JP2007014813A - Nuclear magnetic resonance imaging apparatus - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To rapidly provide an image effective for diagnosis without deterioration of image quality by enabling a parallel nuclear magnetic resonance imaging method to be applied to an image with a movement. <P>SOLUTION: A plurality of reception coils including spatially and partially overlapped and respectively divided detection sensitivity areas is used in an MRI apparatus, where the collection of measurement data and the subsequent reconstitution of the image are continuously performed so as to obtain a plurality of temporally continuous images. In this case, imaging is performed by thinning a part of the measurement data so as to allow a low frequency area to be dense and a high frequency area to be thin in a k-space. A signal is synthesized by using the substantial sensitivity distribution of each reception RF coil, which is calculated based on a densely measured part of the k-space and the measurement data, so that a high resolution image with a return excluded therefrom is acquired. <P>COPYRIGHT: (C)2007,JPO&INPIT

Description

  The present invention continuously measures nuclear magnetic resonance (hereinafter referred to as "NMR") signals from hydrogen, phosphorus, etc. in a subject and visualizes nuclear density distribution, relaxation time distribution, etc. (MRI) relates to equipment.

  In recent years, high-sensitivity coils called “multiple RF coils” or “phased array coils” have begun to be frequently used as receiving coils for detecting NMR signals generated from a subject in an MRI apparatus (Patent Document 1, etc.). Multiple RF coils are arranged with multiple relatively high-sensitivity small RF coils, and the signals received by each RF coil are combined to expand the field of view and maintain high sensitivity while maintaining the high sensitivity of the small RF coils. Various RF coils are proposed according to the static magnetic field method and the detection site.

  On the other hand, in recent years, methods have been proposed for shortening the imaging time by thinning out data in the phase encoding direction using multiple coils (for example, Non-Patent Document 1, Non-Patent Document 2, etc.). Such a technique is called a spatial encoding method, or parallel MRI, and removes aliasing when phase-encoded data is thinned using the fact that sensitivity distributions of multiple RF coils are spatially different from each other. This removal requires high-precision calculations using high-precision RF coil sensitivity distribution. In the method described in Non-Patent Document 1 above, this calculation is performed in the measurement space (k space), and in the method described in Non-Patent Document 2, the calculation is performed in the real space after Fourier transform.

In general, the sensitivity distribution of the RF coil can be obtained from each RF received signal. Specifically, a method in which a uniform phantom is projected in advance and the spatial shading of the image is the sensitivity distribution of the RF coil. A method of calculating by applying a low-frequency filter to an image obtained by separately photographing a specimen is known.
Japanese National Patent Publication No. 2-500195 Daniel K Sodickson, Warren JManning "Simultaneous acquisition of spatial harmonics (SMASH): fast imaging with radiofrequency coil arrays" Magnetic Resonance in Medicine 38,591-603, (1997) J.Wang, A.Reykowski "A SMASH / SENSE related method using ratios of array coil profiles" ISMRM 99

  The processing for obtaining the sensitivity distribution of the RF coil is usually performed prior to imaging. Therefore, for example, when the shape of the subject fluctuates with time due to breathing in the abdomen, the shape of the subject may differ between the time when the sensitivity distribution is calculated and the time of actual imaging. As a result, the spatial arrangement of the RF coil that is in close contact with the subject may change. Also, when taking an image during surgery, the position of the RF coil may change from moment to moment.

  In such shooting that requires real-time display of a shot image, the conventional method using sensitivity data acquired in advance introduces an error and deteriorates image quality. In addition, measuring the sensitivity distribution of the RF coil in advance prior to shooting extends the total shooting time and reduces the effect of short-time shooting, which is a feature of the present technology.

In order to solve the above problems, the MRI apparatus of the present invention includes means for irradiating a subject including a magnetization to be detected with a high frequency pulse to generate transverse magnetization, and a phase-encoded gradient magnetic field pulse to the subject to which transverse magnetization is applied. Means for applying a readout gradient magnetic field pulse, means for detecting an echo signal generated during the application of the readout gradient magnetic field, a control means for controlling each means, and an image from the echo signal. Comprising image reconstructing means to compose,
The means for detecting the echo signal comprises a plurality of receiving coils having detection sensitivity regions spatially different from each other,
The control means continuously performs measurement data collection and subsequent image reconstruction, and performs control to sequentially display a plurality of temporally continuous images. In the collection of at least one measurement data, the phase encoding is performed. Performs control to collect measurement data so that the measurement space (k space) defined by the gradient magnetic field and readout gradient magnetic field has different densities depending on the region,
The image reconstruction means calculates a sensitivity distribution of each receiving coil from a part of the at least one measurement data, and calculates from a part of the at least one measurement data for a plurality of consecutive image reconstructions. Using the sensitivity distribution and each measurement data, a time-series continuous image is acquired.

  In the MRI apparatus of the present invention, since the sensitivity distribution of the RF coil necessary for the calculation is calculated from the acquired data during the main measurement, there is no time difference between the sensitivity distribution data and the measurement data. Therefore, even with MRI imaging in which the situation changes from moment to moment, the aliasing can be removed stably. That is, even when shooting is required to have real-time properties, no error is caused and the image quality does not deteriorate.

  Also, since the sensitivity distribution of the RF coil is not measured in advance prior to projection, the total imaging time is not extended and the effect of short-time imaging is not impaired.

  Further, in the MRI apparatus of the present invention, the control means continuously performs measurement data collection and subsequent image reconstruction, performs control to sequentially display a plurality of temporally continuous images, and the image reconstruction means Since the sensitivity distribution calculated from one measurement data is used for a plurality of image reconstructions, the time required for image reconstruction in dynamic imaging employing parallel MRI can be shortened, and the real-time property can be improved.

  In dynamic imaging, a known pulse sequence such as a gradient echo system or echo planar imaging (EPI) can be employed as an imaging method performed by the control means. In the case of echo planar imaging (EPI), the array of measurement data in the k-space can be coarsened for a part of the region by changing the phase encoding value continuously applied in the EPI according to the time region.

  Hereinafter, the present invention will be described using examples. FIG. 1 is a diagram showing a configuration of a typical MRI apparatus to which the present invention is applied. This MRI apparatus generates a magnetic field 102 around a subject 101 and a gradient magnetic field in the space. A gradient magnetic field coil 103, an RF coil 104 that generates a high-frequency magnetic field in this region, an RF coil 105 that detects an MR signal generated by the subject 101, and a bed 112 on which the subject 101 lies are provided.

  The gradient magnetic field coil 103 is constituted by gradient magnetic field coils in three directions of X, Y, and Z, and each generates a gradient magnetic field in response to a signal from the gradient magnetic field power supply 109. An arbitrary cross section of the subject 101 can be selected by applying the gradient magnetic field, and position information can be given to the MR signal. The gradient magnetic field that gives position information to the MR signal is called a phase encode gradient magnetic field or a read gradient magnetic field, and thereby defines a measurement space (k space) in which measurement data is arranged.

  The RF coil 104 generates a high-frequency magnetic field according to the signal from the RF transmission unit 110. The frequency of the high-frequency magnetic field is tuned to the resonance frequency of the nuclear spin to be imaged. Usually, the subject of MRI imaging is proton, the main constituent of the subject. The signal of the RF coil 105 is detected by the signal detection unit 106, processed by the signal processing unit 107, and converted into an image signal by calculation.

  As shown in FIG. 2, the RF coil 104 is a multiple coil 201 in which a plurality of (four in the illustrated example) small RF coils 202 are arranged. Each small RF coil 202 can be, for example, a rectangular surface coil with a side of 15 cm arranged adjacent to each other, and the rectangular coils are arranged so as to partially overlap in the phase encoding direction of imaging, and are separated from each other. Detection sensitivity region.

  Each small RF coil 202 is connected to a preamplifier 203, and the output from each coil is amplified by the preamplifier 203, respectively. Each preamplifier 203 is connected in parallel to the AD conversion / orthogonal detection circuit 204 to constitute the signal detection unit 106. The signal detected by the AD conversion quadrature detector 204 is sent to the signal processing unit 107 in order to perform Fourier transform, filtering, synthesis operation, etc. for each coil. Processing performed by the signal processing unit 107 is incorporated in advance as a program.

  In FIG. 1, a gradient magnetic field power source 109, an RF transmitter 110, and a signal detector 106 are controlled by a controller 111 according to a time chart generally called a pulse sequence. In the MRI apparatus of the present invention, the control unit 111 performs control so that the phase encoding of a partial region of the k space is coarse.

Next, continuous imaging (dynamic imaging) using the MRI apparatus having the above configuration will be described. In dynamic shooting, the signals acquired by each small RF coil of the multiple coil are combined, and image display / transfer is repeated continuously to create time-sequential images (image numbers 1, 2, 3 ... 1000). get. Each image is obtained by combining signals acquired by each small RF coil by calculation using the sensitivity distribution of each small RF coil.
Hereinafter, a photographing method and image reconstruction (composition) will be described with reference to FIGS. FIG. 3 is a diagram showing an example of a pulse sequence employed in continuous imaging. This pulse sequence is a gradient echo (GrE) method sequence, after applying an RF pulse 301 together with a slice encode gradient magnetic field pulse 302 to excite a nuclear spin in a specific region of the subject to generate transverse magnetization. Then, the phase encode gradient magnetic field pulse 303 is applied, and then the read gradient magnetic field pulse 304 is applied, and the echo signal 305 is measured. The time (echo time) TE from application of the RF pulse 301 to measurement of the echo signal 305 is a parameter that determines the image contrast, and is set in advance in consideration of the target tissue and the like.

  Such a sequence is repeated, for example, a plurality of times while changing the area of the phase encoding gradient magnetic field (the value obtained by integrating the magnetic field intensity with respect to the application time), thereby acquiring data in the k space.

  FIG. 4 is a diagram showing a k-space data array (k trajectory) of measurement data measured by repeating the above sequence, and one column of data in the k-space lateral direction (kx direction) is obtained by one signal acquisition. To be acquired. The value of ky is determined by the area of the phase encoding gradient magnetic field. In the normal GrE sequence, the phase encoding steps are equally spaced, whereas in the sequence of this embodiment, the phase encoding steps are different between the region 1 (402) and the region 2 (403) of the k space 401. For example, in the region 1 (402) occupying the low frequency portion of the phase encoding, signals are densely acquired in the phase encoding (ky) direction, and the region 2 (403) occupying the high frequency portion is sparse in the phase encoding direction. Is acquired. As an example, the phase encoding increases by 1 step from the center of the k space up to 10% of the upper and lower data, but when it exceeds 10%, the phase encoding increases by 2 steps or 4 steps. As a result, the entire shooting time is shortened by the thinned-out amount.

  The ratio of the area 1 (402) to the entire k space (about 20% in this case) is appropriately set in consideration of both the coil sensitivity and the reduction of the photographing time. When the coil sensitivity is steep, it is desirable to increase the ratio, while from the viewpoint of shortening the photographing time, it is preferable to decrease the ratio. The k trajectory is typically a 256 × 256 matrix, and data is collected at this density in region 1 (402). In the region 2 (403), the sampling is performed roughly 2 to 4 times in the phase encoding direction.

  The data measured in this way is sent to the signal processing unit 107 for each receiving coil 202. Here, as shown in FIG. 5, the sensitivity distribution calculation 503 for each receiving coil and the synthesis of signals from each receiving coil are performed. Processing 504 is performed. That is, the sensitivity distribution image Wn (x, y) of each coil is obtained using the signal en (kx, ky) 501 from each coil. n is a coil number, and n = 1, 2, 3 or 4 in this embodiment. Further, (kx, ky) represents the coordinates in the k space, and (x, y) represents the position in the real space. The entire image S (x, y) 505 is synthesized using the sensitivity distribution image and the signal. The sensitivity distribution calculation 503 and the synthesis process 504 will be described in further detail.

  6 and 7 are diagrams showing a procedure for calculating the sensitivity distribution of the RF coil from the signal en (kx, ky) 501 for each receiving coil. First, a low frequency pass filter (LPF) 601 is applied in the phase encoding direction so that only the data of region 1 remains. The filter may be a one-dimensional filter for the purpose of removing aliasing aliasing in the phase encoding direction, but a two-dimensional filter is preferable to one-dimensional to eliminate the fine structure of the living body. In this case, for example, a Gaussian type, a Hamming type, a Hanning type, etc. are suitable. Further, as a highly accurate filtering method, a method using a flying window in an image space is also possible.

  As a result of such filtering, the data in area 2 (403) is all zero as shown in FIG. Further, the boundary between the region 1 (402) and the region 2 (403) is smoothly connected to zero. In FIG. 7, the right curve is the filter profile.

  Next, a two-dimensional Fourier transform (FT) 602 is performed on the entire k space. As a result, only the low frequency component of the image can be extracted. In addition, an image free from aliasing artifacts can be obtained. It is known that these images can be regarded as the sensitivity distribution of the RF coil, and this is also referred to as a sensitivity distribution Wn (x, y) in this embodiment. In the case of multi-slice imaging, the sensitivity distribution of the coil needs to be obtained for each slice of each coil. In the case of three-dimensional imaging, since the signal obtained for each coil is a function of the three-dimensional measurement space (kx, ky, kz), a three-dimensional filter is used as a low-frequency pass filter, and Fourier transformation is performed in three dimensions. The three-dimensional sensitivity distribution Wn (x, y, z) of the coil can be obtained by extending to.

  Next, the synthesis operation 504 using this sensitivity distribution Wn (x, y) will be described. There are a method of performing the composition operation in the image space (real space) and a method of performing it in the measurement space, and any of them can be employed.

  FIG. 8 conceptually illustrates a method performed in the image space. Here, in order to simplify the description, a case of a multiple coil composed of two small coils 801 and 802 will be described. When data is collected roughly (thinned out) in the phase encoding direction as in the region 2 of the k space shown in FIG. 4, the signals from the two coils are phased as shown in FIGS. 8B and 8C. An image 803 in which a folding artifact 804 is generated in the encoding direction is obtained. The aliasing artifact 804 can be removed by multiplying the sensitivity distribution of each small coil with such an image, and an image without overlapping images due to aliasing can be obtained as shown in FIG.

  In the method of synthesizing signals in the measurement space, there is a shortage in the measurement space by determining the weight so that the combined sensitivity distribution obtained by combining the sensitivity distribution of the small RF coil with the appropriate weight becomes the desired frequency. To create data.

このとき合成される信号S(kx,ky)は、次式で示される。

式（２）中、ρは磁化密度、＾は２次元フーリエ変換を表す。この式（２）からわかるように合成感度分布Wcomp(x,y)を用いることにより、ρ＾(kx,ky)からρ＾(kx,ky-mΔky)を求めることができる。これはｋ空間の位相エンコード方向で粗であるデータ間のデータを埋め合せることを意味する。 For example, the sensitivity distribution Wn (x, y) of a small RF coil is synthesized with an appropriate weight Cn, and the combined sensitivity distribution Wcomp (x, y) in the form of exp (i · mΔky · y) [m is an integer] is obtained. Suppose that it is obtained.

The signal S (kx, ky) synthesized at this time is expressed by the following equation.

In equation (2), ρ represents a magnetization density, and ^ represents a two-dimensional Fourier transform. As can be seen from this equation (2), by using the combined sensitivity distribution Wcomp (x, y), ρ ^ (kx, ky-mΔky) can be obtained from ρ ^ (kx, ky). This means that data between data that is coarse in the phase encoding direction of the k space is compensated.

  FIG. 9 is a diagram conceptually showing this method. As shown in the figure, first, sensitivity distribution is obtained from the measurement data of region 1 (402) by LPF, zero filling, and FT processing. Next, for the area 2 (403) where the measurement data is roughly arranged by thinning, the data (corresponding to the solid line in the enlarged view) already obtained by the above calculation (corresponding to the dotted line in the enlarged view) ). The number of new data (number of dotted lines) that can be created in this way depends on the number of small RF coils, and up to four new data can be created when there are four small RF coils. In the example shown in the figure, the thinning rate is 4 and three data are created.

  The data after supplementing with new data in this way is the same as the data measured without thinning out the entire area of k-space, and an image free from aliasing artifacts can be obtained by performing a two-dimensional Fourier transform.

  As described above, in this embodiment, a part of the phase encode is thinned out to shorten the time, and the measurement data obtained by the photographing is used for the dense part of the data, so that the RF coil sensitivity distribution is not turned back. Therefore, the time difference between the measurement for obtaining the sensitivity distribution and the main measurement can be eliminated, and the calculation error associated therewith can be eliminated.

  In particular, by acquiring densely the low-phase encoded component data that contains the main image information in the measurement data, it is possible to obtain an image that does not deteriorate the S / N, and is useful for diagnosis in clinical applications. An extremely effective image can be provided. Further, since it is not necessary to perform measurement for obtaining the sensitivity distribution of the coil in advance, in addition to the time shortening effect in the main measurement, the entire measurement time can be shortened. Therefore, it is particularly suitable for continuous shooting.

  FIG. 10 shows an embodiment in which the present invention is applied to dynamic shooting for obtaining continuous images in real time by repeating shooting in time series. In dynamic shooting, the signals acquired by each small RF coil of the multiple coil are combined, and image display / transfer is repeated continuously to create time-sequential images (image numbers 1, 2, 3 ... 1000). get. Here, in the first image acquisition, the steps of signal acquisition 1001, sensitivity distribution calculation 1002, and signal synthesis 1003 are performed as in steps 502, 503, and 504 shown in FIG. An image from which aliasing artifacts are removed is reconstructed using the distribution. This image is displayed on the display of the MRI apparatus or transferred to an external display device, storage device or the like (1004). The sensitivity distribution calculation result obtained for the first sheet is stored at a specific address in the memory of the signal processing unit.

  Next, for the second image, after the signal is acquired, a synthesizing process 1003 for removing aliasing artifacts is performed using the sensitivity distribution data stored in the memory. Thereafter, unless the arrangement of the receiving coil is changed, the sensitivity distribution calculation is not performed and the synthesis process is performed using the sensitivity distribution data in the memory. Since the sensitivity distribution does not change if the arrangement of the receiving coil does not change, the calculation result obtained first as described above can be used. As a result, even when the shooting interval of dynamic shooting (the interval between image acquisition and the next image acquisition) is shortened, the calculation for imaging can be shortened, and the real time property (time resolution) of display can be improved. For example, when a high-speed sequence such as EPI is used as a shooting sequence, it is important to increase the calculation speed in order to make continuous high-speed shooting effective. However, by adopting the embodiment shown in FIG. It is possible to monitor the condition of the subject.

  Next, an MRI apparatus that incorporates an EPI sequence suitable for the MRI apparatus described above will be described. In this aspect, the configuration of the apparatus is the same as that shown in FIG. 1, but the MRI apparatus according to this aspect measures the control space 111 so that the measurement space (k space) has different densities depending on the area. An EPI sequence for controlling data collection is incorporated.

  FIG. 11 is a diagram showing an embodiment of such an EPI sequence, and shows a spin echo type EPI sequence. That is, simultaneously with the slice selection gradient magnetic field pulse Gs1103, an RF pulse 1101 that excites the nuclear spin of the subject tissue is applied, and the RF pulse 1102 that reverses the transverse magnetization generated by the first RF pulse 1101 after TE / 2 hours is slice-selected. The echo signal 1106 is measured while applying the readout gradient magnetic field pulse Gr1105, which is applied together with the gradient magnetic field pulse Gs1104, and then the polarity is inverted thereafter. At this time, phase encoding gradient magnetic fields Ge1107 and 1108 for phase-encoding the echo signal are applied for each readout gradient magnetic field pulse Gr.

  In a normal EPI sequence, for example, assuming that the matrix size of the k space is 128 × 128, the readout gradient magnetic field pulse is inverted 128 times and 128 echo signals are measured. For the phase encode gradient magnetic field pulse, 128 pulses of the same magnitude are applied in addition to the first offset pulse. On the other hand, in the EPI sequence of this embodiment, for example, a phase encode gradient magnetic field pulse 1107 having a magnitude such that the number of phase encodes is incremented by 1 is applied to an echo signal from a phase encode 0 echo signal to a predetermined phase encode. . For echo signals to be measured thereafter, a plurality of phase encode numbers, for example, a phase encode gradient magnetic field pulse 1108 having a magnitude that increments by four is applied.

  In the example shown in the figure, for the sake of simplicity, the case of measuring eight echo signals is shown. A normal phase encoding gradient magnetic field pulse 1107 is applied until the fifth signal measurement, and the sixth to eighth signals are measured. Until the signal measurement, a phase encode gradient magnetic field pulse 1108 that is four times the normal magnitude is applied. The first to fifth signals correspond to the region 1 (402) in the k space shown in FIG. 4, and the sixth to eighth signals correspond to the region 2 (403). Therefore, for the sixth to eighth signals, the time required to measure 12 (3 × 4) signals is conventionally required. In this sequence, 9 (12-3) signal measurement times are reduced. Can do. In terms of k trajectory, it is possible to measure densely for the region 1 and roughly measure the region 2 by executing the above sequence.

  The present invention can be applied not only to the above-mentioned spin echo type EPI but also to a gradient echo type EPI, to a one shot EPI that collects measurement data necessary for one excitation, or to a multi-shot (split type) EPI. Can also be applied. Such an MRI apparatus according to the second aspect of the present invention is suitable as a parallel MRI sequence using the multiple coils described above. Even when the above-described EPI sequence is applied to parallel MRI, the processing performed by the signal processing unit is the same as in the case of the GrE sequence. That is, using the data measured by the above-described EPI sequence as shown in FIG. 5, the sensitivity distribution calculation 503 is performed for each small RF coil constituting the multiple coil, and the synthesis process 504 is performed using the obtained sensitivity distribution. To obtain an image with no aliasing artifacts.

  In the case of dynamic shooting, as shown in FIG. 10, the sensitivity distribution calculation is performed only when the first image is reconstructed, and the subsequent images are displayed from the signal acquisition to the image display using the sensitivity distribution. / Continues processing up to transfer. In this case, as described above, the EPI sequence of the present invention has a shorter signal acquisition time than a normal EPI sequence, and it is not necessary to perform sensitivity distribution calculation separately from the main measurement or for each signal acquisition. High-speed continuous shooting is possible.

  As mentioned above, although each embodiment of the MRI apparatus of this invention was described, this invention is not limited to these embodiment, A various change is possible. For example, in the above description, the GrE sequence and the EPI sequence are exemplified as the pulse sequence used for the parallel MRI. Applicable. It can also be extended to 3D photography.

  FIG. 12 is a diagram showing the k trajectory 1200 in the case of a spiral sequence. In this case, the circular region 1 (1202) in the center of the k space is a region where signals are densely arranged, and the signal is coarse in the surrounding region 2 (1203). In order to obtain the sensitivity distribution from the measurement data of such a spiral sequence, a two-dimensional filter having filter profiles 1301 and 1302 as shown in FIG. 13 is used. Examples of such a two-dimensional filter include a two-dimensional Gaussian filter, a two-dimensional Hanning filter, and a two-dimensional Hamming filter. Similar to the case of other sequences, the sensitivity distribution for each small coil obtained from the measurement data of the region 1 (1202) is used to synthesize an image from which aliasing artifacts are eliminated.

  According to the MRI apparatus of the present invention, when performing parallel MRI using a multiple coil, imaging is performed by shortening the measurement time by thinning out a part of the k space, and the data of the area where the measurement data is dense is obtained. Since the sensitivity distribution is obtained and the signals are synthesized, the image quality is not deteriorated in photographing that requires real-time characteristics. In particular, it is possible to obtain an image with a high S / N and a high diagnostic value by densely acquiring low-frequency components in the k space.

  In addition, since it is not necessary to measure the sensitivity distribution of the RF coil prior to photographing, the total photographing time is not extended. Therefore, the effect of short-time imaging, which is a feature of the parallel MRI technique, can be exhibited.

1 is a block diagram of an MRI apparatus to which the present invention is applied. The block diagram which shows the principal part of the MRI apparatus of FIG. The figure which shows one Example of the pulse sequence which the MRI apparatus of this invention employ | adopts. The figure which shows an example of the arrangement | sequence of the k space data of the measurement data by the sequence of FIG. The schematic diagram which shows one Example of the process of the signal processing part of the MRI apparatus of this invention. The figure explaining the sensitivity distribution calculation by this invention. The figure explaining the sensitivity distribution calculation by this invention. The figure explaining one Example of the signal synthesis | combination by this invention. The figure explaining the other Example of the signal synthesis | combination by this invention. The figure which shows one Example of the continuous imaging | photography by the MRI apparatus of this invention. The figure which shows the other Example of the pulse sequence which the MRI apparatus of this invention employ | adopts. The figure which shows the other example of k space data arrangement | sequence of the measurement data by this invention. The figure explaining the other Example of the sensitivity distribution calculation by this invention.

Explanation of symbols

101 ・ ・ ・ ・ ・ ・ Subject
103 ・ ・ ・ ・ ・ ・ Gradient magnetic field coil
104 ・ ・ ・ ・ ・ ・ Transmitting RF coil
105 ・ ・ ・ ・ ・ ・ Receiver RF coil
107 ・ ・ ・ ・ ・ ・ Signal processing section
111 ・ ・ ・ ・ ・ ・ Control part
202 ・ ・ ・ ・ ・ ・ Small RF coil

Claims (2)

Means for generating transverse magnetization by irradiating a subject including magnetization to be detected with a high-frequency pulse;
Means for applying a phase encoding gradient magnetic field pulse to a subject to which transverse magnetization is applied; means for applying a read gradient magnetic field pulse; means for detecting an echo signal generated during application of the read gradient magnetic field; In a nuclear magnetic resonance imaging apparatus including a control means for controlling the means and an image reconstruction means for reconstructing an image from an echo signal,
The means for detecting the echo signal comprises a plurality of receiving coils having detection sensitivity regions spatially different from each other,
The control means continuously performs measurement data collection and subsequent image reconstruction, and performs control to sequentially display a plurality of temporally continuous images,
In collecting at least one measurement data, the measurement space (k space) defined by the phase encoding gradient magnetic field and readout gradient magnetic field is controlled to collect measurement data so that the density varies depending on the region,
The image reconstruction means calculates a sensitivity distribution of each receiving coil from a part of the at least one measurement data, and calculates from a part of the at least one measurement data for a plurality of consecutive image reconstructions. A nuclear magnetic resonance imaging apparatus that acquires time-sequential images using sensitivity distribution and each measurement data. The nuclear magnetic resonance imaging apparatus according to claim 1,
The image reconstruction means performs the sensitivity distribution calculation for an image acquired first among a plurality of temporally continuous images, and performs image reconstruction using the sensitivity distribution for subsequent images. Characteristic nuclear magnetic resonance imaging apparatus.

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