KR100610931B1 - Rf coil and magnetic resonance imaging method and apparatus - Google Patents

Abstract

To provide orthogonal RF coils with good frequency characteristics and magnetic resonance imaging methods and apparatus using the RF coils, a main path 602 connected in series via coupling paths 606, 608, 616, 618. 604) —The primary paths 602, 604, 612, 614 are not orthogonal when combining two coil loops that include orthogonal—, where the coupling paths 606, 608, 616, 618 do not overlap each other. Not made.

Description

RF Coil and Magnetic Resonance Imaging Method and Apparatus {RF COIL AND MAGNETIC RESONANCE IMAGING METHOD AND APPARATUS}             

1 is a block diagram of an exemplary apparatus in accordance with one embodiment of the present invention.

2 is a schematic diagram illustrating the configuration of a transmitting coil section in an apparatus according to an embodiment of the invention.

3 is a schematic diagram illustrating the configuration of a transmitting coil section in an apparatus according to an embodiment of the invention.

4 is a schematic diagram illustrating the configuration of a transmitting coil section in an apparatus according to an embodiment of the invention.

5 is a schematic diagram illustrating the configuration of a portion of a transmitting coil section in the apparatus.

6 is a schematic diagram illustrating an example pulse sequence executed by the apparatus.

Explanation of symbols for the main parts of the drawings

2: generating static field 4, 4 ': gradient coil section

6, 6 ': transmitting coil section 10: imaging table

8: subject 16: gradient driving section

18: transmitter section 20: receiver section

22: A-D Converter Section 24: Computer

30: control section 32: display section

34: action section 64: main path

106: receiving coil section

The present invention relates to a radio frequency (RF) coil and a magnetic resonance imaging method and apparatus, and more particularly to an RF in a direction parallel to the loop surface of the coil. An RF coil for generating a magnetic field, and a magnetic resonance imaging method and apparatus using the RF coil.

Magnetic resonance imaging devices having a direction of static magnetic field perpendicular to the body axis of a subject are generally referred to as vertical magnetic resonance imaging devices, which create an open static magnetic space and thus the pole piece of the static magnetic field generating unit. An RF coil having a loop surface parallel to the pole piece is used as an RF magnetic field generating RF coil. This type of RF coil generates an RF magnetic field in a direction parallel to the coil loop surface, forming an RF magnetic field perpendicular to the direction of the static magnetic field. Such RF coils are disclosed in U.S. Patent 5,760,583.

On the other hand, it consists of a combination of two RF coils and can provide an increased RF magnetic field through the vector component of each RF magnetic field generated by the two RF coils or drive power per coil to generate an RF magnetic field of desired intensity. There is another type of RF coil called a quadrature RF coil.

It is an object of the present invention to provide a spherical RF coil having good frequency characteristics and a magnetic resonance imaging method and apparatus using the RF coil.

According to a first aspect of the invention, when three mutually orthogonal directions are represented in the x direction, the y direction and the z direction, a first electrical path extending in the x direction and a second parallel to the first electrical path in the xy plane An electrical path, a third electrical path parallel to the first electrical path in the xz plane, and a fourth parallel to the third electrical path in the plane parallel to the xy plane and parallel to the second electrical path in a plane parallel to the xz plane The electrical path and the first and second electric paths to transmit respective currents in the same direction and the third and fourth electric paths to transmit respective currents in the same direction opposite to the directions of the first and second electric paths. A fifth electrical path connecting the first to fourth electrical paths in series, a sixth electrical path extending in the y direction in the xy plane, a seventh electrical path parallel to the sixth electrical path in the xy plane, and the yz plane The eighth electricity parallel to the sixth electrical path in the The path, the ninth electrical path parallel to the eighth electrical path in a plane parallel to the xy plane and parallel to the seventh electrical path in a plane parallel to the yz plane, and the sixth and seventh electrical paths share the same current. And a tenth electrical path connecting the sixth to ninth electrical paths so as to transmit in the direction and the eighth and ninth electrical paths transmit respective currents in the same direction opposite to the directions of the sixth and seventh electrical paths. The RF coil—the fifth electrical path and the tenth electrical path do not overlap each other in the z direction—is provided.

According to a second aspect, there is provided an RF coil as described with respect to the first aspect, wherein one of the fifth and tenth electrical paths in the RF coil coil is located inside the other electrical path in the xy plane, The other of the ten paths is located inside of one of the fifth and tenth electrical paths in a plane parallel to the xy plane.

According to a third aspect of the invention, when three mutually orthogonal directions are represented in the x direction, the y direction and the z direction, a first electrical path extending in the x direction and a second parallel to the first electrical path in the xy plane An electrical path, a fifth electrical path in series connecting the first and second electrical paths so that the first and second electrical paths transmit respective currents in the same direction, and a sixth electrical path extending in the y direction in the xy plane And a seventh electrical path parallel to the sixth electrical path in the xy plane, and a tenth electrical path connecting the sixth and seventh electrical paths in series such that the sixth and seventh electrical paths transmit respective currents in the same direction. An RF coil comprising a fifth electrical path and a tenth electrical path are provided not overlapping each other in the z direction.                         

According to the fourth aspect, when the three mutually orthogonal directions are displayed in the x direction, the y direction, and the z direction in the space where the subject is located, generating a static magnetic field in the z direction, and a gradient magnetic field within the space. fields), generating a high frequency magnetic field in the space, measuring a magnetic resonance signal from the space, and generating an image based on the measured magnetic resonance signal; A magnetic resonance imaging method is provided, wherein generating a high frequency magnetic field comprises: a first electrical path extending in the x direction, a second electrical path parallel to the first electrical path in the xy plane, and a first electrical path in the xz plane; A third electrical path that is parallel, and a fourth electrical path that is parallel to the third electrical path in a plane parallel to the xy plane and parallel to the second electrical path in a plane parallel to the xz plane; The first and second electrical paths transmit respective currents in the same direction, and the third and fourth electrical paths transmit respective currents in the same direction opposite to the directions of the first and second electrical paths. A fifth electrical path connecting the fourth electrical path in series, a sixth electrical path extending in the y direction in the xy plane, a seventh electrical path parallel to the sixth electrical path in the xy plane, and a sixth electrical in the yz plane An eighth electrical path parallel to the path, a ninth electrical path parallel to the eighth electrical path in a plane parallel to the xy plane and parallel to the seventh electrical path in a plane parallel to the yz plane, and sixth and seventh electrical The sixth-ninth electrical paths are connected in series such that the paths transmit respective currents in the same direction and the eighth and ninth electrical paths transmit respective currents in the same direction opposite to the directions of the sixth and seventh electrical paths. 10th electric path to the po The fifth coil and tenth electrical paths containing RF coils are implemented using non-overlapping ones in the z direction.

According to the fifth aspect, static magnetic field generating means for generating a static magnetic field in the z direction when three mutually orthogonal directions are displayed in the x direction, the y direction, and the z direction in the space where the subject is located, and a gradient magnetic field within the space. gradient magnetic field generating means for generating gradient magnetic fields, high frequency magnetic field generating means for generating a high frequency magnetic field in the space, measuring means for measuring a magnetic resonance signal from the space, and magnetism measured by the measuring means There is provided a magnetic resonance imaging apparatus including image generating means for generating an image based on a resonance signal, wherein the means for generating a high frequency magnetic field comprises: a first electrical path extending in the x direction, and a first electrical path in the xy plane; A second parallel electrical path, a third electrical path parallel to the first electrical path in the xz plane, and a third electrical path in a plane parallel to the xy plane A fourth electrical path parallel to the path and parallel to the second electrical path in a plane parallel to the xz plane, the first and second electrical paths transmitting respective currents in the same direction, and the third and fourth electrical paths A fifth electrical path connecting the first to fourth electrical paths in series to transmit respective currents in the same direction opposite the directions of the first and second electrical paths, and a sixth electrical path extending in the y direction in the xy plane; a seventh electrical path parallel to the sixth electrical path in the xy plane, an eighth electrical path parallel to the sixth electric path in the yz plane, and a yz plane parallel to the eighth electrical path in a plane parallel to the xy plane A ninth electrical path parallel to the seventh electrical path in a parallel plane, and the sixth and seventh electrical paths transmit respective currents in the same direction, and the eighth and ninth electrical paths respectively transmit the sixth and sixth electrical paths. 7 the opposite of the direction of the electrical path An RF coil comprising a tenth electrical path connecting the sixth to ninth electrical paths to transmit in the same direction—the fifth electrical path and the tenth electrical path do not overlap each other in the z direction.

In any one invention as described with respect to the first to fifth aspects, the pair of electrical paths intersecting with each other in the xy plane is interlaced because the quality between each RF magnetic field generated by the electrical path pair is improved. It is desirable to intersect the interlaced intersection.

In the present invention, the connection between the coils through the drift capacity is reduced because the coupling paths do not overlap each other in the z direction.

Accordingly, according to the present invention, a spherical RF coil having good frequency characteristics and a magnetic resonance imaging method and apparatus using the RF coil can be implemented.

Other objects and advantages of the present invention will become apparent from the following description of the preferred embodiments of the invention illustrated in the accompanying drawings.

Embodiments of the present invention will now be described in more detail with reference to the accompanying drawings. 1 shows a block diagram of a magnetic resonance imaging apparatus, which is an embodiment of the invention. The configuration of the device represents one embodiment of the device according to the invention and the operation of the device represents one embodiment of the method according to the invention.

As shown in FIG. 1, the apparatus comprises a static magnetic field generating section 2 which generates a homogeneous static magnetic field in the interior space. The static field generating section 2 represents one embodiment of the static field generating means of the present invention. The static magnetic field generating section 2 includes a pair of magnetic generators, such as permanent magnets, which are oriented in the vertical direction to each other at regular intervals, to generate a static magnetic field (vertical magnetic field) in the intervening space. Obviously, the magnetic generator is not limited to a permanent magnet, but may be a superconducting electromagnet, a standard conducting electromagnet, or the like.

Gradient coil sections 4 and 4 'and transmitting coil sections 6 and 6' which face each other in the vertical direction at regular intervals are arranged in the internal space of the static field generating section 2. The transmitting coil sections 6, 6 ′ represent one embodiment of the RF coil of the present invention. The description of the transmitting coil sections 6, 6 ′ will be made later.

The subject 8 is placed on the imaging table 10 and is transferred to the space between the transmitting coil sections 6, 6 'facing by means of a conveying means (not shown). The body axis of the subject 8 is orthogonal to the direction of the static magnetic field. The imaging table 10 is attached with a receiving coil section 106 surrounding the position of the subject 8 to be imaged. The receiving coil section 106 is for example imaging the lumbar spine (L spine) and is attached and surrounds the hip of the subject 8. The receiving coil section 106 may be placed not only around the lumbar bone but also at any location corresponding to the desired location to be imaged.

The gradient coil sections 4, 4 ′ are connected to the gradient drive section 16. The gradient drive section 16 supplies a drive signal to the gradient coil sections 4, 4 'to create a gradient magnetic field. The gradient coil sections 4, 4 ′ and the gradient drive section 16 together represent one embodiment of the gradient magnetic field generating means of the present invention. The gradient magnetic fields to be generated are the next three magnetic fields: a slice gradient magnetic field, a readout gradient magnetic field and a phase-encoding gradient magnetic field.

The transmitting coil sections 6, 6 ′ are connected with the transmitter section 18. The transmitter section 18 supplies a drive signal to the transmitting coil sections 6, 6 'to generate an RF magnetic field, thereby exciting the spin in the subject 8. The transmitting coil sections 6, 6 ′ and the transmitter section 18 together represent one embodiment of the high frequency magnetic field generating means of the present invention.

The receiving coil section 106 receives a magnetic resonance signal generated by the spin excited in the subject 8. The receiving coil section 106 is connected to the input of the receiver section 20 and inputs the received signal to the receiver section 20.

The output of the receiver section 20 is connected to the input of an analog-to-digital converter section 22. The A-D converter section 22 converts the output signal of the receiver section 20 into a digital signal.

The receiving coil section 106, the receiver section 20 and the A-D converter section 22 together represent one embodiment of the measuring means of the invention. The output of the A-D converter section 22 is connected to the computer 24.

The computer 24 receives the digital signal from the A-D converter section 22 and stores the signal in a memory (not shown). Thus, data space is formed in the memory. The data space constitutes a two-dimensional Fourier space. The computer 24 performs two-dimensional inverse Fourier transform on the data in the two-dimensional Fourier space to reproduce an image of the subject 8. The computer 24 represents one embodiment of the image generating means of the present invention.

The computer 24 is connected to the control section 30. The control section 30 is connected to the gradient drive section 16, the transmitter section 18, the receiver section 20 and the A-D converter section 22. The control section 30 controls the gradient drive section 16, the transmitter section 18, the receiver section 20 and the AD converter section 22 based on the instructions supplied from the computer 24 to provide magnetic resonance imaging. Run

The computer 24 is connected with the display section 32 and the operation section 34. The display section 32 displays the reproduction image and various information output from the computer 24. The operation section 34 is operated by an operator who enters various commands and information into the computer 24.

2 schematically shows the configuration of the transmitting coil sections 6, 6 ′. 2 illustrates the three-dimensional structure of the electrical path of the RF coil, which constitutes the main part of the transmitting coil sections 6, 6 ′. The three mutually orthogonal directions in three-dimensional space are called x, y, z. The z direction is the static magnetic field direction. As shown, the transmitting coil section 6 has an electrical path configured in the x-y plane, and the other transmitting coil section 6 'has an electrical path configured in another x-y plane away from the previous x-y plane in the z direction.

The transmitting coil section 6 has two parallel main paths 602, 604 extending in the x direction. Primary paths 602 and 604 represent embodiments of the first and second electrical paths of the present invention, respectively.

One end of the main path 602 is connected to the transmitter section 18 and the other end is connected to one end of the main path 604 via the coupling path 606. The joining path 606 bypasses the x-y plane on the side opposite to where the main path 604 is located and connects the other end of the main path 602 and one end of the main path 604.

Although the engagement path 606 is illustrated as a straight path, for example bent at 90 ° at a corner and moving around, the engagement path 606 is not limited to this and is usually the main at the other end of the main path 602. It may be a semi-circular line or a suitable curve moving around to one end of the path 604. This also applies to similar components described below.

The other end of main path 604 is connected to one end of coupling path 610 via bypass path 608 bypassing on the side opposite to the side where main path 602 is located. The coupling path 610 connects the transmitting coil sections 6, 6 ′.

Although the engagement path 608 is illustrated as a straight line, for example, bent 90 ° at a corner and moving around, the engagement path 608 is not limited to this and is usually defined at the other end of the main path 604. It may be a semicircular line or a suitable curve moving around to one end of 610. This also applies to similar components described below.

The transmitting coil section 6 also has two parallel main paths 612, 614 extending in the y direction. Main paths 612 and 614 represent embodiments of the sixth and seventh paths of the present invention, respectively.

One end of the main path 612 is connected to the transmitter section 18, and the other end of the main path 612 is connected to one end of the main path 614 via the coupling path 616. The coupling path 616 bypasses the x-y plane on the side opposite to the side where the main path 614 is located and connects the other end of the main path 612 with one end of the main path 614. The bond path 616 is configured to pass outside of the bond paths 606 and 608.

The other end of main path 614 is connected to one end of coupling path 610 ′ via a coupling path 618 that bypasses on the opposite side of main path 612. The coupling path 610 'connects the transmitting coil sections 6, 6'. The coupling path 618 is configured to pass outside of the coupling paths 606 and 608.

Depending on the electrical path configuration, the main paths 602 and 604 and the main paths 612 and 614 are orthogonal to each other in the xy plane, and the coupling paths 616 and 618 are outside of the coupling paths 606 and 608 in the xy plane. Located in

The transmitting coil section 6 'has two parallel main paths 602', 604 'extending in the x direction. Main paths 602 ', 604' represent embodiments of the third and fourth electrical paths of the present invention, respectively.

One end of the main path 602 'is connected to the transmitter section 18, and the other end of the main path 602' is connected to one end of the main path 604 'via the coupling path 606'. . The coupling path 606 'bypasses the x-y plane on the side opposite the side where the main path 604' is located and connects the other end of the main path 602 'with one end of the main path 604'. The other end of main path 604 'is connected to the other end of coupling path 610 via a coupling path 608' bypassing the main path 602 'on the opposite side.

The transmitting coil section 6 'also has two parallel main paths 612', 614 'extending in the y direction. Main paths 612 '614' represent embodiments of the eighth and ninth electrical paths of the present invention, respectively.

One end of the main path 612 'is connected to the transmitter section 18, and the other end of the main path 612' is connected to one end of the main path 614 'via the coupling path 616'. . The coupling path 616 'bypasses on the x-y plane on the opposite side of the main path 614' and connects the other end of the main path 612 'with one end of the main path 614'. The bond path 616 'is configured to pass through the interior of the bond paths 606', 608 '.

The other end of main path 614 'is connected to the other end of coupling path 610' via a coupling path 618 'bypassing on the opposite side of main path 612'. The bond path 618 ′ is configured to pass through the interior of the bond paths 606 ′ and 608.

According to the electrical path configuration, the main paths 602 'and 604' and the main paths 612 'and 614' are orthogonal to each other in the xy plane, and the coupling paths 616 'and 618' are combined in the xy plane. 606 ', 608').

In the transmitting coil sections 6, 6 ', the main paths 602, 604, 602', 604 'are coupled paths 606, 608, 606', 608 'in one-stroke continuous lines. 610 is connected in series. This is the same direction of current flowing through the main paths 602 and 604 and the same direction of current flowing through the main paths 602 'and 604' but opposite to the direction of current flowing through the main paths 602 and 604. Form an in-coil loop (indicated by a solid line). Coupling paths 606, 608, 606 ', 608', 610 together represent one embodiment of a fifth electrical path of the present invention.

Likewise, main paths 612, 614, 612 ′ 614 ′ are continuously connected in one stroke continuous line by coupling paths 616, 618, 616 ′ 618 ′, 610 ′, and through main paths 612, 614. To form coil loops (dotted lines) with the same direction of current flowing and having the same direction of current flowing through main paths 612 'and 614' but opposite to the direction of current flowing through main paths 612 and 614. do. Coupling paths 616, 618, 616 ', 618', 610 'together represent one embodiment of the tenth electrical path of the present invention.

The coil loop indicated by the solid line and the coil loop indicated by the dotted line have respective main paths orthogonal to each other in the x-y plane, thereby forming a so-called quadrature coil. Thus, by supplying respective RF currents having the same phase to the two coil loops, an RF field having increased intensity can be obtained through vector synthesis of each RF magnetic field generated by the coil loop. Furthermore, by supplying each of the RF currents with phases different from each other by 90 ° to the two coil loops, an RF magnetic field rotating in a plane perpendicular to the z direction results in vector synthesis of each RF magnetic field generated by the coil loop. Can be obtained through

Depending on the orthogonal coils, the coupling paths 606 and 608 and the coupling paths 616 'and 618' in the inner path on the x-y plane, respectively, in the z direction are configured to have the same length. Similarly, the coupling paths 616 and 618 and the coupling paths 606 'and 608' in the outer path on both x-y planes are configured to have the same length. Thus, both coil loops have the same overall length. Thus, for the transmitter section 18, the respective load conditions on the two coil loops are the same, enabling even RF driving.

If the inequality can be tolerated to some extent, the coupling paths 606, 608, 606 ', 608' of the coil loop shown in solid lines, as shown for example in FIG. 3, are indicated by dotted lines on the two xy planes. It can be placed inside the coupling paths 616, 618, 616 ', 618' of the coil loop, and vice versa.

Moreover, an orthogonal coil loop need not always be formed across two x-y planes, and the orthogonal coil loop may be configured on only one x-y plane, as shown for example in FIG. 4.

Copper foil, for example, is used as the conductive material for producing the coil loop having the pattern described above on the x-y plane. Copper foils are used to form coil patterns, including, for example, flat electrical paths on insulating materials, such as plastic substrates, that are, for example, tens of micrometers thick, several centimeters wide or ten centimeters wide.

In this case, the two intersecting main paths are insulated by suitable means. Moreover, one of the two bonding paths is outside or inside the other path in the x-y plane, and the two bonding paths are spaced apart from one another at a distance equal to, for example, the width of the copper foil. Thus, the two coil loops do not overlap each other in the portion of the coupling path that occupies most of the total length. Thus, the coupling between two coil loops through the drift capacity is significantly reduced, providing an orthogonal coil with good frequency characteristics.

In addition, in that each RF magnetic field generated by the two coil loops is equalized, for example, as shown in FIG. 5, the two main paths preferably intersect and cross each other.

Hereinafter, the operation of the apparatus will be described. The apparatus is operated under the control of the control section 30. The following description relates to imaging by the spin-echo technique as a specific example of magnetic resonance imaging. The spin echo technique uses a plus sequence as signed by way of example in FIG.

6 is a schematic diagram of a plus sequence for collecting a magnetic resonance signal (spin echo signal) during one observation. The plus sequence is repeated for example 256 times to collect the spin echo signal for 256 observations.

The execution of the plus sequence and the collection of spin echo signals are controlled by the control section 30. However, magnetic resonance imaging is not limited to being performed using spin echo techniques, and various other techniques, such as gradient echo techniques, can certainly be used.

As shown in Fig. 6 (6), the plus sequence is divided into four periods (a)-(d) along the time axis. First, RF excitation is obtained at 90 ° plus P90 in the period (a) shown in (1). RF excitation is excited by the transmitting coil sections 6, 6 ′ driven by the transmitter section 18. Since the transmitting coil sections 6, 6 'are composed of orthogonal RF coils configured as described above in order to have good frequency characteristics, RF excitation can be performed very difficult.

Along with the RF excitation, the slice gradient magnetic field Gs is applied as shown in (2). The application of the slice gradient magnetic field Gs is effected by the gradient coil sections 4, 4 'driven by the gradient drive section 16. The spin is thus excited at a predetermined slice in the subject 8 (selective excitation).

Next, the phase-coded gradient magnetic field Gp is applied in the period b shown in (3). The application of the phase-coded gradient magnetic field Gp is also performed by the gradient coil sections 4 and 4 'driven by the gradient drive section 16.

Also, rephasing of spins in the phase coding period is made by the slice gradient magnetic field Gs as shown in (2). Moreover, the read gradient magnetic field Gr is applied to dephase the spin as shown in (4). The application of the read gradient magnetic field Gr is also performed by the gradient coil sections 4 and 4 'driven by the gradient drive section 16.

Then, 180 ° plus P180 is applied in period (c) as shown in (1), causing the spin to be reversed. Inversion of the spin is performed by the transmitting coil sections 6, 6 ′. Since the transmitting coil sections 6, 6 'are composed of orthogonal RF coils configured as described above in order to have good frequency characteristics, the inversion of the spin may be performed very efficiently.

Next, the read gradient magnetic field Gr is applied in the period d as shown in (4). This generates the spin echo signal MR from the subject 8 as shown in (5).

The spin echo signal MR is received by the receiving coil section 106. The receiving coil section 106 receives the spin echo signal of the lumbar bone. The received signal is input to the computer 24 via the receiver section 20 and the A-D converter section 22. The computer 24 stores the input signal of the receiving coil section 106 in the memory as measurement data. Thus, spin echo data for one observation is collected in the receive coil section 106 into memory.

The operation is repeated for example 256 times in a predetermined cycle, for example. The phase coding gradient magnetic field Gp is changed during each repetition period, so that the phase coding is different each time. This is represented by a number of dotted lines in the waveform of FIG. 6 (3).

The computer 24 executes image reproduction based on the spin echo data for all observations collected in the memory, and generates an image of the lumbar bone. Therefore, the generated image is displayed as a visible image in the section 32 at the time of display.

Many very different embodiments of the invention can be constructed without departing from the spirit and scope of the invention. The invention is not limited to the specific embodiments described in the specification, except as defined in the appended claims.

As described above, according to the present invention, there is provided an RF coil for generating an RF magnetic field in a direction parallel to the loop surface of the coil, and a magnetic resonance imaging method and apparatus using the RF coil.

Claims (5)

In the RF coil, When three mutually orthogonal directions are displayed in the x direction, the y direction, and the z direction, a first electrical path extending in the x direction, a second electrical path parallel to the first electrical path in an x-y plane, a third electrical path parallel to the first electrical path in an x-z plane, A fourth electrical path parallel to the third electrical path in a plane parallel to the x-y plane and parallel to the second electrical path in a plane parallel to the x-z plane, Wherein the first and second electrical paths transmit respective currents in the same direction and the third and fourth electrical paths transmit respective currents in the same direction opposite to the directions of the first and second electrical paths. A fifth electrical path connecting the first to fourth electrical paths in series, A sixth electrical path extending in the y direction in the x-y plane, A seventh electrical path parallel to the sixth electrical path in the x-y plane, an eighth electrical path parallel to the sixth electrical path in a y-z plane, A ninth electrical path parallel to the eighth electrical path in a plane parallel to the x-y plane and parallel to the seventh electrical path in a plane parallel to the y-z plane, Wherein the sixth and seventh electrical paths transmit respective currents in the same direction and the eighth and ninth electrical paths transmit respective currents in the same direction opposite to the directions of the sixth and seventh electrical paths. Tenth electrical path connecting the sixth to ninth electrical paths—The fifth and tenth electrical paths do not overlap each other in the z direction. RF coil comprising a. The method of claim 1, One of the fifth and tenth electrical paths is located inside another electrical path in the xy plane, and the other of the fifth and tenth electrical paths is in the plane parallel to the xy plane And an RF coil located inside one of the tenth electrical paths. In the RF coil, When three mutually orthogonal directions are displayed in the x direction, the y direction, and the z direction, a first electrical path extending in the x direction, a second electrical path parallel to the first electrical path in an x-y plane, A fifth electrical path connecting the first and second electrical paths in series such that the first and second electrical paths transmit respective currents in the same direction; A sixth electrical path extending in the y direction in the x-y plane, A seventh electrical path parallel to the sixth electrical path in the x-y plane, A tenth electric path connecting the sixth and seventh electric paths in series such that the sixth and seventh electric paths transmit respective currents in the same direction—the fifth and tenth electric paths are mutually different in the z direction. Do not overlap━ RF coil comprising a. When three mutually orthogonal directions are displayed in the x, y and z directions in the space where the subject is located, Generating a static field in the z direction, Generating gradient magnetic fields in the space, generating a high frequency magnetic field in the space, Measuring a magnetic resonance signal from the space; Generating an image based on the measured magnetic resonance signal As a magnetic resonance imaging method comprising: Generating the high frequency magnetic field A first electrical path extending in the x direction, a second electrical path parallel to the first electrical path in an x-y plane, a third electrical path parallel to the first electrical path in an x-z plane, A fourth electrical path parallel to the third electrical path in a plane parallel to the x-y plane and parallel to the second electrical path in a plane parallel to the x-z plane, Wherein the first and second electrical paths transmit respective currents in the same direction and the third and fourth electrical paths transmit respective currents in the same direction opposite to the directions of the first and second electrical paths. A fifth electrical path connecting the first to fourth electrical paths in series, A sixth electrical path extending in the y direction in the x-y plane, A seventh electrical path parallel to the sixth electrical path in the x-y plane, An eighth electrical path parallel to the sixth electrical path in the y-z plane, A ninth electrical path parallel to the eighth electrical path in a plane parallel to the x-y plane and parallel to the seventh electrical path in a plane parallel to the y-z plane, Wherein the sixth and seventh electrical paths transmit respective currents in the same direction and the eighth and ninth electrical paths transmit respective currents in the same direction opposite to the directions of the sixth and seventh electrical paths. A tenth electrical path connecting the sixth to ninth electrical paths in which the fifth and tenth electrical paths are not overlapped with each other in the z direction are implemented using an RF coil. Magnetic resonance imaging method. When three mutually orthogonal directions are displayed in the x, y and z directions in the space where the subject is located, Static field generating means for generating a static field in the z direction, Gradient magnetic field generating means for generating gradient magnetic fields in the space, High frequency magnetic field generating means for generating a high frequency magnetic field in the space; Measuring means for measuring a magnetic resonance signal from the space; Image generating means for generating an image based on the magnetic resonance signal measured by the measuring means A magnetic resonance imaging device comprising: The high frequency magnetic field generating means The first electrical path extending in the x direction, a second electrical path parallel to the first electrical path in an x-y plane, a third electrical path parallel to the first electrical path in an x-z plane, A fourth electrical path parallel to the third electrical path in a plane parallel to the x-y plane and parallel to the second electrical path in a plane parallel to the x-z plane, Wherein the first and second electrical paths transmit respective currents in the same direction and the third and fourth electrical paths transmit respective currents in the same direction opposite to the directions of the first and second electrical paths. A fifth electrical path connecting the first to fourth electrical paths in series, A sixth electrical path extending in the y direction in the x-y plane, A seventh electrical path parallel to the sixth electrical path in the x-y plane, an eighth electrical path parallel to the sixth electrical path in a y-z plane, A ninth electrical path parallel to the eighth electrical path in a plane parallel to the x-y plane and parallel to the seventh electrical path in a plane parallel to the y-z plane, Wherein the sixth and seventh electrical paths transmit respective currents in the same direction and the eighth and ninth electrical paths transmit respective currents in the same direction opposite to the directions of the sixth and seventh electrical paths. A tenth electrical path connecting the sixth to ninth electrical paths, wherein the fifth and tenth electrical paths do not overlap each other in the z direction. Magnetic resonance imaging device.

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