JPH0564058B2 - - Google Patents

Description

[Detailed Description of the Invention] [Object of the Invention] (Field of Industrial Application) The present invention is directed to magnetic resonance (MR).
The present invention relates to a magnetic resonance imaging device that can image the brain surface structure of a subject (living body) using the resonance phenomenon.

(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. It resonates at the angular frequency ω ₀ (ω ₀ =2πν ₀ , ν ₀ ; Larmor frequency) shown in .

ω ₀ =γH ₀ where γ is the gyromagnetic ratio specific to the type of atomic nucleus, and H ₀ is the static magnetic field strength.

The device that performs biological diagnosis using the above principles is
The electromagnetic waves of the same frequency as above that are induced after the above-mentioned resonance absorption are signal-processed to produce diagnostic information that reflects information such as nuclear density, longitudinal relaxation time T1, transverse relaxation time T2, flow, chemical shift, etc. The aim is to obtain slice images, etc., 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 demands for imaging images. from,
The actual device excites a specific region and collects its signals.

In this case, the specific region to be imaged is generally a slice region with a certain thickness, and magnetic resonance signals (MR signals) such as echo signals and FID signals from this slice region are collected many times. The data is collected by performing a data encoding process, and an image of the specific slice region is generated by subjecting these data groups to image reconstruction processing using, for example, a two-dimensional Fourier transform method.

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 brain surface structures such as cerebral sulci are an important guide to knowing the location of lesions localized in the cortex and subcortex. Accurate positioning is often 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 shaped like a cage so that it wraps around the head, so it collects signals from the entire head, so the images contain more information deep beneath the surface of the brain. As a result, it is not possible to meet the above-mentioned diagnostic requirements.

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 sulcal water and fat are collected in the same way without distinction, making it difficult to determine the location of lesions localized in the cortex or subcortex. There was a problem in that it was not possible to obtain brain surface structure images for diagnosis.

SUMMARY OF THE INVENTION Accordingly, an object of the present invention is to provide a magnetic resonance imaging apparatus capable of obtaining an image depicting a brain surface structure for diagnosing a lesion 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, the invention according to claim 1 of the present invention includes: a static magnetic field generating means for generating a static magnetic field; a gradient magnetic field generating means for generating a gradient magnetic field; and a high-frequency pulse for generating a magnetic resonance phenomenon related to protons. a receiving coil that detects an echo signal as a magnetic resonance signal related to protons and is placed close to the head of the subject; and a receiving coil that is placed in the static magnetic field. for applying the gradient magnetic field and high-frequency pulse to the subject under predetermined conditions, and for collecting at least two echo signals having different echo times from each of a plurality of slice sites of the subject's head; a control means for executing a pulse sequence; and when the control means is driven, an echo signal obtained from the reception coil with a short echo time related to the execution of the pulse sequence is processed to increase the echo time at the head. Obtaining a plurality of slice images based on short echo signals and processing echo signals with a long echo time related to execution of the pulse sequence obtained from the receiving coil to obtain an image depicting the brain surface structure in the head. a signal processing means; a display means for displaying an image depicting a brain surface structure in the head obtained by the signal processing means and a plurality of slice images based on the echo signal with a short echo time; It is characterized by

The invention according to claim 2 provides: a static magnetic field generating means for generating a static magnetic field; a gradient magnetic field generating means for generating a gradient magnetic field; and a high frequency pulse generating means for generating a high frequency pulse for generating a magnetic resonance phenomenon related to protons. a receiving coil that detects an echo signal as a magnetic resonance signal related to protons and is placed close to the head of the subject; Executing a pulse sequence for applying a gradient magnetic field and a high-frequency pulse under predetermined conditions and collecting at least two echo signals having different echo times from each of a plurality of slice regions of the head of the subject. a control means; when the control means is driven, reconstructing an echo signal with a short echo time related to the execution of the pulse sequence obtained from the receiving coil, based on the echo signal with a short echo time in the head; A plurality of slice images are obtained by reconstruction, and an echo signal having a long echo time related to the execution of the pulse sequence obtained by the receiving coil is reconstructed to obtain a plurality of slice images based on the echo signal having a long echo time in the head. a reconstruction means that obtains a brain in the head by giving a predetermined weight to each of a plurality of slice images based on the echo signal having a long echo time, and adding the weighted plurality of slice images. an addition means for obtaining an image in which a surface structure is depicted; an image in which a brain surface structure in the head obtained by the addition means is depicted; and an echo signal having a short echo time obtained by the reconstruction means; and display means for displaying a plurality of slice images based on the image data.

The invention according to claim 3 provides the following: static magnetic field generating means for generating a static magnetic field; gradient magnetic field generating means for generating a gradient magnetic field; and high-frequency pulse generating means for generating a high-frequency pulse for generating a magnetic resonance phenomenon related to protons. a receiving coil that detects an echo signal as a magnetic resonance signal related to protons and is placed close to the head of the subject; Executing a pulse sequence for applying a gradient magnetic field and a high-frequency pulse under predetermined conditions and collecting at least two echo signals having different echo times from each of a plurality of slice regions of the head of the subject. a control means; when the control means is driven, reconstructing an echo signal with a short echo time related to the execution of the pulse sequence obtained from the receiving coil, based on the echo signal with a short echo time in the head; A plurality of slice images are obtained by reconstruction, and an echo signal having a long echo time related to the execution of the pulse sequence obtained by the receiving coil is reconstructed to obtain a plurality of slice images based on the echo signal having a long echo time in the head. a reconstruction means that obtains by reconstruction, a predetermined weight is given to the matrix component of each of the plurality of slice images based on the echo signal having a long echo time, and the plurality of slice images having the weighted matrix components are added. an addition means for obtaining an image in which the brain surface structure in the head is depicted; an image in which the brain surface structure in the head obtained by the addition means is depicted; and an image in which the brain surface structure in the head is depicted, obtained by the reconstruction means. A display means for displaying a plurality of slice images based on an echo signal having a short echo time.

The invention according to claim 4 is characterized in that the adding means in the invention according to claim 2 or 3 is configured to add the plurality of slice images while shifting the position of each slice image. shall be.

The invention according to claim 5 is characterized in that the receiving coil in the invention according to any one of claims 1 to 3 has a cylindrical shape that can wrap around the head.

(Function) According to the invention according to claim 1, the control means executes a pulse sequence using a combination of a multi-slice method and a multi-echo method. This allows echo signals with short echo times (e.g. the first,
A plurality of slice images based on the echo signals having a short echo time in the head can be obtained by signal processing by reconstructing the second echo signal). Further, by signal processing an echo signal having a long echo time (for example, a third echo signal), it is possible to obtain an image depicting the brain surface structure in the head based on the echo signal having a long echo time in the head. . In this case, an image depicting the brain surface structure is created using detected echo signals from water that are emphasized and echo signals from fat that are suppressed. For this reason, a cerebral sulcus image is drawn due to the water in the cerebral sulci of the head, and since echo signals from fat are suppressed, the fat image is not superimposed on the water-based brain sulcus image. , a brain surface structure image suitable for diagnosing a lesion existing on the brain surface can be presented.

Therefore, the positional relationship in the depth direction can be easily known. In this case, it is possible to obtain a brain surface structure image and a normal image by executing a pulse sequence, which is a single imaging method, so that the brain surface structure image and the normal image can be observed simultaneously, improving diagnostic efficiency. is planned. Furthermore, since a brain surface structure image and a normal image can be obtained, imaging efficiency and diagnostic efficiency can be improved in this respect.

According to the invention according to claim 2, it is possible to obtain the same effect as the invention according to claim 1, and in addition, the brain surface structure image is created by applying a predetermined weight to each of a plurality of slice images based on an echo signal with a long echo time. Since it is obtained by adding a plurality of weighted slice images, phase disturbance is suppressed as much as possible.

According to the invention according to claim 3, it is possible to obtain the same effect as the invention according to claim 1, and the brain surface structure image is created using matrix components of each of a plurality of slice images based on echo signals having a long echo time. Since it is obtained by adding a plurality of slice images having predetermined weights and weighted matrix components, phase disturbance is suppressed as much as possible.

According to the invention according to claim 4, two images with different viewing directions can be obtained, and stereo viewing can be performed using these two images.

According to the invention according to claim 5, since the cylindrical receiving coil that can wrap around the head is used, the head to be photographed and the receiving coil can be easily set in any positional relationship, so that the receiving coil can be set easily and in any desired position. It is possible to obtain an image of the brain surface structure viewed from the direction.

(Example) An example of a magnetic resonance imaging 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, a magnet assembly MA capable of accommodating a subject P therein is equipped with a static magnetic field coil using a normal conducting or superconducting method (even if it is configured using a permanent magnet). ) 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 the induced magnetic resonance signals (MR signals: echo signals and FID signals), such as transmitting coils and receiving coils. 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 a static magnetic field control system 4 that performs customary control of the static magnetic field power supply, a transmitter 5 that performs RF pulse transmission control, and an induced MR signal reception control. receiver 6, gradient magnetic field generating coils 2 for X, Y, and Z axes
X-axis, Y-axis, and Z-axis gradient magnetic field power supplies 7, 8, and 9 that perform excitation control for each of and a computer system 1 that displays it.
1. Consists of a display device 12.

In addition, in this example, the magnetic assembly
The head PH of the subject P is placed at the center of the magnetic field of the MA, and as shown in FIG. 2, the head coil 13 is arranged as a cylindrical coil so as to surround the head PH. This head coil 13 is driven by a transmitter 5 or a receiver 6 in the same way as the implantable whole body probe 3, so that it can transmit and receive data.

Here, in the pulse sequence for data collection, the transmitter 5 is driven, 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 supply 7, 8 and 9, gradient magnetic fields Gx, Gy, and Gz are applied from the gradient magnetic field generating coil 2 for slicing, phase encoding, and reading, and signals from a specific region are sent to the receiving coil of the implantable whole body probe 3 or The head coil 13 collects the data. This sequence is repeated a predetermined number of times to obtain a data group,
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 imaging regarding protons, and fat signals are suppressed and water (cerebrospinal fluid: CSF) signals are emphasized. This sequence is based on the spin echo method or field echo method, and is executed in multi-slice mode. Here, in the spin echo method, for example, as shown in Fig. 2, the echo time T _E
is longer than usual, for example, about 250 msec (usually about 80 msec), and the pulse repetition interval is
T _R is set to about 2000 msec (usually about 500 msec). In addition, in the field echo method, the echo time T _E is set longer than usual, for example, about 20 to 30 msec (usually about 14 msec), and the pulse repetition interval T _R is set to 80 to 1000 msec.
sec (usually about 50 msec). Furthermore, the flip angle of the RF pulse is set to 10 to 20 degrees.

In addition, RF is the excitation pulse, Gs is the gradient magnetic field for slicing, in this case, the gradient magnetic field in the Z-axis direction, Gr is the gradient magnetic field for reading, which in this case is the gradient magnetic field in the X-axis direction, and Ge is the gradient magnetic field for encoding. In this case, it 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 such condition settings, an RF pulse is transmitted by the transmitting coil or head coil 13 of the implantable whole body probe 3, and a gradient magnetic field Gs for slicing is applied from the gradient magnetic field generating coil 2, and then the lead is reversed. Adding a gradient magnetic field Gr and a gradient magnetic field Ge for phase encoding with variable intensity, the echo time is
Echo signals are collected from the multi-slice region using the head coil 13 at T _E. 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).
It is displayed on the display device 12.

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

Addition processing methods 1, 2, and 3 described below are methods to obtain sensitivity characteristics similar to those using surface coils and to obtain a signal suppression effect depending on the position (depth) of the lesion (region of interest). Yes, addition processing method 4
is a method for obtaining images for stereo viewing.

<Addition processing method 1> N multi-slice images (matrix)
Let Mk (i, j). k=1, 2,..., N, i,
j = 1 to 256 (matrix).

The image obtained by weighted addition of these images is S(i,
j).

S(i, j)= _N 〓 ^k=1 ak·Mk(i, j) Here, for ak, a value (coefficient) corresponding to, for example, the sensitivity of the surface coil is used. Figure 4 is a characteristic diagram showing the relationship between the depth of the surface coil and the sensitivity.
For example, if a lesion exists at a position 5 cm away from the coil (head coil 13) and you want to clearly visualize the lesion with the same characteristics as when using a surface coil, then follow the method shown in Figure 4. If we determine ak, we get the following.

a1=1.0, a2=0.9, a3=0.75, a4=0.6, a5=
0.5... That is, by selecting the value of the coefficient ak attached to each slice image to an appropriately smaller value as the slice position becomes deeper, signals in deep parts such as the ventricles and basal ganglia are suppressed, and as a result, Signals from deep areas such as the ventricles and basal ganglia are suppressed, and they no longer overlap in the cerebral sulcus image.

Therefore, in the image displayed on the display device 12, the cerebral sulci are 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
This method obtains the same characteristics as the surface coil, and also selects the value of the weighting coefficient ak according to the position (depth) of the lesion.

That is, as shown in FIG. 5a, 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. 5b, a1=1.0, a2=0.9, a3=0.6, a4=0.2, etc. are selected. When selected in this way, water (CSF) signals from deep slices such as in the ventricle are suppressed for addition, and signal overlap is also suppressed.As a result, the addition image is shallow. This clearly depicts the brain surface structure, including the location of the lesion.

Contrary to the above, as shown in FIG. 6a, when the lesion exists in a deep position, the degree of decrease in ak is reduced. For example, as shown in FIG. 6b, a1=1.0, a2=0.95, a3=0.8, a4=0.7, etc. are selected.

<Addition processing method 3> In addition processing methods 1 and 2, a weighting coefficient ak is attached to each slice image, but in addition processing method 3, a weighting coefficient ak is attached to matrices i and j, which are internal elements of each slice image. A weighting factor ak is assigned accordingly.

S (i, j) = _N 〓 ^{k = 1} ak (i, j)・Mk (i, j) For example, if you want to emphasize the brain surface in particular, by selecting ak as below, you can It becomes heavier in shape.

ak (i, j) = √ (-) ^{2 2} + (-128) ² 12
8 ² + (-128) ² 128 ² k=1, 2, 3,..., N, i, j=1, 2,
3,...,256 <Addition processing method 4> Addition processing method 4 enables stereo viewing through addition processing. In other words, when performing weighted addition in addition processing methods 1, 2, and 3, the viewing direction can be changed by shifting the position of each slice image, and as a result, the viewing direction can be changed without scanning two images with different viewing directions. , enables stereo viewing with only one multi-slice image.

That is, given Δi and Δj, S′=(i,j)= _N 〓 ^k=1 ak・Mk(i+k(Δi), j+k(Δj)), images S(i,j)′ with different viewing directions are obtained. Create. In this case, when Δi and Δj are non-integers, interpolation such as linear interpolation is performed as appropriate to create an image.

For example, if the pixels of the image Mk (i, j) are 1
mm, and the slice thickness is 10 mm.

If Δi=1 (that is, 1 mm) and Δj=0, then the seventh
As shown in the figure, approximately 5.7° from the line of sight (= tan ^-1 1/
10), and it becomes possible to perform stereo viewing using images S and S'.

The present applicant has previously filed a patent application for an invention related to this embodiment. Future application (Showa 62
In the invention described in the specification and drawings of Japanese Patent Application No. 62-232949 filed on September 17, 2007 (title of the invention "Magnetic Resonance Imaging Method"), a surface coil is used, and the slice thickness is approximately 8 cm. Slice and
A spin echo method in which the echo time is set longer than usual (2 msec) and the pulse repetition interval T _R is set longer than usual (2000 msec) obtains the same effect as in this example, that is, brain surface structure images ( SAS images (Surface Anatomy Scan) can be obtained.

The above embodiment has the following advantages compared to the invention of the earlier application. That is, it is possible to capture a SAS image viewed from a desired direction without being specified by the installation position of the surface coil, unlike the invention of 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 performing addition, by appropriately adjusting the weighting coefficient according to the location of the lesion and the case, it becomes possible to obtain a SAS image that accurately represents the location of the lesion and the case. Stereo viewing can be performed without rescanning in a different viewing direction. Since the slice thickness is small, the voxels during imaging are small, so phase disturbances are small and signal degradation is small.

In addition, in the invention related to the previous related application, for example, if the pulse repetition interval T _R is 2 seconds and the encoding is 256 times, the data collection time is 2 × 256 =
It takes 512 seconds, but if the field echo method is used in this example, the pulse repetition interval T _R will be 80 to 1000 m.
sec is sufficient, so 0.08 seconds (1.0) x 256 = 20.48 (256)
This is advantageous because data collection can be completed in an extremely short time.

In both of the above examples (those using the sequence shown in Figure 2), one echo signal is obtained by one encoding, and N times of encoding is required to image an N×N matrix. Although this is an example of a single-echo method requiring a single echo method, it can be extended to an embodiment that utilizes the sequence of FIG. 2 as a means for obtaining one echo signal in a multi-echo method.

FIG. 8 shows one encoding pulse sequence of the multi-echo method of this embodiment,
The third echo signal is the same as the echo signal shown in FIG. The first echo signal has an echo time T _E of about 20 msec, the second echo signal has an echo time T _E of about 120 msec, and the pulse repetition interval T _R is about 2000 msec, the same as in FIG. 2. That is, N×N of the sequence shown in FIG.
By performing encoding N times to image the matrix, it is possible to obtain a density-weighted image for the image based on the first echo signal, and a T2 _- weighted image for the image based on the second echo signal. It's getting old. Therefore, the sequence for obtaining the first echo signal and the second echo signal is a sequence for obtaining images used for normal clinical examinations, and the sequence for obtaining the third echo signal is for obtaining brain surface structure images. It is a sequence to obtain.

In this way, the normal imaging sequence is encoded along with the brain surface structure imaging sequence, and a brain surface structure image and a normal image can be obtained and observed simultaneously in a single imaging session, improving diagnostic efficiency. It will be done. For the 3 multi-echo method shown in Figure 8,
The number of multi-slices can be about 6.

Note that the multi-echo method in the above example is 1
Although it is assumed that three echo signals are obtained by one encoding, the present invention can be applied to obtaining two echo signals or obtaining four echo signals. For example, in two echoes, the first echo signal has an echo time T _E of about 120 msec as a normal imaging sequence, and the echo time T _E of the second echo signal is 250 msec as a brain surface structure imaging sequence.
Approximately sec.

In addition, for 4 echoes, the normal imaging sequence is the first echo signal with an echo time T _E of about 40 msec, the second echo signal with an echo time T _E of about 80 msec, and the third echo signal with an echo time T _E of about 120 msec. As an echo signal, the echo time T _E of the fourth echo signal is 250 m as a sequence for brain surface structure imaging.
Approximately sec.

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. That is, as a normal imaging sequence, the first echo signal is the echo time
T _E is about 20 msec, the second echo signal has an echo time T _E of 80 msec, and the third echo signal has an echo time T _E of 250 msec as a brain surface structure imaging sequence.
It should be about msec. However, pulse repetition interval T _R
is approximately 3000 msec. This will allow you to make about 10 slices.

In addition, as a normal imaging sequence, the first echo signal has an echo time T _E of about 20 msec, and the second echo signal has an echo time T _E of about 120 msec.
The echo time T _E of the third echo signal is set to about 200 msec as a brain surface structure imaging sequence. The pulse repetition interval T _R is approximately 2000 msec. This also makes it possible to slice about 10 pieces. However, as a sequence for brain surface structure imaging, the echo time T _E of the third echo signal is set to 200 m.
sec, so the contrast as a brain surface structure image is slightly reduced, but there is no problem with practicality.

Of course, the brain surface structure imaging sequence and the normal imaging sequence can be applied not only to the spin echo method but also to the field echo method, as well as 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, according to the present invention, it is possible to provide a magnetic resonance imaging apparatus capable of obtaining images depicting brain surface structures.

[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 supply,
9...Z-axis gradient magnetic field power supply, 10...Sequencer,
11... Computer system, 12... Display device, 13... Head coil.

Claims (1)

[Scope of Claims] 1. Static magnetic field generating means for generating a static magnetic field; Gradient magnetic field generating means for generating a gradient magnetic field; High-frequency pulse generating means for generating a high-frequency pulse for generating a magnetic resonance phenomenon related to protons. , a receiving coil that detects an echo signal as a magnetic resonance signal related to protons, the receiving coil being placed close to the head of the subject, and the tilting with respect to the subject being placed in the static magnetic field. Control for applying a magnetic field and high-frequency pulse under predetermined conditions, and for executing a pulse sequence for collecting at least two echo signals having different echo times from each of a plurality of slice sites of the head of the subject. means, when the control means is driven, signal processing is performed on an echo signal with a short echo time related to execution of the pulse sequence obtained from the receiving coil, and a plurality of echo signals based on the echo signal with a short echo time in the head are processed. a signal processing means for obtaining a slice image of the head and processing an echo signal having a long echo time related to execution of the pulse sequence obtained from the receiving coil to obtain an image depicting a brain surface structure in the head; A display means for displaying an image depicting the brain surface structure in the head obtained by the signal processing means and a plurality of slice images based on the echo signal having a short echo time. Magnetic resonance imaging device. 2. Static magnetic field generating means for generating a static magnetic field; Gradient magnetic field generating means for generating a gradient magnetic field; High frequency pulse generating means for generating a high frequency pulse for generating a magnetic resonance phenomenon related to protons; Magnetic resonance related to protons. The device detects an echo signal as a signal, and includes a receiving coil placed close to the head of a subject, and a receiving coil that applies the gradient magnetic field and high-frequency pulse to the subject placed in the static magnetic field. a control means for executing a pulse sequence for collecting at least two echo signals having different echo times from each of a plurality of slice regions of the head of the subject; is driven, reconstructing echo signals with a short echo time related to execution of the pulse sequence obtained from the receiving coil and reconstructing a plurality of slice images based on the echo signals with a short echo time in the head. and reconstructing an echo signal with a long echo time related to the execution of the pulse sequence obtained by the receiving coil to obtain a plurality of slice images based on the echo signal with a long echo time in the head by reconstruction. means: assigning a predetermined weight to each of a plurality of slice images based on the echo signal with a long echo time, and adding the weighted plurality of slice images to create an image depicting a brain surface structure in the head. an image depicting the brain surface structure in the head obtained by the addition means, and a plurality of slice images based on the echo signal with a short echo time obtained by the reconstruction means. A magnetic resonance imaging apparatus comprising: a display means for displaying a display; and a magnetic resonance imaging apparatus. 3. Static magnetic field generating means for generating a static magnetic field; Gradient magnetic field generating means for generating a gradient magnetic field; High frequency pulse generating means for generating a high frequency pulse for producing a magnetic resonance phenomenon related to protons; Magnetic resonance related to protons. The device detects an echo signal as a signal, and includes a receiving coil placed close to the head of a subject, and a receiving coil that applies the gradient magnetic field and high-frequency pulse to the subject placed in the static magnetic field. a control means for executing a pulse sequence for collecting at least two echo signals having different echo times from each of a plurality of slice regions of the head of the subject; is driven, reconstructing echo signals with a short echo time related to execution of the pulse sequence obtained from the receiving coil and reconstructing a plurality of slice images based on the echo signals with a short echo time in the head. and reconstructing an echo signal with a long echo time related to the execution of the pulse sequence obtained by the receiving coil to obtain a plurality of slice images based on the echo signal with a long echo time in the head by reconstruction. a means for attaching a predetermined weight to a matrix component of each of a plurality of slice images based on the echo signal having a long echo time, and adding the plurality of slice images having the weighted matrix components to obtain information about the brain in the head. an addition means for obtaining an image in which a surface structure is depicted; an image in which a brain surface structure in the head obtained by the addition means is depicted; and an echo signal having a short echo time obtained by the reconstruction means; 1. A magnetic resonance imaging apparatus, comprising: a display means for displaying a plurality of slice images based on the image. 4. Claim 2, wherein the adding means is configured to add the plurality of slice images while shifting the position of each slice image.
or the magnetic resonance imaging apparatus according to 3. 5. The magnetic resonance imaging apparatus according to claim 1, wherein the receiving coil has a cylindrical shape that can wrap around the head.