opposite to each other. Positions of the first echo data E1and the third echo data E1′ on the ky-axis may differ from each other.

The directions513and517, in which pieces of data are placed in the k-space when the MRI apparatus300aor300bobtains the third echo data E1′ and the fourth echo data E2′, are the same. If the MRI apparatus300aor300bgenerates a B0 map by using the third echo data E1′ and the fourth echo data E2′, the MRI apparatus300aor300bmay minimize an error caused when directions in which echo time shifts occur differ from each other.

As shown inFIG. 5A, the first echo data E1may include data of a central part of the k-space and the second echo data E2may not include the data of the central part of the k-space.

Referring toFIG. 5A, when a T1-weighted image is to be obtained, the MRI apparatus300aor300bmay determine the first echo time TE1as a reference echo time. In this case, the first echo data E1that is reference echo data may include an overlapping part in the k-space with the second echo data E2.

FIG. 5Bis a diagram illustrating a process performed by the MRI apparatus300aor300bto obtain an MR image, according to the pulse sequence diagram510ofFIG. 5A, according to an exemplary embodiment.

Referring toFIG. 5B, the MRI apparatus300aor300bperforms a process of reconstructing a final image based on the first echo data E1corresponding to the first echo time TE1and the second echo data E2corresponding to the second echo time TE2.

The MRI apparatus300aor300baccording to an exemplary embodiment may obtain the first echo data E1corresponding to the first echo time TE1and may obtain the second echo data E2corresponding to the second echo time TE2that is later than the first echo time. Also, the MRI apparatus300aor300bmay obtain the third echo data E1′ corresponding to the third echo time TE1′ and the fourth echo data E2′ corresponding to the fourth echo time TE2′ to perform phase correction.

Referring toFIG. 5B, reference echo data may be the first echo data E1and a reference echo time may be the first echo time TE1. In this case, the first echo data E1may include an overlapping part in the k-space with the second echo data E2. For example, the first echo data E1may further include additional data525about an overlapping part in a k-space with the second echo data E2. The additional data525may account for, for example, about 10% of the entire k-space.

The MRI apparatus300aor300baccording to an exemplary embodiment may perform phase correction on the second echo data E2. As described with reference toFIG. 5A, because the directions513and517, in which pieces of data are placed in the k-space when the MRI apparatus300aor300bobtains the third echo data E1′ and the fourth echo data E2′, are the same, the MRI apparatus300aor300bmay minimize an error caused by an echo time shift.

The MRI apparatus300aor300bmay perform phase correction on the second echo data E2and may obtain the second echo data E2C whose phase is corrected based on the first echo time TE1. The phase correction may be performed by using a B0 map generated by using the third echo data E1′ and the fourth echo data E2′.

The MRI apparatus300aor300bmay obtain the final k-space data E1+E2C based on the first echo data E1and the corrected second echo data E2C. The final k-space data E1+E2C may be k-space data reconstructed in the k-space. When the final k-space data E1+E2C is reconstructed, k-space data may be first reconstructed based on data of the first echo data E1other than the additional data525and the second echo data E2. The MRI apparatus300aor300bmay use a GRAPPA method or the like to reconstruct the k-space data. Next, the MRI apparatus300aor300bmay re-reconstruct the k-space data based on the first echo data E1including the additional data525and the corrected second echo data E2C. In this case, a GRAPPA method or the like may be re-applied to the additional data525, and the MRI apparatus300aor300bmay obtain the final k-space data E1+E2C.

According to the exemplary embodiment ofFIGS. 5A and 5B, the MRI apparatus300aor300bmay obtain the k-space data by using the first echo data E1and the second echo data E2obtained by applying gradient magnetic fields having the same sign. Likewise, the MRI apparatus300aor300bmay generate a B0 map by using the third echo data E1′ and the fourth echo data E2′ obtained by applying gradient magnetic fields having the same sign. Accordingly, the MRI apparatus300aor300bmay minimize an error of an echo time.

Also, according to the exemplary embodiment ofFIGS. 5A and 5B, the MRI apparatus300aor300bmay generate a B0 map for performing phase correction and final k-space data by using echo data obtained during one TR. Accordingly, the MRI apparatus300aor300bmay obtain data to be used for phase correction by using only a pulse sequence for obtaining k-space data without additionally using a pulse sequence for phase correction.

FIG. 6Ais a pulse sequence diagram610of a pulse sequence with an ETL of 3 applied by the MRI apparatus300aor300b, according to an exemplary embodiment.

Referring toFIG. 6A, the MRI apparatus300aor300bmay apply a gradient magnetic field620according to a multi-echo sequence shown in the pulse sequence diagram610.

The pulse sequence diagram610may show gradient magnetic fields PE1, PE2, PE2rewind, PE2+PE3, and PE rewind of a phase encoding direction and the gradient magnetic field620of a readout direction applied by the MRI apparatus300aor300baccording to an exemplary embodiment during one TR.

Referring toFIG. 6A, the MRI apparatus300aor300bmay apply the gradient magnetic field620for generating a plurality of echoes in the readout direction of a k-space as shown in the pulse sequence diagram610.

The MRI apparatus300aor300bmay generate echoes at the first echo time TE1, the second echo time TE2, the third echo time TE1′, the fourth echo time TE2′, and a fifth echo time TE3during one TR by applying the gradient magnetic field620. That is, the pulse sequence diagram610ofFIG. 6Ais different from the pulse sequence diagram510ofFIG. 5Ain that an echo corresponding to the fifth echo time TE3may be additionally generated.

The MRI apparatus300aor300bmay obtain the first echo data E1, the second echo data E2, and fifth echo data E3by using echoes generated at the first echo time TE1, the second echo time TE2, and the fifth echo time TE3included in one TR. The MRI apparatus300aor300breconstructs a final k-space by obtaining the first echo data E1, the second echo data E2, and the fifth echo data E3.

According to the exemplary embodiment ofFIG. 6A, the third echo data E1′ and the fourth echo data E2′ may be data used for phase correction, instead of data used to reconstruct final k-space data. According to another exemplary embodiment, the third echo data E1′ and the fourth echo data E2′ may include data used to reconstruct the final k-space data.

First, the MRI apparatus300aor300bmay determine a position of the first echo data E1on a ky-axis in the k-space by applying the gradient magnetic field PE1of the phase encoding direction before obtaining the first echo data E1.

After the gradient magnetic field PE1of the phase encoding direction is applied, the MRI apparatus300aor300bmay fill one line of data among the first echo data E1of the k-space in a positive direction611by using a readout gradient magnetic field corresponding to the first echo time TE1.

The MRI apparatus300aor300bmay fill one line of data among the third echo data E1′ of the k-space in a negative direction613by using a readout gradient magnetic field corresponding to the third echo time TE1′ by reversing a sign of the readout gradient magnetic field.

The MRI apparatus300aor300bmay determine a position of the second echo data E2on the ky-axis in the k-space by applying the gradient magnetic field PE2of the phase encoding direction before obtaining the second echo data E2.

The MRI apparatus300aor300bmay fill one line of data among the second echo data E2of the k-space in a positive direction615by using a readout gradient magnetic field corresponding to the second echo time TE2by re-reversing a sign of the readout gradient magnetic field.

Next, the MRI apparatus300aor300bmay apply the gradient magnetic field PE2rewind of the phase encoding direction that has the same strength and the opposite direction as and to those of the gradient magnetic field PE2of the phase encoding direction. Next, the MRI apparatus300aor30bmay fill one line of data among the fourth echo data E2′ of the k-space in a negative direction617by using a readout gradient magnetic field corresponding to the fourth echo time TE2′ by re-reversing a sign of the readout gradient magnetic field.

The MRI apparatus300aor300bmay determine a position of the fifth echo data E3on the ky-axis in the k-space by applying the gradient magnetic field PE2+PE3of the phase encoding direction.

The MRI apparatus300aor300bmay fill one line of data among the fifth echo data e3of the k-space in a positive direction619by using a readout gradient magnetic field corresponding to the fifth echo time TE3by re-reversing a sign of the readout gradient magnetic field.

Referring toFIG. 6A, the MRI apparatus300aor300bmay obtain the first echo data E1corresponding to the first echo time TE1, the second echo data E2corresponding to the second echo time TE2, the third echo data E1′ corresponding to the third echo time TE1′, the fourth echo data E2′ corresponding to the fourth echo time TE2′, and the fifth echo data E3corresponding to the fifth echo time TE3by applying the gradient magnetic field620during several TRs.

The directions611,615, and619, in which pieces of data are placed in the k-space when the MRI apparatus300aor300bobtains the first echo data E1, the second echo data E2, and the fifth echo data E3, are the same. That is, a readout gradient magnetic field applied at the first echo time TE1, a readout gradient magnetic field applied at the second echo time TE2, and a readout gradient magnetic field applied at the fifth echo time TE3have the same sign.

Referring toFIG. 6A, positions of the third echo data E1′ and the fourth echo data E2′ on the ky-axis in the k-space may be opposite to each other. Positions of the first echo data E1and the third echo data E1′ on the ky-axis may differ from each other.

The directions613and617, in which pieces of data are placed in the k-space when the MRI apparatus300aor300bobtains the third echo data E1′ and the fourth echo data E2′, are the same. If the MRI apparatus300aor300bgenerates a B0 map by using the third echo data E1′ and the fourth echo data E2′, an error caused when directions of echo time shifts differ from each other may be minimized.

As shown inFIG. 6A, the first echo data E1may include data of a central part of the k-space and the second echo data E2and the fifth echo data E3may not include the data of the central part of the k-space.

Referring toFIG. 6A, when a T1-weighted image is to be obtained, the MRI apparatus300aor300bmay determine the first echo time TE1as a reference echo time. In this case, the first echo data E1that is reference echo data may include an overlapping part in the k-space with the second echo data E2. Also, the second echo data E2may include an overlapping part in the k-space with the fifth echo data E3.

FIG. 6Bis a diagram illustrating a process performed by the MRI apparatus300aor300bto obtain an MR image, according to the pulse sequence diagram610ofFIG. 6A, according to an exemplary embodiment.

Referring toFIG. 6B, the MRI apparatus300aor300bperforms a process of reconstructing a final image based on the first echo data E1corresponding to the first echo time TE1, the second echo data E2corresponding to the second echo time TE2, and the fifth echo data E3corresponding to the fifth echo time TE3.

The MRI apparatus300aor300baccording to an exemplary embodiment may obtain the first echo data E1corresponding to the first echo time TE1, may obtain the second echo data E2corresponding to the second echo time TE2that is later than the first echo time TE1, and may obtain the fifth echo data E3corresponding to the fifth echo time TE3that is later than the second echo time TE2. Also, the MRI apparatus300aor300bmay obtain the third echo data E1′ corresponding to the third echo time TE1′ and the fourth echo data E2′ corresponding to the fourth echo time TE2′ to perform phase correction.

Referring toFIG. 6B, reference echo data may be the first echo data E1and a reference echo time may be the first echo time TE1. In this case, the first echo data E1may further include additional data625about the overlapping part in the k-space with the second echo data E2. Also, the second echo data E2may further include additional data635about the overlapping part in the k-space with the third echo data E3.

First, the MRI apparatus300aor300baccording to an exemplary embodiment may perform phase correction on the fifth echo data E3. As described with reference toFIG. 6A, because the directions613and617, in which pieces of data are placed in the k-space when the MRI apparatus300aor300bobtains the third echo data E1′ and the fourth echo data E2′ used for phase correction, are the same, an error caused by an echo time shift may be minimized.

The MRI apparatus300aor300bmay perform phase correction on the fifth echo data E3and may obtain fifth echo data E3CE2whose phase is corrected based on the second echo time TE2. The phase correction may be performed by using a B0 map generated by using the third echo data E1′ and the fourth echo data E2′.

The MRI apparatus300aor300bperforms first phase correction on the fifth echo data E3and then performs second phase correction on intermediate k-space data E2+E3CE2obtained based on the second echo data E2and the corrected fifth echo data E3CE2. The first phase correction may be performed based on a phase of the second echo data E2and the second phase correction may be performed based on a phase of the first echo data E1.

The MRI apparatus300aor300bmay obtain the intermediate k-space data E2+E3CE2based on the second echo data E2and the corrected fifth echo data E3CE2. If the second echo data E2and the fifth echo data E3are under-sampled k-space data, the intermediate k-space data E2+E3CE2may be data reconstructed by using a GRAPPA method or a SMASH method.

Also, when the intermediate k-space data E2+E3CE2is reconstructed, the MRI apparatus300aor300bmay reconstruct k-space data based on data of the second echo data E2other than the additional data635and the fifth echo data E3. The MRI apparatus300aor300bmay use a GRAPPA method or the like to reconstruct the k-space data. Next, the MRI apparatus300aor300bmay re-reconstruct the k-space data based on the second echo data E2including the additional data635and the corrected fifth echo data E3CE2. In this case, a GRAPPA method or the like may be re-applied to the additional data635, and the MRI apparatus300aor300bmay obtain the intermediate k-space data E2+E3CE2.

Next, the MRI apparatus300aor300bmay perform second phase correction on the intermediate k-space data E2+E3CE2obtained based on the second echo data E2and the corrected fifth echo data E3CE2.

The MRI apparatus300aor300bmay perform phase correction on the intermediate k-space data E2+E3CE2and may obtain intermediate k-space data (E2+E3CE2)CE1whose phase is corrected based on the first echo time TE1. The phase correction may be performed by using a B0 map generated by using the third echo data E1′ and the fourth echo data E2′.

The MRI apparatus300aor300bmay obtain final k-space data E1+(E2+E3CE2)CE1based on the first echo data E1and the corrected intermediate k-space data (E2+E3CE2)CE1. The final k-space data E1+(E2+E3CE2)CE1may be k-space data reconstructed in the k-space.

A method performed by the MRI apparatus300aor300bto reconstruct the final k-space data E1+(E2+E3CE2)CE1by using the additional data625is similar to that described with reference toFIG. 5B, and thus a detailed explanation thereof will not be given.

According to the exemplary embodiment ofFIGS. 6A and 6B, the MRI apparatus may obtain k-space data by using the first echo data E1, the second echo data E2, and the fifth echo data E3obtained by applying gradient magnetic fields having the same sign. Likewise, the MRI apparatus300aor300bmay generate a B0 map by using the third echo data E1′ and the fourth echo data E2′ obtained by applying gradient magnetic fields having the same sign. Accordingly, the MRI apparatus300aor300bmay minimize an error of an echo time.

Also, according to the exemplary embodiment ofFIGS. 6A and 6B, the MRI apparatus300aor300bmay generate a B0 map for performing phase correction and final k-space data by using echo data obtained during one TR. Accordingly, the MRI apparatus300aor300bmay obtain data to be used for phase correction by using only a pulse sequence for obtaining k-space data without additionally using a pulse sequence for phase correction.

According to the exemplary embodiments ofFIGS. 4A through 6B, when a reference echo time is determined to correspond to an early echo, the MRI apparatus300aor300bmay determine the first echo data as reference echo data.

A case where a reference echo time corresponds to a late echo will now be explained with reference toFIGS. 7A through 8B.

FIG. 7Ais a pulse sequence diagram710of a pulse sequence with an ETL of 2 applied by the MRI apparatus300aor300b, according to an exemplary embodiment.

Referring toFIG. 7A, the MRI apparatus300aor300bmay apply a gradient magnetic field720according to a multi-echo sequence shown in the pulse sequence diagram710.

In detail, the pulse sequence diagram710may show the gradient magnetic fields PE1, PE2, and PE rewind of a phase encoding direction and a gradient magnetic field720of a readout direction applied by the MRI apparatus300aor300baccording to an exemplary embodiment during one TR.

When the pulse sequence diagram710ofFIG. 7Aand the pulse sequence diagram510ofFIG. 5Aare compared to each other, the gradient magnetic field720of the readout direction may be the same as the gradient magnetic field520of the readout direction in the pulse sequence diagram510. The pulse sequence diagram710is different from the pulse sequence diagram510ofFIG. 5Ain the gradient magnetic fields PE1, PE2, and PE rewind of the phase encoding direction, and thus the following will focus on the difference.

The MRI apparatus300aor300bmay determine a position of the first echo data E1on a ky-axis in a k-space by applying the gradient magnetic field PE1of the phase encoding direction before obtaining the first echo data E1.

After the gradient magnetic field PE1of the phase encoding direction is applied, the MRI apparatus300aor300bmay fill one line of data among the first echo data E1of the k-space in a positive direction711by using a readout gradient magnetic field corresponding to the first echo time TE1. The first echo data E1may not include data whose ky-coordinate in the k-space is 0.

The MRI apparatus300aor300bmay determine a position of the third echo data E1′ on the ky-axis in the k-space by applying the gradient magnetic field PE2of the phase encoding direction before obtaining the third echo data E1′.

The MRI apparatus300aor300bmay fill one line of data among the third echo data E1′ of the k-space in a negative direction713by using a readout gradient magnetic field corresponding to the third echo time TE1′ by reversing a sign of the readout gradient magnetic field.

The MRI apparatus300aor300bmay fill one line of data among the second echo data E2of the k-space in a positive direction714by using a readout gradient magnetic field corresponding to the second echo time TE2by re-reversing a sign of the readout gradient magnetic field.

Next, the MRI apparatus300aor300bmay fill one line of data among the fourth echo data E2′ of the k-space in a negative direction715by using a readout gradient magnetic field corresponding to the fourth echo time TE2′ by re-reversing a sign of the readout gradient magnetic field.

Next, the MRI apparatus300aor300bmay apply the gradient magnetic field PE rewind of the phase encoding direction. When the MRI apparatus300aor300bapplies the gradient magnetic field PE rewind of the phase encoding direction, data of the k-space in a next TR may be placed at a position whose ky-coordinate is 0.

As shown inFIG. 7A, the MRI apparatus300aor300bmay obtain the first echo data E1not including data of a central part of the k-space at the first echo time TE1and may obtain the second echo data E2including the data of the central part of the k-space at the second echo time TE2.

Referring toFIG. 7A, when a T2 or T2*-weighted image is to be obtained, the MRI apparatus300aor300bmay determine the second echo time TE2as a reference echo time. In this case, the second echo data E2that is reference echo data may include an overlapping part in the k-space with the first echo data E1.

FIG. 7Bis a diagram illustrating a process performed by the MRI apparatus300aor300bto obtain an MR image, according to the pulse sequence diagram710ofFIG. 7A, according to an exemplary embodiment.

Referring toFIG. 7B, the MRI apparatus300aor300bperforms a process of reconstructing a final image based on the first echo data E1corresponding to the first echo time TE1and the second echo data E2corresponding to the second echo time TE2.

The MRI apparatus300aor300baccording to an exemplary embodiment may obtain the first echo data E1corresponding to the first echo time TE1and then may obtain the second echo data E2corresponding to the second echo time TE2that is later than the first echo time TE1. Also, the MRI apparatus300aor300bmay obtain the third echo data E1′ corresponding to the third echo time TE1′ and the fourth echo data E2′ corresponding to the fourth echo time TE2′.

Referring toFIG. 7B, reference echo data may be the second echo data E2and a reference echo time may be the second echo time TE2. WhenFIG. 7BandFIG. 5Bare compared with each other, there is a difference in reference echo data and a reference echo time and others inFIGS. 7B and 5Bmay be the same. Accordingly, the following will focus on the difference.

Referring toFIG. 7B, reference echo data may be the second echo data E2, and in this case, the second echo data E2may include an overlapping part in a k-space with the first echo data E1. For example, the second echo data E2may further include additional data725about the overlapping part in the k-space with the first echo data E1. The additional data725may account for, for example, about 10% of the entire k-space.

The MRI apparatus300aor300baccording to an exemplary embodiment may perform phase correction on the first echo data E1. Because the directions713and715(seeFIG. 7A), in which pieces of data are placed in the k-space when the MRI apparatus300aor300bobtains the third echo data E1′ and the fourth echo data E2′, are the same, an error caused by an echo time shift may be minimized.

The MRI apparatus300aor300bmay perform phase correction on the first echo data E1and may obtain first echo data E1C whose phase is corrected based on the second echo time TE2. The phase correction may be performed by using a B0 map generated by using the third echo data E1′ and the fourth echo data E2′.

The MRI apparatus300aor300bmay obtain final k-space data E1C+2E based on the first echo data E1and the corrected second echo data E2C. The final k-space data E1C+2E may be k-space data reconstructed in the k-space. When the final k-space data E1C+2E is reconstructed, k-space data may be reconstructed based on data of the second echo data E2other than the additional data725and the first echo data E1. The MRI apparatus300aor300bmay use a GRAPPA method or the like to reconstruct the k-space data. Next, the MRI apparatus300aor300bmay re-reconstruct the k-space data based on the second echo data E2including the additional data725and the corrected first echo data E1C. In this case, a GRAPPA method or the like may be re-applied to the additional data725, and the MRI apparatus300aor300bmay obtain the final k-space data E1C+2E.

FIG. 8Ais a pulse sequence diagram810of a pulse sequence with an ETL of 3 applied by the MRI apparatus300aor300b, according to an exemplary embodiment.

Referring toFIG. 8A, the MRI apparatus300aor300bmay apply a gradient magnetic field820according to a multi-echo sequence shown in the pulse sequence diagram810.

The pulse sequence diagram810shows the gradient magnetic fields PE1, PE2, and PE rewind of a phase encoding direction and the gradient magnetic field820of a readout direction applied by the MRI apparatus300aor300baccording to an exemplary embodiment during one TR.

Referring toFIG. 8A, the MRI apparatus300aor300bmay apply the gradient magnetic field820for generating a plurality of echoes in the readout direction of a k-space as shown in the pulse sequence diagram810. The pulse sequence diagram810ofFIG. 8Ais different from the pulse sequence diagram710ofFIG. 7Ain that an echo corresponding to the fifth echo time TE3may be additionally generated.

When the pulse sequence diagram810ofFIG. 8Aand the pulse sequence diagram710ofFIG. 7Aare compared with each other, the gradient magnetic field820of the readout direction has an ETL of 3, whereas the gradient magnetic field720of the readout direction in the pulse sequence diagram710has an ETL of 2 and there is a difference in the gradient magnetic field820of the readout direction and the gradient magnetic fields PE1, PE2, and PE rewind of the phase encoding direction, and thus the following will focus on the difference.

The MRI apparatus300aor300bmay obtain the first echo data E1, the second echo data E2, and the fifth echo data E3by using echoes generated at the first echo time TE1, the second echo time TE2, and the fifth echo time TE3included in one TR. The MRI apparatus300aor300breconstructs a final k-space by obtaining the first echo data E1, the second echo data E2, and the fifth echo data E3.

First, the MRI apparatus300aor300bmay determine a position of the first echo data E1on a ky-axis in the k-space by applying the gradient magnetic field PE1of the phase encoding direction before obtaining the first echo data E1.

After the gradient magnetic field PE1of the phase encoding direction is applied, the MRI apparatus300aor300bmay fill one line of data among the first echo data E1of the k-space in a positive direction811by using a readout gradient magnetic field corresponding to the first echo time TE1.

The MRI apparatus300aor300bmay determine a position of the second echo data E2on the ky-axis in the k-space by applying the gradient magnetic field PE2of the phase encoding direction before obtaining the second echo data E2.

The MRI apparatus300aor300bmay fill one line of data among the second echo data E2of the k-space in a positive direction813by causing a sign of the readout gradient magnetic field corresponding to the echo time TE2to be the same as that used to obtain the first echo data E1.

The MRI apparatus300aor300bmay determine a position of the third echo data E1′ on the ky-axis in the k-space by applying the gradient magnetic field PE3of the phase encoding direction before obtaining the third echo data E1′.

The MRI apparatus300aor300bmay fill one line of data among the third echo data E1′ of the k-space in a negative direction815by using a readout gradient magnetic field corresponding to the third echo time TE1′ by reversing a sign of the readout gradient magnetic field.

The MRI apparatus300aor300bmay fill one line of data among the fifth echo data E3of the k-space in a positive direction817by using a readout gradient magnetic field corresponding to the fifth echo time TE3by re-reversing a sign of the readout gradient magnetic field.

Next, the MRI apparatus300aor300bmay fill one line of data among the fourth echo data E2′ of the k-space in a negative direction819by using a readout gradient magnetic field corresponding to the fourth echo time TE2′ by re-reversing a sign of the readout gradient magnetic field.

When the MRI apparatus300aor300bapplies the gradient magnetic field PE rewind of the phase encoding direction, data of the k-space of a next TR may be placed at a position whose ky-coordinate is 0.

Referring toFIG. 8A, the MRI apparatus300aor300bmay obtain the first echo data E1corresponding to the first echo time TE1, the second echo data E2corresponding to the second echo time TE2, the third echo data E1′ corresponding to the third echo time TE1′, the fourth echo data E2′ corresponding to the fourth echo time TE2′, and the fifth echo data E3corresponding to the fifth echo time TE3by applying the gradient magnetic field820during several TRs.

The directions811,813, and817, in which pieces of data are placed in the k-space when the MRI apparatus300aor300bobtains the first echo data E1, the second echo data E2, and the fifth echo data E3, are the same. That is, a readout gradient magnetic field applied at the first echo time TE1, a readout gradient magnetic field applied at the second echo time TE2, and a readout gradient magnetic field applied at the fifth echo time TE3have the same sign.

The directions815and819, in which pieces of data are placed in the k-space when the MRI apparatus300aor300bobtains the third echo data E1′ and the fourth echo data E2′, are the same. If the MRI apparatus300aor300bgenerates a B0 map by using the third echo data E1′ and the fourth echo data E2′, an error caused when directions of echo time shifts differ from each other may be minimized.

As shown inFIG. 8A, the fifth echo data E3may include data of a central part of the k-space, and the first echo data E1and the second echo data E2may not include the data of the central part of the k-space.

Referring toFIG. 8A, when a T2 or T2*-weighted image is to be obtained, the MRI apparatus300aor300bmay determine the fifth echo time TE3as a reference echo time. In this case, the fifth echo data E3that is reference echo data may include an overlapping part in the k-space with the second echo data E2. Also, the second echo data E2may include an overlapping part in the k-space with the first echo data E1.

FIG. 8Bis a diagram illustrating a process performed by the MRI apparatus300aor300bto obtain an MR image, according to the pulse sequence diagram810ofFIG. 8A, according to an exemplary embodiment.

Referring toFIG. 8B, the MRI apparatus300aor300bperforms a process of reconstructing a final image based on the first echo data E1corresponding to the first echo time TE1, the second echo data E2corresponding to the second echo time TE2, and the fifth echo data E3corresponding to the fifth echo time TE3.

The MRI apparatus300aor300baccording to an exemplary embodiment may obtain the first echo data E1corresponding to the first echo time TE1, may obtain the second echo data E2corresponding to the second echo time TE2that is later than the first echo time TE1, and may obtain the fifth echo data E3corresponding to the fifth echo time TE3that is later than the second echo time TE2. Also, the MRI apparatus300aor300bmay obtain the third echo data E1′ corresponding to the third echo time TE1′ and the fourth echo data E2′ corresponding to the fourth echo time TE2′ to perform phase correction.

Referring toFIG. 8B, reference echo data may be the fifth echo data E3and a reference echo time may be the fifth echo time TE3. In this case, the fifth echo data E3may further include additional data825about the overlapping part in the k-space with the second echo data E2. Also, the second echo data E2may further include additional data835about the overlapping part in the k-space with the first echo data E1.

First, the MRI apparatus300aor300baccording to an exemplary embodiment may perform phase correction on the first echo data E1. As described with reference toFIG. 6A, because the directions815and819, in which pieces of data are placed in the k-space when the MRI apparatus300aor300bobtains the third echo data E1′ and the fourth echo data E2′, are the same, an error caused by an echo time shift may be minimized.

The MRI apparatus300aor300bmay perform phase correction on the first echo data E1and may obtain first echo data E1CE2whose phase is corrected based on the second echo time TE2. The phase correction may be performed by using a B0 map generated by using the third echo data E1′ and the fourth echo data E2′.

The MRI apparatus300aor300bperforms first phase correction on the first echo data E1and then performs second phase correction on intermediate k-space data E2+E1CE2obtained based on the second echo data E2and the corrected first echo data E1CE2. The first phase correction may be performed based on a phase of the second echo data E2and the second phase correction may be performed based on a phase of the fifth echo data E3.

The MRI apparatus300aor300bmay obtain the intermediate k-space data E2+E1CE2based on the second echo data E2and the corrected first echo data E1CE2. If the second echo data E2and the fifth echo data E3are under-sampled k-space data, the intermediate k-space data E2+E1CE2may be data reconstructed by using a GRAPPA method or a SMASH method.

Also, when the intermediate k-space data E2+E1CE2is reconstructed, the MRI apparatus300aor300bmay reconstruct k-space data based on data of the second echo data E2other than the additional data835and the fifth echo data E3. The MRI apparatus300aor300bmay use a GRAPPA method or the like to reconstruct k-space data. Next, the MRI apparatus may re-reconstruct the k-space data based on the second echo data E2including the additional data835and the corrected first echo data E1CE2. In this case, a GRAPPA method or the like may be re-applied to the additional data835, and the MRI apparatus300aor300bmay obtain the intermediate k-space data E2+E1CE2.

Next, the MRI apparatus300aor300bmay perform second phase correction on the intermediate k-space data E2+E1CE2obtained based on the second echo data E2and the corrected first echo data E1CE2.

The MRI apparatus300aor300bmay perform phase correction on the intermediate k-space data E2+E1CE2and may obtain intermediate k-space data (E2+E1CE2)CE3whose phase is corrected based on the fifth echo time TE3. The phase correction may be performed by using a B0 map generated by using the third echo data E1′ and the fourth echo data E2′.

The MRI apparatus300aor300bmay obtain final k-space data E3+(E2+E1CE2)CE3based on the first echo data E1and the corrected intermediate k-space data (E2+E1CE2)CE3. The final k-space data E3+(E2+E1CE2)CE3may be k-space data reconstructed in the k-space.

A method performed by the MRI apparatus300aor300bto reconstruct the final k-space data E3+(E2+E1CE2)CE3by using the additional data825is similar to that described with reference toFIG. 7B, and thus an explanation thereof will not be given.

FIG. 9Ais a diagram illustrating the first echo data E1and the second echo data E2obtained by the MRI apparatus300aor300b.

In detail,FIG. 9Aillustrates the first echo data E1that is under-sampled and the second echo data E2that is under-sampled in a k-space.

Referring toFIG. 9A, a data line that is actually obtained is marked by a solid line. Also, a data line to be constructed by using a GRAPPA method is marked by a dashed line. Also, an auto calibrating signal (ACS) may be obtained at a position whose ky-coordinate in the k-space is close to 0. For example, a line905marked by a thick solid line may be an ACS line.

Also, each of first through fourth kernels911,913,915, and917ofFIG. 9Amay be a kernel having a size of 2*5. That is, the MRI apparatus300aor300bmay use a GRAPPA method by using a correlation between 2*5 pieces of data included in the first through fourth kernels911,913,915, and917.

Referring toFIG. 9A, the first kernel911and the fourth kernel917may include only the first echo data E1. Also, the second kernel913may include only the second echo data E2. The third kernel915may include both the first echo data E1and the second echo data E2.

The accuracy of reconstructed data when the MRI apparatus300aor300buses a GRAPPA method based on the third kernel915including pieces of data obtained by using different echoes, that is, the first echo data E1and the second echo data E2, may be lower than that when the MRI apparatus300aor300buses a GRAPPA method based on the first kernel911, the second kernel913, and the fourth kernel917including pieces of echo data obtained by using the same echo.

A case where additional data about an overlapping part between the first echo data E1and the second echo data E2is used to improve the accuracy of reconstructed data based on the third kernel915will now be explained with reference toFIG. 9B.

FIG. 9Bis a diagram illustrating a process of reconstructing k-space data by applying a GRAPPA method to the first echo data E1and the second echo data E2obtained by the MRI apparatus300aor300b, according to an exemplary embodiment.

InFIG. 9B, a diagram910shows the first echo data E1that is under-sampled and the second echo data E2that is under-sampled. The diagram910ofFIG. 9Billustrates a part of the first echo data E1that is under-sampled other than additional data about an overlapping part in a k-space with the second echo data E2. Also, a diagram920ofFIG. 9Billustrates pieces of additional data922and924of the first echo data E1that is under-sampled.

First, as shown in a diagram930ofFIG. 9B, the MRI apparatus300aor300bmay obtain reconstructed k-space data based on the first echo data E1that is under-sampled and the second echo data E2that is under-sampled. For example, the MRI apparatus300aor300bmay obtain the reconstructed k-space data by applying a GRAPPA method to the first echo data E1that is under-sampled and the second echo data E2that is under-sampled.

Next, as shown in a diagram940ofFIG. 9B, the MRI apparatus300aor300bmay perform phase correction on the second echo data E2of the diagram930and may obtain the corrected second echo data E2C.

Next, as shown in a diagram950ofFIG. 9B, the MRI apparatus300aor300bmay apply a GRAPPA method to pieces of additional data952and954.

The pieces of additional data952and954shown in the diagram950ofFIG. 9Bmay correspond to the pieces of additional data922and924of the diagram920. Also, the pieces of additional data952and954of the diagram950ofFIG. 9Bmay correspond to data having a low accuracy among the reconstructed k-space data of the diagram930. As shown in the diagram950ofFIG. 9B, when a GRAPPA method is re-used based on the pieces of additional data952and954, the accuracy of the reconstructed k-space data may be improved.

The additional data952of the diagram950ofFIG. 9Bmay be the first echo data E1that is under-sampled. That is, the additional data952may include a data line955that is actually obtained and a data line953to which a GRAPPA method is applied. Although the pieces of additional data952and954are shown as two lines inFIG. 9B, the pieces of additional data952and954may account for about 10% of an entire k-space data line. The additional data954of the diagram950ofFIG. 9Bmay also be the first echo data E1that is under-sampled, like the additional data952.

As shown in the diagram950, when GRAPPA is applied to the pieces of additional data952and954, data lines located over and under the pieces of additional data952and954may be further used in consideration of a size of a kernel. For example, data lines of the diagram940ofFIG. 9Bmay be located over and under the pieces of additional data952and954.

For example, a data line951located under the additional data952may correspond to a data line941of the diagram940ofFIG. 9B, and a data line957located over the additional data952may correspond to a data line947of the diagram940ofFIG. 9B. Likewise, data lines of the diagram940ofFIG. 9Bmay also be located over and under the additional data954.

Referring to a diagram960ofFIG. 9B, the MRI apparatus300aor300bmay obtain pieces of reconstructed additional data962and964by applying a GRAPPA method to the pieces of additional data952and954of the diagram950. Data lines963and969obtained after applying a GRAPPA method to the pieces of reconstructed additional data962and964of the diagram960ofFIG. 9Bmay correspond to data lines953and959of the pieces of additional data952and954of the diagram950.

Referring to a diagram970ofFIG. 9B, the MRI apparatus300aor300bmay obtain final k-space data by replacing first echo data942and944corresponding to additional data among data lines of the diagram940ofFIG. 9Bwith the pieces of reconstructed additional data962and964.

FIG. 10Ais a diagram illustrating the first echo data E1and the second echo data E2obtained by the MRI apparatus300aor300b, using a multi-band method.

In detail,FIG. 10Aillustrates the first echo data E1and the second echo data E2, which are obtained by using a multi-band method, on a ky-axis and a kz-axis. Data of a kx-axis is not shown. Echo data obtained by using a multi-band method refers to k-space data about two slices having different z-coordinates. For example, echo data obtained by using a multi-band method may be a sum of pieces of k-space data about two slices, or a difference between pieces of k-space data about two slices. When echo data obtained by using a multi-band method is reconstructed by using a GRAPPA method, a final image of two slices may be reconstructed by reconstructing two lines of data in the kz-axis.

Referring toFIG. 10A, a part O is a part that obtains data and a part X is a part that does not obtain data. Also, a part A is an ACS.

In detail, the part O ofFIG. 10Ais a part including both pieces of data about two slices obtained by using a multi-band method.

Also, the part X ofFIG. 10Amay be a part that has to obtain data by using a GRAPPA method. The part X ofFIG. 10Amay be obtained by using a correlation between pieces of data included in, for example, a kernel of 2*1.

Referring toFIG. 10A, a first kernel1011may include only the first echo data E1. Also, a second kernel1015may include only the second echo data E2. A third kernel1019may include both the first echo data E1and the second echo data E2.

The accuracy of reconstructed data when the MRI apparatus300aor300buses a GRAPPA method based on the third kernel1019including echo data obtained by using different echoes, that is, both the first echo data E1and the second echo data E2, may be lower than that when the MRI apparatus300aor300buses a GRAPPA method based on the first kernel1011and the second kernel1015including echo data obtained by using the same echo.

A case where additional data about an overlapping part between the first echo data E1and the second echo data E2is used to improve the accuracy of data reconstructed based on the third kernel1019will now be explained with reference toFIG. 10B.

FIG. 10Bis a diagram illustrating a process of reconstructing k-space data by applying a GRAPPA method to the first echo data E1and the second echo data E2obtained by the MRI apparatus300aor300b, using a multi-band method, according to an exemplary embodiment.

A diagram1010ofFIG. 10Bshows the first echo data E1and the second echo data E2obtained by using a multi-band method. The diagram1010ofFIG. 10Billustrates data of the first echo data E1, which is obtained by using a multi-band method, other than additional data about an overlapping part in a k-space with the second echo data E2. Also, a diagram1020ofFIG. 10Billustrates pieces of additional data1022and1024of the first echo data E1obtained by using a multi-band method.

First, as shown in a diagram1030ofFIG. 10B, the MRI apparatus300aor300bmay obtain reconstructed k-space data based on the first echo data E1and the second echo data E2obtained by using a multi-band method. A part O ofFIG. 10Bis a part including both pieces of data about two slices obtained by using a multi-band method.

For example, the MRI apparatus300aor300bmay obtain reconstructed k-space data by applying a GRAPPA method to the first echo data E1and the second echo data E2obtained by using a multi-band method. In this case, the MRI apparatus300aor300bmay reconstruct k-space data about a part X of the diagram1010by using a kernel1031having a size of 2*1. Referring to the diagram1030ofFIG. 10B, a part o is a part indicating k-space data reconstructed by using echo data obtained by using the same echo. Also, a part c is a part indicating k-space data reconstructed by using echo data obtained by using different echoes.

Next, as shown in a diagram1040ofFIG. 10B, the MRI apparatus300aor300bmay perform phase correction on the second echo data E2of the diagram1030and may obtain the corrected second echo data E2C.

Next, as shown in a diagram1050ofFIG. 10B, the MRI apparatus300aor300bmay apply a GRAPPA method to pieces of additional data1052and1054.

The pieces of additional data1052and1054shown in the diagram1050ofFIG. 10Bmay correspond to the pieces of additional data1022and1024of the diagram1020. Also, the pieces of additional data1052and1054ofFIG. 10Bmay correspond to data having a low accuracy among the reconstructed k-space data of the diagram1030. As shown in the diagram1050ofFIG. 10B, when a GRAPPA method is re-applied to the pieces of additional data1052and1054, the accuracy of the reconstructed k-space data may be improved.

The pieces of additional data1052and1054of the diagram1050ofFIG. 10Bmay be the first echo data E1obtained by using a multi-band method. Also, the pieces of additional data1052and1054may include a part X to which a GRAPPA method is to be applied and a part O that is actually obtained. Although the pieces of additional data1052and1054are shown as one line inFIG. 10B, the pieces of additional data1052and1054may correspond to a data line that actually accounts for about 10% of the entire k-space.

As shown in the diagram1050, when a GRAPPA method is applied to the pieces of additional data1052and1054, pieces of data located over and under the pieces of additional data1052and1054may be further used in consideration of a size of a kernel. For example, pieces of data of the diagram1040ofFIG. 10Bmay be located over and under the pieces of additional data1052and1054.

For example, pieces of data1051and1053located under the additional data1052may correspond to pieces of data1041and1043of the diagram1040ofFIG. 10B, and data1055located over the additional data1052may correspond to data1045of the diagram1040ofFIG. 10B. Likewise, pieces of data of the diagram1040ofFIG. 10Bmay also be located over and under the additional data1054.

Referring to a diagram1060ofFIG. 10B, the MRI apparatus300aor300bmay obtain pieces of additional data1062and1064reconstructed by applying a GRAPPA method to the pieces of additional data1052and1054of the diagram1050. The pieces of reconstructed additional data1062and1064of the diagram1060ofFIG. 10Bmay be obtained by using a correlation between pieces of data included in a kernel1061shown in the diagram1060ofFIG. 10B. The reconstructed additional data1062may include k-space data reconstructed by using echo data obtained by using the same echo and the reconstructed additional data1064may include k-space data reconstructed by using echo data obtained by using different echoes.

Referring to a diagram1070ofFIG. 10B, the MRI apparatus300aor300bmay obtain final k-space data by replacing at least parts of pieces of data1042and1044including additional data among pieces of data of the diagram1040ofFIG. 10Bwith the pieces of reconstructed additional data1062and1064. That is, parts of data1072and1074of the final k-space data may correspond to the pieces of additional data1062and1064.

FIG. 11is a flowchart illustrating a method of an MRI apparatus, according to an exemplary embodiment.

The method according to an exemplary embodiment may be performed by the MRI apparatus300aor300b. Also, the method according to an exemplary embodiment may be a method of obtaining an MR image by using a multi-echo sequence.

In operation S110, the MRI apparatus300aor300bmay obtain the first echo data E1and the second echo data E2including an overlapping part in a k-space.

In detail, the MRI apparatus300aor300bmay obtain the first echo data E1by using an echo generated at the first echo time TE1and may obtain the second echo data E2by using an echo generated at the second echo time TE2that is later than the first echo time TE1.

In operation S120, the MRI apparatus300aor300bmay reconstruct an MR image based on the first echo data E1and the second echo data E2.

FIG. 12is a flowchart illustrating another method of an MRI apparatus, according to an exemplary embodiment.

The method according to an exemplary embodiment may be performed by the MRI apparatus300aor300b. The MRI apparatus300aor300bperforms phase correction on echo data obtained by using different echoes.

In operation S210, the MRI apparatus300aor300bmay obtain the first echo data E1and the second echo data E2including an overlapping part in a k-space.

In operation S220, the MRI apparatus300aor300bmay reconstruct k-space data based on a part of the first echo data E1other than additional data and the second echo data E2.

In operation S230, the MRI apparatus300aor300bmay perform phase correction on the second echo data E2included in the reconstructed k-space data.

In operation S240, the MRI apparatus300aor300bmay re-reconstruct the k-space data based on the additional data of the first echo data E1and the second echo data E2C whose phase is corrected.

FIG. 13is a flowchart illustrating another method of an MRI apparatus, according to an exemplary embodiment.

The method according to an exemplary embodiment may be performed by the MRI apparatus300aor300b.

In operation S310, the MRI apparatus300aor300bmay determine characteristics of an MR image.

In operation S320, the MRI apparatus300aor300bmay determine that the first echo data E1or the second echo data E2is to include data of a central part of a k-space according to the determined characteristics of the MR image.

In operation S330, the MRI apparatus300aor300bmay obtain the first echo data E1and the second echo data E2including an overlapping part in the k-space.

In detail, the MRI apparatus300aor300bmay obtain the first echo data E1by using an echo generated at the first echo time TE1and may obtain the second echo data E2by using an echo generated at the second echo time TE2that is later than the first echo time TE1.

In operation S340, the MRI apparatus300aor300bmay reconstruct k-space data based on the first echo data E1and the second echo data E2.

FIG. 14is a flowchart illustrating another method of an MRI apparatus, according to an exemplary embodiment.

The method according to an exemplary embodiment may be performed by the MRI apparatus300aor300b.

In operation S410, the MRI apparatus300aor300bmay obtain the first echo data E1, the second echo data E2, and the fifth echo data E3.

In operation S420, the MRI apparatus300aor300bmay perform phase correction on the fifth echo data E3.

In operation S430, the MRI apparatus300aor300bmay obtain the intermediate k-space data E2+E3CE2based on the second echo data E2and the fifth echo data E3CE2whose phase is corrected.

In operation S440, the MRI apparatus300aor300bmay perform phase correction on the intermediate k-space data E2+E3CE2to obtain the corrected intermediate k-space data (E2+E3CE2)CE1.

In operation S450, the MRI apparatus300aor300bmay reconstruct k-space data based on the first echo data E1and the corrected intermediate k-space data (E2+E3CE2)CE1.

FIG. 15is a block diagram of a general MRI system. Referring toFIG. 15, the general MRI system may include a gantry20, a signal transceiver30, a monitor40, a system controller50, and an operating portion60.

The gantry20prevents external emission of electromagnetic waves generated by a main magnet22, a gradient coil24, and an RF coil26. A magnetostatic field and a gradient magnetic field are formed in a bore in the gantry20, and an RF signal is emitted toward an object10.

The main magnet22, the gradient coil24, and the RF coil26may be arranged in a predetermined direction of the gantry20. The predetermined direction may be a coaxial cylinder direction. The object10may be disposed on a table28that is capable of being inserted into a cylinder along a horizontal axis of the cylinder.

The main magnet22generates a magnetostatic field or a static magnetic field for aligning magnetic dipole moments of atomic nuclei of the object10in a constant direction. A precise and accurate MR image of the object10may be obtained due to a magnetic field generated by the main magnet22being strong and uniform.

The gradient coil24includes X, Y, and Z coils for generating gradient magnetic fields in X-, Y-, and Z-axis directions crossing each other at right angles. The gradient coil24may provide location information of each region of the object10by differently inducing resonance frequencies according to the regions of the object10.

The RF coil26may emit an RF signal toward a patient and receive an MR signal emitted from the patient. In detail, the RF coil26may transmit, toward atomic nuclei included in the patient and having precessional motion, an RF signal having the same frequency as that of the precessional motion, stop transmitting the RF signal, and then receive an MR signal emitted from the atomic nuclei included in the patient.

For example, to transit an atomic nucleus from a low energy state to a high energy state, the RF coil26may generate and apply an electromagnetic wave signal that is an RF signal corresponding to a type of the atomic nucleus, to the object10. When the electromagnetic wave signal generated by the RF coil26is applied to the atomic nucleus, the atomic nucleus may transit from the low energy state to the high energy state. Then, when electromagnetic waves generated by the RF coil26disappear, the atomic nucleus to which the electromagnetic waves were applied transits from the high energy state to the low energy state, thereby emitting electromagnetic waves having a Lamor frequency. In other words, when the applying of the electromagnetic wave signal to the atomic nucleus is stopped, an energy level of the atomic nucleus is changed from a high energy level to a low energy level, and thus the atomic nucleus may emit electromagnetic waves having a Lamor frequency. The RF coil26may receive electromagnetic wave signals from atomic nuclei included in the object10.

The RF coil26may be realized as one RF transmitting and receiving coil having both a function of generating electromagnetic waves each having an RF that corresponds to a type of an atomic nucleus and a function of receiving electromagnetic waves emitted from an atomic nucleus. Alternatively, the RF coil26may be realized as a transmission RF coil having a function of generating electromagnetic waves each having an RF that corresponds to a type of an atomic nucleus, and a reception RF coil having a function of receiving electromagnetic waves emitted from an atomic nucleus.

The RF coil26may be fixed to the gantry20or may be detachable. When the RF coil26is detachable, the RF coil26may be an RF coil for a part of the object10, such as a head RF coil, a chest RF coil, a leg RF coil, a neck RF coil, a shoulder RF coil, a wrist RF coil, or an ankle RF coil.

The RF coil26may communicate with an external apparatus via wires and/or wirelessly, and may also perform dual tune communication according to a communication frequency band.

The RF coil26may be a birdcage coil, a surface coil, or a transverse electromagnetic (TEM) coil according to structures.

The RF coil26may be a transmission exclusive coil, a reception exclusive coil, or a transmission and reception coil according to methods of transmitting and receiving an RF signal.

The RF coil26may be an RF coil having various numbers of channels, such as 16 channels, 32 channels, 72 channels, and 144 channels.

The gantry20may further include a display29disposed outside the gantry20and a display disposed inside the gantry20. The gantry20may provide predetermined information to the user or the object10through the display29and the display respectively disposed outside and inside the gantry20.

The signal transceiver30may control the gradient magnetic field formed inside the gantry20, i.e., in the bore, according to a predetermined MR sequence, and control transmission and reception of an RF signal and an MR signal.

The signal transceiver30may include a gradient amplifier32, a transmission and reception switch34, an RF transmitter36, and an RF receiver38.

The gradient amplifier32drives the gradient coil24included in the gantry20, and may supply a pulse signal for generating a gradient magnetic field to the gradient coil24under the control of a gradient magnetic field controller54. By controlling the pulse signal supplied from the gradient amplifier32to the gradient coil24, gradient magnetic fields in X-, Y-, and Z-axis directions may be synthesized.

The RF transmitter36and the RF receiver38may drive the RF coil26. The RF transmitter36may supply an RF pulse in a Lamor frequency to the RF coil26, and the RF receiver38may receive an MR signal received by the RF coil26.

The transmission and reception switch34may adjust transmitting and receiving directions of the RF signal and the MR signal. For example, the transmission and reception switch34may emit the RF signal toward the object10through the RF coil26during a transmission mode, and receive the MR signal from the object10through the RF coil26during a reception mode. The transmission and reception switch34may be controlled by a control signal output by an RF controller56.

The signal transceiver30ofFIG. 15may include the data obtainer310ofFIG. 3Aor the data obtainer315ofFIG. 3B. For example, the data obtainer310ofFIG. 3Aor the data obtainer315ofFIG. 3Bmay be connected to the RF receiver38included in the signal transceiver30, and may receive an MR signal from the RF receiver38.

According to an exemplary embodiment, the signal transceiver30may obtain the first echo data E1and the second echo data E2by using the MR signal received through the RF receiver38.

The monitor40may monitor or control the gantry20or devices mounted on the gantry20. The monitor40may include a system monitor42, an object monitor44, a table controller46, and a display controller48.

The system monitor42may monitor and control a state of the magnetostatic field, a state of the gradient magnetic field, a state of the RF signal, a state of the RF coil26, a state of the table28, a state of a device measuring body information of the object10, a power supply state, a state of a thermal exchanger, and a state of a compressor.

The object monitor44monitors a state of the object10. In detail, the object monitor44may include a camera for observing a movement or position of the object10, a respiration measurer for measuring the respiration of the object10, an electrocardiogram (ECG) measurer for measuring the electrical activity of the object10, or a temperature measurer for measuring a temperature of the object10.

The table controller46controls a movement of the table28where the object10is positioned. The table controller46may control the movement of the table28according to a sequence control of the system controller50. For example, during moving imaging of the object10, the table controller46may continuously or discontinuously move the table28according to the sequence control of the system controller50, and thus the object10may be imaged in a field of view (FOV) larger than that of the gantry20.

The display controller48controls the display29disposed outside the gantry20and the display disposed inside the gantry20. In detail, the display controller48may control the display29and the display to be on or off, and may control a screen image to be output on the display29and the display. Also, when a speaker is located inside or outside the gantry20, the display controller48may control the speaker to be on or off, or may control sound to be output via the speaker.

The system controller50may include a sequence controller52for controlling a sequence of signals formed in the gantry20, and a gantry controller58for controlling the gantry20and the devices mounted on the gantry20.

The sequence controller52may include the gradient magnetic field controller54for controlling the gradient amplifier32, and the RF controller56for controlling the RF transmitter36, the RF receiver38, and the transmission and reception switch34. The sequence controller52may control the gradient amplifier32, the RF transmitter36, the RF receiver38, and the transmission and reception switch34according to a pulse sequence received from the operating portion60. Here, the pulse sequence includes all information used to control the gradient amplifier32, the RF transmitter36, the RF receiver38, and the transmission and reception switch34. For example, the pulse sequence may include information about a strength, an application time, and application timing of a pulse signal applied to the gradient coil24.

The operating portion60may request the system controller50to transmit pulse sequence information while controlling an overall operation of the MRI system.

The operating portion60may include an image processor62for receiving and processing the MR signal received by the RF receiver38, an output interface64, and an input interface66.

The image processor62may process the MR signal received from the RF receiver38to generate MR image data of the object10.

The image processor62receives the MR signal received by the RF receiver38and performs any one or any combination of various signal processes, such as amplification, frequency transformation, phase detection, low frequency amplification, and filtering, on the received MR signal.

The image processor62may arrange digital data in a k-space (for example, also referred to as a Fourier space or a frequency space) of a memory, and rearrange the digital data into image data via 2D or 3D Fourier transformation.

The image processor62may perform a composition process or a difference calculation process on the image data. The composition process may include an addition process on a pixel or a maximum intensity projection (MIP) process. The image processor62may store not only the rearranged image data but also image data on which a composition process or a difference calculation process is performed, in a memory or an external server.

The image processor62may perform any of the signal processes on the MR signal in parallel. For example, the image processor62may perform a signal process on a plurality of MR signals received by a multi-channel RF coil in parallel to rearrange the plurality of MR signals into image data.

The image processor62ofFIG. 15may include the image processor320ofFIG. 3Aor the image processor325ofFIG. 3B. For example, the image processor62may reconstruct an MR image by using the first echo data E1and the second echo data E2obtained by the signal transceiver30.

The output interface64may output image data generated or rearranged by the image processor62to the user. The output interface64may also output information used for the user to manipulate the MRI system, such as a UI, user information, or object information. The output interface64may be a speaker, a printer, a CRT display, an LCD, a PDP display, an OLED display, an FED, an LED display, a VFD, a DLP display, an FPD, a 3D display, a transparent display, or any one or any combination of other various output devices that are well known to one of ordinary skill in the art.

The output interface64ofFIG. 15may include the output interface340ofFIG. 15.

The user may input object information, parameter information, a scan condition, a pulse sequence, or information about image composition or difference calculation by using the input interface66. The input interface66may be a keyboard, a mouse, a track ball, a voice recognizer, a gesture recognizer, a touch screen, or any one or any combination of other various input devices that are well known to one of ordinary skill in the art.

The signal transceiver30, the monitor40, the system controller50, and the operating portion60are separate components inFIG. 15, but respective functions of the signal transceiver30, the monitor40, the system controller50, and the operating portion60may be performed by another component. For example, the image processor62converts the MR signal received from the RF receiver38into a digital signal, but alternatively, the conversion of the MR signal into the digital signal may be performed by the RF receiver38or the RF coil26.

The gantry20, the RF coil26, the signal transceiver30, the monitor40, the system controller50, and the operating portion60may be connected to each other by wire or wirelessly, and when they are connected wirelessly, the MRI system may further include an apparatus for synchronizing clock signals therebetween. Communication between the gantry20, the RF coil26, the signal transceiver30, the monitor40, the system controller50, and the operating portion60may be performed by using a high-speed digital interface, such as low voltage differential signaling (LVDS), asynchronous serial communication, such as a universal asynchronous receiver transmitter (UART), a low-delay network protocol, such as error synchronous serial communication or a controller area network (CAN), or optical communication.

FIG. 16is a block diagram of a communication interface70according to an exemplary embodiment. Referring toFIG. 16, the communication interface70may be connected to at least one selected from the gantry20, the signal transceiver30, the monitor40, the system controller50, and the operating portion60ofFIG. 15.

The communication interface70may transmit and receive data to and from a hospital server or another medical apparatus in a hospital, which is connected through a picture archiving and communication system (PACS), and perform data communication according to the digital imaging and communications in medicine (DICOM) standard.

As shown inFIG. 16, the communication interface70may be connected to a network80by wire or wirelessly to communicate with a server92, a medical apparatus94, or a portable device96.

In detail, the communication interface70may transmit and receive data related to the diagnosis of an object through the network80, and may also transmit and receive a medical image captured by the medical apparatus94, such as a CT apparatus, an MRI apparatus, or an X-ray apparatus. In addition, the communication interface70may receive a diagnosis history or a treatment schedule of the object from the server92and use the same to diagnose the object. The communication interface70may perform data communication not only with the server92or the medical apparatus94in a hospital, but also with the portable device96, such as a mobile phone, a personal digital assistant (PDA), or a laptop of a doctor or patient.

Also, the communication interface70may transmit information about a malfunction of the MRI system or about medical image quality to a user through the network80, and receive a feedback regarding the information from the user.

The communication interface70may include at least one component enabling communication with an external apparatus.

For example, the communication interface70may include a local area communication interface72, a wired communication interface74, and a wireless communication interface76. The local area communication interface72refers to an interface for performing local area communication with an apparatus within a predetermined distance. Examples of local area communication technology according to an exemplary embodiment include, but are not limited to, a wireless local area network (LAN), Wi-Fi, Bluetooth, ZigBee, Wi-Fi direct (WFD), ultra wideband (UWB), infrared data association (IrDA), Bluetooth low energy (BLE), and near field communication (NFC).

The wired communication interface74refers to an interface for performing communication by using an electric signal or an optical signal. Examples of wired communication technology according to an exemplary embodiment include wired communication techniques using a pair cable, a coaxial cable, and an optical fiber cable, and other well known wired communication techniques.

The wireless communication interface76transmits and receives a wireless signal to and from at least one selected from a base station, an external apparatus, and a server in a mobile communication network. Here, the wireless signal may be a voice call signal, a video call signal, or data in any one or any combination of various formats according to transmission and reception of a text/multimedia message.

The server92, the medical apparatus94, or the portable device96connected to the MRI system may be, for example, the MRI apparatus300aor300bofFIG. 3A or 3B. That is, the communication interface70ofFIG. 16may be connected to the MRI apparatus300aor300b.

The MRI apparatus according to the one or more embodiments may improve the quality of a reconstructed final image by obtaining additional data about an overlapping part between first echo data and second echo data obtained at different echo times in a k-space.

Also, the MRI apparatus according to the one or more embodiments may reduce the effects of blur or aliasing that may occur in a final image as pieces of data obtained at different echo times are used by performing phase correction on first echo data and second echo data obtained at different echo times.

The above-described embodiments of the present disclosure may be written as computer programs and may be implemented in general-use digital computers that execute the programs using a computer-readable recording medium.

Examples of the computer-readable recording medium include magnetic storage media (e.g., read-only memories (ROMs), floppy disks, hard disks, etc.), optical recording media (e.g., compact disk (CD)-ROMs, or digital versatile disks (DVDs), etc.), and transmission media such as Internet transmission media.

While the present disclosure has been shown and described with reference to embodiments thereof, it will be understood by one of ordinary skill in the art that various changes in form and details may be made therein without departing from the spirit and accordingly, the above embodiments and all aspects thereof are examples only and are not limiting.