JPH02213327A - magnetic resonance imaging device - Google Patents

Abstract

PURPOSE:To diagnose the lesion part present on the surface of a brain by preventing the overlap of a represented image due to fat with a brain groove represented image due to water by emphasizing the magnetic resonance signal from water at every slice region approaching a cylindrical coil wrapping the head to detect the same while suppressing the magnetic resonance signal from fat. CONSTITUTION:An RF pulse is transmitted by the transmission coil or head coil 13 of an embedding whole body probe 3 and a slice inclined magnetic field is added from an inclined magnetic field generating coil 2 and, thereafter, a reversed read inclined magnetic field and an intensity variable phase encoding inclined magnetic field are added. Then, an echo signal is collected from a multistylus part within an echo time by the head coil 13. An image is subjected to addition processing in a computer system 11 and a multiecho method executing a brain surface structure imaging sequence surpressing the signal from fat and emphasizing the signal from water during one encoding process and a usual imaging sequence is executed along with a multistylus method. A represented image due to fat is prevented from the overlap with a brain groove represented image due to water to diagnose the lesion part present on the surface of a brain.

Description

[Detailed Description of the Invention] [Object of the Invention] (Industrial Field of Application) The present invention is directed to magnetic resonance (MR)
MRI that uses the phenomenon (sonance) to obtain morphological information of the subject (living body) and functional information such as spectroscopy.
The present invention relates to a method for imaging brain surface structures using a magnetic resonance imaging device (magnetic resonance imaging device).

(Prior art) Magnetic resonance is a phenomenon in which an atomic nucleus with non-zero spin and magnetic moment placed in a static magnetic field resonantly absorbs and emits only electromagnetic waves of a specific frequency. The angular frequency ω0 (ωo−2πshi0.shi0
; Larmor frequency).

ω0−γH.

Here, γ is the gyromagnetic ratio specific to the type of atomic nucleus,
Further, Ho is the static magnetic field strength.

An apparatus that performs biological diagnosis using the above-mentioned principle processes the electromagnetic waves of the same frequency as the above induced after the above-mentioned resonance absorption, and calculates the nuclear density, longitudinal relaxation time TI, transverse relaxation time T2. Diagnostic information that reflects information such as flow and chemical shift, such as slice images of a subject, can be obtained non-invasively.

Collecting diagnostic information by magnetic resonance can excite all parts of a subject placed in a static magnetic field and collect signals, but there are limitations in the equipment configuration and clinical requirements for imaging images. Therefore, in an actual device, a specific part is excited and its signal is collected.

In this case, the specific region to be imaged is generally a sliced region with a certain thickness;
Magnetic resonance signals (MR multiplied signals) of echo signals and FID signals from this slice site are collected by performing a data encoding process many times, and these data groups are subjected to image reconstruction processing using, for example, a two-dimensional Fourier transform method. By doing so, an image of the specific slice region is generated.

On the other hand, we will discuss clinical applications realized by using magnetic resonance imaging equipment. In other words, when performing surgical treatment for intracranial diseases, images depicting the brain surface structure, including sensation, are an important guide for knowing the location of lesions localized in the cortex and subcortex, and are important for determining the location of lesions localized in the cortex and subcortex. Accurate position determination is desired, and several attempts have been made to accomplish this using magnetic resonance imaging. An example will be explained below.

One method is to perform normal proton imaging using a head coil. In this method, the head coil is box-shaped so that it wraps around the head, so signals from the entire head are collected, so the image contains information deep below the layer surface. As a result, the above-mentioned request for diagnosis cannot be fully met.

There is also a method of performing normal proton imaging using a surface coil. In this method, due to the sensitivity characteristics of the surface coil, that is, the areas close to the coil are highly sensitive, only signals from the surface layer, such as subcutaneous fat, are collected, and as a result, the above-mentioned diagnostic requirements are not met. It's not something you can get rid of.

In other words, neither of the above two methods can present an image that accurately represents the brain surface structure.

(Problem to be solved by the invention) In this way, in the conventional technology, signals from cerebral effusion and fat are collected in the same way without distinction, so it is difficult to diagnose the location of a localized lesion in the cortex or subcortex. There was a problem in that it was not possible to obtain images of the brain surface structure for analysis.

SUMMARY OF THE INVENTION Therefore, an object of the present invention is to provide a method for imaging brain surface structures using an MRI apparatus, which can obtain images depicting brain surface structures for diagnosing lesions existing on the brain surface of the head. .

[Structure of the Invention] (Means for Solving the Problems) In order to solve the above problems and achieve the objects, the present invention has the following structure. That is, claim 1 of the present invention
The configuration involved is a static magnetic field magnet.

In a method of imaging the brain surface structure using an MRI device that includes gradient magnetic field coils and transmitting/receiving coils and collects signals associated with the magnetic resonance phenomenon of specific atomic nuclei and images them, a cylindrical shape that can wrap around the head is used. Using a coil that can perform at least one of transmitting and receiving, the subject's head is targeted for proton imaging, suppressing signals from fat and emphasizing signals from water during a single encoding process. The multi-echo method, which executes a brain structure imaging sequence that does not suppress signals from fat and a normal imaging sequence that does not emphasize signals from water, is performed together with the multi-slice method, and brain surface structure images and It is characterized by obtaining a normal image.

The structure according to claim 2 of the present invention is a static magnetic field magnet.

In a method of imaging the brain surface structure using an MRI device that has gradient magnetic field coils and transmitting and receiving coils and collects and images signals associated with the magnetic resonance phenomenon of specific atomic nuclei, a cylindrical shape that can wrap around the head is used. Using a coil that can perform at least one of transmitting and receiving, the subject's head is targeted for proton imaging, suppressing signals from fat and emphasizing signals from water during a single encoding process. A multi-echo method that executes a brain structure imaging sequence that does not suppress signals from fat and a normal imaging sequence that does not emphasize signals from water is executed together with a multi-slice method. A predetermined weight is attached to each of the multi-slice images obtained by executing the sequence, each slice image with this weight attached is added to obtain a brain surface structure image, and this brain surface structure image and the normal image are displayed. It is characterized by providing

The structure according to claim 3 of the present invention is a static magnetic field magnet.

In a method of imaging the brain surface structure using an MRI device that has gradient magnetic field coils and transmitting and receiving coils and collects and images signals associated with the magnetic resonance phenomenon of specific atomic nuclei, a cylindrical shape that can wrap around the head is used. Using a coil that can perform at least one of transmitting and receiving, the subject's head is targeted for proton imaging, suppressing signals from fat and emphasizing signals from water during a single encoding process. A multi-echo method that executes a brain structure imaging sequence that does not suppress signals from fat and a normal imaging sequence that does not emphasize signals from water is executed together with a multi-slice method. A predetermined weight is attached to the matrix component of each slice image obtained by executing the sequence, and each weighted slice image is added to this matrix component to obtain a brain surface structure image, and this brain surface structure image and the normal image are It is characterized in that it is provided for display.

6. The configuration according to claim 4 of the present invention is defined in claim 2 or 3.
This configuration is characterized in that when adding each slice image, the addition is performed while shifting the position of each slice image.

(Function) According to the configuration according to claim 1, by executing the brain structure imaging sequence, the coil that has a cylindrical shape that can wrap around the head and that can perform at least one of transmission and reception comes close to the coil. Since the magnetic resonance signal from the water in each slice region is enhanced and the magnetic resonance signal from the fat is suppressed, it is possible to visualize the sensation image of the water in the sensation of the head, and also to detect the fat. Since the magnetic resonance signals from the brain are suppressed, the images rendered by fat do not overlap with the sensational images rendered by water, which is suitable for diagnosing lesions existing on the brain surface. A table structure image can be presented. In addition, since a cylindrical coil that can wrap around the head is used, it is easy to set up the coil and the object to be imaged (the head), allowing slices depicting the brain surface structure viewed from any direction. Images can be obtained, and by referring to each image, the positional relationship in the depth direction can be easily determined.

In this case, the normal imaging sequence is encoded together with the brain surface structure imaging sequence, and a brain surface structure image and a normal image can be obtained and observed at the same time in a single imaging session, improving diagnostic efficiency. .

According to the configurations according to claims 2 and 3, in addition to achieving the effects of the configuration according to claim 1, the same effect as when using a surface coil is achieved, and the overlapping of strong signals from deep structures such as the brain substance is prevented. Therefore, the added image will be one that accurately depicts the brain surface structure, and since the voxels of each slice image during addition are small, the added image will have phase disturbances suppressed as much as possible. .

According to the configuration according to claim 4, in addition to producing the effect of the configuration according to claim 2 or 3, at least two images with different viewing directions can be obtained by performing addition while shifting the position of each slice image. It is possible to perform stereo viewing using two images.

(Example) An example of a method for imaging a brain surface structure using an MRI apparatus according to the present invention will be described below with reference to the drawings. FIG. 1 is a diagram showing the overall configuration of a magnetic resonance imaging apparatus to which the method of the present invention is applied.

As shown in FIG. 1, the magnet assembly MA capable of accommodating the subject P therein may have a configuration using a static magnetic field coil (permanent magnet) using a normal conduction or superconductivity method. ) 1, and X for generating a gradient magnetic field for providing positional information of the magnetic resonance signal induction site.

Y- and Z-axis gradient magnetic field generating coils 2, and a transmitting and receiving system for transmitting a rotating high-frequency magnetic field and detecting an induced magnetic resonance signal (MR multiplied signal echo signal or FID signal), such as a transmitting coil and a receiving coil. It has an implantable whole body probe 3 consisting of.

If it is a superconducting system, it includes a refrigerant supply control system and mainly controls the energization of the static magnetic field power source, the transmitter 5, which controls the transmission of RF pulses, and the induced MR multiplied signal reception control. a receiver 6 for controlling the X, Y, and Z axes;
Y-axis and Z-axis gradient magnetic field power supplies 7, 8, 9, a sequencer 10 capable of implementing a pulse sequence for data collection, a computer system 11 that controls these and performs signal processing of detection signals and display thereof, and a display. Device 1
2.

In addition, in this embodiment, the head PH of the subject P is placed at the center of the magnetic field of the magnet assembly MA, and the head coil 13 is placed as a cylindrical coil so as to wrap around the head PH, as shown in FIG. are doing. This head coil 13 is connected to the transmitter 5 or receiver 6 similarly to the implantable whole body probe 3.
It is driven by , making it possible to transmit and receive data.

Here, the pulse sequence for data collection is
The transmitter 5 is driven, and an RF pulse of a rotating magnetic field is applied from the transmitting coil of the implantable whole body probe 3 or the head coil 13, and the gradient magnetic field power supplies 7, 8.9 are driven, so that the gradient magnetic field generating coil 2 Gradient magnetic fields Gx, Gy, and Gz are applied for 1-phase encoding for slices and for reading, and signals from a specific region are collected by the receiving coil of the implantable whole-body probe 3 or the head coil 13. This sequence is repeated a predetermined number of times to obtain a data group, and an image is generated from this data group.

In addition, in the pulse sequence for collecting images described above, the head PH of the subject P is targeted for proton imaging, fat signals are suppressed, and water (cerebrospinal fluid: C
This sequence is based on a spin echo method or a field echo method in which the signal of 5F) is emphasized, and this sequence is executed in a multi-slice manner. Here, as a spin echo method, as shown in FIG. 2, for example, the echo time TE
is longer than usual, for example, about 250 m5ec (usually about 80 m5ec), and the pulse repetition interval TR is about 2000 a+sec (usually about 500 g).
It is about g5ec. ). In addition, in the field echo method, the echo time TE is set longer than usual, for example, about 20 to 30 m5ec (usually 14 m5ec).
It is about ec. ), and the pulse repetition interval TR is 8
0 to 1000 a+sec (usually 50111sO
It is about e. ). Further, the flip angle of the RF pulse is set to 10 to 20 degrees.

RF is an excitation pulse, Gs is a slicing gradient magnetic field in the Z-axis direction, G is a read gradient magnetic field in the X-axis direction, and Ge is an encoding gradient magnetic field. In this case, MR is a gradient magnetic field in the Y-axis direction, and MR is an induced magnetic resonance signal, which in this case is an echo signal.

Under these condition settings, an RF pulse is transmitted by the transmitting coil or head coil 13 of the implantable whole body probe 3, and a slicing gradient magnetic field Gs is applied from the gradient magnetic field generating coil 2, and then the lead is reversed. Gradient magnetic field G
r and a phase encoding gradient magnetic field Ge of variable intensity are applied, and an echo signal is collected from the multi-slice region by the head coil 13 at an echo time TE. By repeating this a predetermined number of times, a data group is provided to the computer system 11, and a multi-slice image is generated from this data group. Then, this multi-slice image is subjected to addition processing in the computer system 11 using a method described later, and an added image and a current multi-slice image are obtained (
(see FIG. 3) is displayed on the display device 12.

Here, the addition processing of multi-slice images will be explained.

The addition processing methods 1, 2.3 described below are methods for obtaining sensitivity characteristics similar to those using surface coils and for obtaining signal suppression effects depending on the position (depth) of the lesion (region of interest). Addition processing method 4 is a method for obtaining images for stereo viewing.

<Addition processing method 1> N multi-slice images (matrix) are
, j). k-1,2,...,N,,i.

j-1 to 256 (matrix).

The image obtained by weighted addition of these images is assumed to be S(1°j).

Here, al( is a value (coefficient) that corresponds to the sensitivity of the surface coil, for example. Figure 4 is a characteristic diagram showing the relationship between the depth of the surface coil and the sensitivity. If there is a lesion at a position 5 cm away from 13) and you want to clearly visualize the lesion with the same characteristics as when using a surface coil, then if you define ak according to Figure 4, you will get the following: It becomes like this.

al=1.0, a2mo, 9, a3-0.75, a4=
0.6, a5-0.5, ... In other words, by selecting the value of the coefficient ak attached to each slice image to an appropriately smaller value as the slice position becomes deeper, deep parts such as the ventricles and basal ganglia can be As a result, signals from deep areas such as the ventricles and basal ganglia are suppressed, and they no longer overlap in the sensational image.

Therefore, in the image displayed on the display device 12, sensationalism is depicted without overlap with other images, the positional relationship between the brain surface and the lesion is clear, and clinically extremely useful diagnostic information can be presented.

Additive processing method 2> Additive processing method 1 was simply to obtain the same characteristics as the surface coil, but additive processing method 2 obtains the same characteristics as the surface coil, and also ), the weighting selects the value of the coefficient ak.

That is, as shown in FIG. 5(a), when the lesion exists at a shallow position, the deeper the slice is located, the smaller the value of the coefficient ak and the greater the degree of reduction. For example, as shown in FIG. 5(b), al ml, 0
．． a2-0.9. a3-Q, 6. a4 =0.2.・
Select as follows. When selected in this way, water (CS) from slices located deep within the ventricle etc.
Since the signal F) is suppressed, the overlap of the signals is also suppressed, and as a result, the added image clearly depicts the structure of the back of the brain, including the lesion located at a shallow position.

Contrary to the above, as shown in FIG. 6(a), when the lesion exists in a deep position, the degree of decrease in ak is reduced. For example, as shown in FIG. 6(b), al-1,
0, a2-0.95. a3-0.8. a4 =0.7.
Select as follows.

<Addition processing method 3) In addition processing method 1.2, a coefficient ak is attached to each slice image for weighting, but in addition processing method 3, matrix i, which is an internal element of each slice image, Weighting is done by adding a coefficient ak depending on j.

For example, if you want to particularly emphasize the brain surface, by selecting ak as shown below, it will be weighted hemispherically.

ak(1,j) −(k-N)"/N'+(i"128)2/128"+
(j-128)2/1282k -1,2,3,...
, N, t, j-1, 2, 3, . . . , 256 Addition processing method 4> Addition processing method 4 enables stereo viewing through addition processing. In other words, the weighting in addition processing method 1゜2.3 can change the viewing direction by shifting the position of each slice image during addition, and as a result, two images with different viewing directions are scanned. To enable stereo viewing using only one multi-slice image without having to

That is, Δ1. Given Δj, images S(1,j)' with different line-of-sight directions are created. In this case, Δ1. When Δj is a non-integer, interpolation such as linear interpolation is performed as appropriate to create an image.

For example, let the pixels of the image Mk (i, j) be lll1
1 and the slice thickness is 10II11.

If Δ1-1 (that is, 4gta) + Δj-0, the line of sight direction is approximately 5.7° (= ta
n-' 1/10), and the image S
It becomes possible to perform stereo viewing using and S'.

The present applicant has previously filed a patent application for an invention related to this embodiment. In the invention described in the specification and drawings of the earlier application (Japanese Patent Application No. 62-232949 filed on September 17, 1988, title of the invention "Magnetic Resonance Imaging Method"), a surface coil is used to slice 8cm thick
The echo time was set longer than usual (2505 sec), and the pulse repetition interval TR was
The same effect as in this example is obtained using the spin echo method in which the time is set to be longer than usual (2000 m5ec), that is, a brain surface structure image (SA3 image: S urraceA nat
osy S can ).

The above embodiment has the following advantages compared to the invention of the earlier application. That is, an SA3 image viewed from a desired direction can be taken without being specified by the installation position of the surface coil, unlike the invention according to the previous application. Furthermore, since a head coil is used, setting is easy. By referring to the added image and the slice image, the positional relationship in the depth direction can be easily determined. When adding up, the weighting coefficient is adjusted appropriately depending on the location of the lesion and the case, so that the S that accurately represents the location of the lesion and the case is
It becomes possible to obtain A3 images. Stereo viewing can be performed without rescanning with a different viewing direction. Since the slice thickness is small, the voxels during imaging are small, so phase disturbance is small and signal degradation is small.

In addition, in the invention according to the previous related application, for example, when the pulse repetition interval TR is 2 seconds and the encoding is performed 256 times, the data collection time is 2 x 256-512 seconds, but in this embodiment, the field echo method is used. If used, the pulse repetition interval TR may be 80 to 1000 m5ec, so 0.08 (1,0) x 256 - 20.48 (25
6) seconds, which is advantageous because data collection can be completed in an extremely short time.

In each of the above examples (those using the sequence shown in Figure 2), one echo signal is obtained by one encoding, and N encodings are required to image an NXN matrix. This is an example of the single echo method, but it can be extended to an embodiment using the sequence shown in FIG. 2 as a procedure for obtaining one echo signal in the multi-22 method.

FIG. 8 shows one encoding pulse sequence of the multi-echo method of this embodiment, and the third echo signal is the same as the echo signal shown in FIG. Then, the first echo signal has an echo time TE of 20■See
The second echo signal has an echo time TE of 1205
The pulse repetition interval 'rn is about 20005 seconds, which is the same as in FIG. 2. That is, the eighth
By encoding the sequence shown in the figure N times to perform NXN matrix imaging, a density-weighted image can be obtained for the image based on the first echo signal, and a T2-weighted image can be obtained for the image based on the second echo signal. You will be able to do this. Therefore, the first echo signal and the second
The sequence for obtaining echo signals is the sequence for obtaining images used for normal clinical examinations.
The sequence for obtaining the third echo signal is a sequence for obtaining a brain surface structure image.

In this way, by encoding the normal imaging sequence along with the brain surface structure imaging sequence, it is possible to obtain and observe the brain surface structure image and the normal image at the same time in a single imaging session, thereby improving diagnostic efficiency. . In the 3 multi-echo method shown in FIG. 8, the number of multi-slices can be about 6.

Note that the multi-echo method in the above example assumes that three echo signals are obtained in one encoding, but it can be applied to methods that obtain two echo signals or four echo signals. For example, with 2 echoes, the echo time TE is 1 as a normal imaging sequence.
The first echo signal is about 20 m5ec, and the echo time T of the second echo signal is used as a brain surface structure imaging sequence.
Let E be approximately 250 w+sec.

In addition, for 4 echoes, the normal imaging sequence is a first echo signal with an echo time TE of about 40 m5ec, a second echo signal with an echo time TE of about 80 m5ec, and a third echo signal with an echo time TE of about 120 m5ec. As an echo signal, the echo time TE of the fourth echo signal is set to about 250 m5ec as a brain surface structure imaging sequence.

Furthermore, in order to increase the number of slices beyond the six described above when obtaining a brain surface structure image, the following sequence may be executed. In other words, the first sequence is the normal imaging sequence.
The echo time T6 of the echo signal is about 20 tssec, the echo time TE of the second echo signal is about 80 seconds, and the echo time TE of the third echo signal is about 2505 seconds as a brain surface structure imaging sequence. However, the pulse repetition interval TR is set to about 3000 ■See. This makes it possible to slice about 100 pieces.

In addition, as a normal imaging sequence, the first echo signal has an echo time TE of about 20 m5ec, the second echo signal has an echo time TE of about 120 m5ec, and the third echo signal has an echo time TE of about 120 m5ec as a sequence for brain surface structure imaging. The echo time TE of the echo signal is approximately 200 m5ec. The pulse repetition interval TR is approximately 2000 m5ec. This also makes it possible to slice about 100 pieces. However, since the echo time TE of the third echo signal is set to about 200 seconds as a brain surface structure imaging sequence, there is no problem in practicality although the contrast as a brain surface structure image is slightly reduced.

Of course, not only the spin echo method but also the field echo method can be applied to the brain structure imaging sequence and the normal imaging sequence to the multi-echo method and the multi-slice method.

In addition, various modifications can be made without departing from the gist of the present invention.

[Effects of the Invention] As described above, in the configuration according to claim 1 of the present invention, the MR which has a static magnetic field magnet, a gradient magnetic field coil, and a transmitter/receiver coil collects and images signals accompanying the magnetic resonance phenomenon of a specific atomic nucleus.
In a method of imaging brain surface structures using an I device, a cylindrical coil that can wrap around the head and that can perform at least one of transmission and reception is used to image the head of a subject regarding protons. A brain structure imaging sequence that suppresses signals from fat and emphasizes signals from water during one encoding process, and a normal sequence that does not suppress signals from fat and emphasizes signals from water. The multi-echo method that executes the imaging sequence is executed together with the multi-slice method to obtain a brain surface structure image and a normal image, and the brain structure imaging sequence is executed to wrap around the head. For each slice region close to a coil that is cylindrical and can perform at least one of transmission and reception, magnetic resonance signals from water within that region are enhanced and magnetic resonance signals from fat are suppressed. Since it is detected, it is possible to depict the sensational image of the water in the sensation of the head, and since the magnetic resonance signal from the fat is suppressed, the image of the fat does not overlap with the sensational image of the water, and it is possible to visualize the sensational image of the water. Brain surface structure images corresponding to each slice site suitable for diagnosing lesions present on the surface can be presented. In addition, since a cylindrical coil that can wrap around the head is used, it is easy to set up the coil and the object to be imaged (the head), allowing slices depicting the brain surface structure viewed from any direction. Images can be obtained, and by referring to each image, the positional relationship in the depth direction can be easily determined. in this case,
By encoding the normal imaging sequence as well as the brain structure imaging sequence, it is possible to simultaneously obtain and observe the brain surface structure image and the normal image in a single imaging session, improving diagnostic efficiency. be effective.

The configuration according to claim 2 or 3 is a static magnetic field magnet.

In a method of imaging the brain surface structure using an MRI device that has gradient magnetic field coils and transmitting and receiving coils and collects and images signals associated with the magnetic resonance phenomenon of specific atomic nuclei, a cylindrical shape that can wrap around the head is used. Using a coil that can perform at least one of transmitting and receiving, the subject's head is targeted for proton imaging, suppressing signals from fat and emphasizing signals from water during a single encoding process. A multi-echo method that executes a brain structure imaging sequence that does not suppress signals from fat and a normal imaging sequence that does not emphasize signals from water is executed together with a multi-slice method. A predetermined weight is attached to each of the multi-slice images obtained by executing the sequence, and each slice image to which this weight is attached is added, or a predetermined weight is attached to a matrix component and the weight is attached to this matrix component. The brain surface structure image is obtained by adding each slice image, and the brain surface structure image and the normal image are displayed.
In addition to achieving the same effect as using a surface coil, it is possible to prevent the overlap of strong signals from deep structures such as the brain, so surface structures of the brain are suitable for addition images. The images are accurately depicted, and since the voxels of each slice image during addition are small, the resulting added image has phase disturbances suppressed as much as possible.

In the configuration according to claim 4 of the present invention, in claim 2 or 3, when adding each slice image, the addition is performed while shifting the position of each slice image. In addition to achieving the effects of this configuration, by performing addition while shifting the position of each slice image, at least two images with different viewing directions can be obtained, and stereo viewing can be performed using the two images.

Therefore, according to the present invention according to claims 1 to 4, there is provided a method for imaging a brain surface structure using an MRI apparatus, which can obtain an image depicting the brain surface structure for diagnosing a lesion existing on the brain surface of the head. It is possible to provide

[Brief explanation of the drawing]

FIG. 1 is a diagram showing the configuration of a magnetic resonance imaging apparatus to which an embodiment of the method according to the present invention is applied, FIG. 2 is a diagram showing a sequence for imaging the brain surface structure in the same embodiment, and FIG. A diagram showing an example of multi-slice in the same embodiment, FIG. 4 is a diagram showing the sensitivity characteristics of the surface coil, FIGS. 5 and 6 are diagrams showing coefficients in addition processing, and FIG. 7 is a diagram showing stereo viewing. , FIG. 8 is a diagram showing a brain surface structure imaging sequence and a normal imaging sequence in the multi-echo method as another example. MA... Magnet assembly, 1... Static magnetic field coil, 2... Gradient magnetic field generation coil for x, y, and z axes, 3
... Implantable whole body probe, 4... Static magnetic field control system, 5... Transmitter, 6... Receiver, 7... X-axis gradient magnetic field power supply, 8... Y-axis gradient magnetic field Power source, 9... 2-axis gradient magnetic field power source, 10... Sequencer, 11... Combinator system, 12... Display device, 13... Head coil.

Claims (4)

[Claims] (1) A method of imaging the brain surface structure using an MRI device that has a static magnetic field magnet, a gradient magnetic field coil, and a transmitter/receiver coil and collects and images signals associated with the magnetic resonance phenomenon of specific atomic nuclei. Using a cylindrical coil that can be wrapped around and capable of at least one of transmitting and receiving,
A brain surface structure imaging sequence that targets the subject's head for proton imaging and suppresses signals from fat and emphasizes signals from water during a single encoding process, and suppresses signals from fat. A brain surface structure using an MRI apparatus characterized in that a multi-echo method that executes a normal imaging sequence without emphasizing signals from water and a multi-slice method is performed together with a multi-slice method to obtain a brain surface structure image and a normal image. imaging method. (2) In a method of imaging the brain surface structure using an MRI device that has a static magnetic field magnet, a gradient magnetic field coil, and a transmitting/receiving coil and collects and images signals associated with the magnetic resonance phenomenon of specific atomic nuclei, the head is Using a cylindrical coil that can be wrapped around and capable of at least one of transmitting and receiving,
A brain surface structure imaging sequence that targets the subject's head for proton imaging and suppresses signals from fat and emphasizes signals from water during a single encoding process, and suppresses signals from fat. A multi-echo method that performs a normal imaging sequence that does not emphasize signals from water and does not emphasize signals from water is performed together with a multi-slice method, and a predetermined A brain surface structure image is obtained by adding the weighted slice images, and the brain surface structure image and the normal image are displayed.
A method for imaging brain surface structures using an RI device. (3) In a method of imaging the brain surface structure using an MRI device that has a static magnetic field magnet, a gradient magnetic field coil, and a transmitting/receiving coil and collects and images signals accompanying the magnetic resonance phenomenon of specific atomic nuclei, Using a cylindrical coil that can be wrapped around and capable of at least one of transmitting and receiving,
A brain surface structure imaging sequence that targets the subject's head for proton imaging and suppresses signals from fat and emphasizes signals from water during a single encoding process, and suppresses signals from fat. The multi-echo method, which executes the normal imaging sequence without emphasizing the signal from water, is executed together with the multi-slice method, and the matrix components of each slice image obtained by executing this brain surface structure imaging sequence are An MRI apparatus characterized in that a predetermined weight is attached, each weighted slice image is added to this matrix component to obtain a brain surface structure image, and this brain surface structure image and a normal image are displayed. Imaging method for brain surface structures. (4) The method for imaging a brain surface structure using an MRI apparatus according to claim 2 or 3, characterized in that when adding up each slice image, the addition is performed while shifting the position of each slice image.