WO2010021222A1 - 高周波コイル及び磁気共鳴撮像装置 - Google Patents
高周波コイル及び磁気共鳴撮像装置 Download PDFInfo
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- WO2010021222A1 WO2010021222A1 PCT/JP2009/063107 JP2009063107W WO2010021222A1 WO 2010021222 A1 WO2010021222 A1 WO 2010021222A1 JP 2009063107 W JP2009063107 W JP 2009063107W WO 2010021222 A1 WO2010021222 A1 WO 2010021222A1
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- coil
- magnetic field
- electromagnetic coupling
- high frequency
- capacitor
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
- G01R33/00—Arrangements or instruments for measuring magnetic variables
- G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
- G01R33/28—Details of apparatus provided for in groups G01R33/44 - G01R33/64
- G01R33/32—Excitation or detection systems, e.g. using radio frequency signals
- G01R33/36—Electrical details, e.g. matching or coupling of the coil to the receiver
- G01R33/3642—Mutual coupling or decoupling of multiple coils, e.g. decoupling of a receive coil from a transmission coil, or intentional coupling of RF coils, e.g. for RF magnetic field amplification
- G01R33/365—Decoupling of multiple RF coils wherein the multiple RF coils have the same function in MR, e.g. decoupling of a receive coil from another receive coil in a receive coil array, decoupling of a transmission coil from another transmission coil in a transmission coil array
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
- G01R33/00—Arrangements or instruments for measuring magnetic variables
- G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
- G01R33/28—Details of apparatus provided for in groups G01R33/44 - G01R33/64
- G01R33/32—Excitation or detection systems, e.g. using radio frequency signals
- G01R33/34—Constructional details, e.g. resonators, specially adapted to MR
- G01R33/341—Constructional details, e.g. resonators, specially adapted to MR comprising surface coils
- G01R33/3415—Constructional details, e.g. resonators, specially adapted to MR comprising surface coils comprising arrays of sub-coils, i.e. phased-array coils with flexible receiver channels
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
- G01R33/00—Arrangements or instruments for measuring magnetic variables
- G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
- G01R33/28—Details of apparatus provided for in groups G01R33/44 - G01R33/64
- G01R33/32—Excitation or detection systems, e.g. using radio frequency signals
- G01R33/36—Electrical details, e.g. matching or coupling of the coil to the receiver
- G01R33/3642—Mutual coupling or decoupling of multiple coils, e.g. decoupling of a receive coil from a transmission coil, or intentional coupling of RF coils, e.g. for RF magnetic field amplification
- G01R33/3657—Decoupling of multiple RF coils wherein the multiple RF coils do not have the same function in MR, e.g. decoupling of a transmission coil from a receive coil
Definitions
- the present invention relates to a magnetic resonance imaging (MRI) apparatus, and more particularly, to a high-frequency coil that detects a magnetic resonance signal.
- MRI magnetic resonance imaging
- the MRI apparatus is a medical image diagnostic apparatus that causes magnetic resonance to occur in nuclei in an arbitrary cross section that crosses the examination target, and obtains a tomographic image in the cross section from the generated magnetic resonance signal.
- a gradient magnetic field to a living body placed in a static magnetic field and irradiating a high-frequency magnetic field with a high-frequency coil (RF coil)
- nuclei in the living body for example, hydrogen nuclei
- RF coil high-frequency coil
- a circularly polarized magnetic field is generated as a magnetic resonance signal.
- This signal is detected by an RF coil, and signal processing is performed to image the hydrogen nucleus distribution in the living body.
- an improvement in reception sensitivity, SN ratio, etc. is required for an RF coil that detects a magnetic resonance signal.
- an image pick-up performed using a plurality of RF coils for the purpose of expanding the detection range.
- a technique for detecting a magnetic resonance signal from a subject using a plurality of surface coils, synthesizing output signals of the surface coils, and obtaining an image having a high SN ratio over a wide range see, for example, Patent Document 1).
- a plurality of surface coils are arranged near the imaging target region of the subject, and a magnetic resonance signal from the subject is detected using the plurality of surface coils.
- Signal processing is performed on each magnetic resonance signal detected by each surface coil, and image data is generated for each surface coil. Then, the pixel data corresponding to the same position in the generated image are multiplied by the weighting coefficient obtained from the sensitivity distribution of each surface coil and added.
- Non-Patent Document 2 As a technique for preventing electromagnetic coupling between coils, a part of adjacent coils are overlapped with each other and the area of the overlapping loop is adjusted (for example, see Non-Patent Document 2). A method of canceling electromagnetic coupling by bringing inductors inserted in series close to each other (see, for example, Patent Document 2), a part of capacitors inserted in the loop conductors of adjacent coils is shared between the coils, and the value of the capacitor is adjusted Thus, a method for preventing electromagnetic coupling (for example, see Non-Patent Document 3), and a method for connecting a part of adjacent coils with a neutralization circuit composed of a capacitor (for example, see Patent Document 3).
- Patent Document 4 A method in which an eight-shaped or loop-shaped coil is placed on two adjacent coils so as to overlap each other (for example, see Patent Document 4).
- Non-Patent Document 2 In parallel imaging, it is necessary to prevent electromagnetic coupling between a plurality of RF coils arranged at intervals. Therefore, the methods disclosed in Non-Patent Document 2 and Non-Patent Document 3 described above cannot be used. Further, although the method disclosed in Patent Document 2 is applicable, it is necessary to finely adjust the position and shape of the inductor manually, which requires time and effort and is difficult to reproduce. Further, the method disclosed in Patent Document 3 requires adjustment while changing a plurality of capacitor values, and the adjustment is difficult. Similarly, in the method disclosed in Patent Document 4, since the degree of electromagnetic coupling greatly changes depending on the shape and arrangement of the RF coils to be overlapped, the reproducibility is low and the adjustment difficulty is high.
- Non-Patent Document 2 needs to reduce the input impedance value to a small value of 1 ⁇ or less in order to exert a sufficient effect to prevent electromagnetic coupling. Lowering causes a decrease in the amplification factor of the preamplifier, resulting in a decrease in the SN ratio of the acquired image.
- the impedance adjustment circuit is configured by a plurality of inductors and capacitors, it is necessary to adjust while changing the values of the plurality of inductors and capacitors. high. Further, as the number of RF coils increases, the number of adjustment points for preventing electromagnetic coupling increases, so that adjustment takes time and effort, resulting in an increase in the manufacturing cost of the RF coils.
- the present invention has been made in view of the above circumstances, and is a technique for preventing electromagnetic coupling between adjacent RF coils in an MRI apparatus including a plurality of RF coils arranged at intervals. It is an object of the present invention to provide a technique that is high and easy to adjust.
- a means capable of generating a magnetic flux that cancels a magnetic flux generated from one RF coil and interlinked with the other RF coil is disposed between adjacent RF coils.
- the magnetic resonance imaging apparatus includes a plurality of surface coils, and the resonance frequency is a frequency of a magnetic resonance signal of a predetermined nucleus, between adjacent surface coils in the plurality of surface coils.
- a plurality of surface coils arranged at intervals in a first direction, and the electromagnetic coupling preventing means includes a loop conductor including a capacitor; The loop conductor generates a magnetic coupling with the two adjacent surface coils, and generates a magnetic flux generated from one surface coil of the two adjacent surface coils and interlinked with the other surface coil.
- the resonance frequency of the electromagnetic decoupling means to provide a high frequency coil, characterized in that it is adjusted to be smaller than the resonance frequency of the high-frequency coil.
- an MRI apparatus including a plurality of RF coils
- electromagnetic coupling between adjacent RF coils arranged at intervals is prevented with a method having high reproducibility and easy adjustment. Can do.
- BRIEF DESCRIPTION OF THE DRAWINGS It is an external view of the MRI apparatus of 1st embodiment, (a) is an MRI apparatus of a horizontal magnetic field system, (b) is an MRI apparatus of a vertical magnetic field system. It is a block diagram which shows schematic structure of the MRI apparatus of 1st embodiment. BRIEF DESCRIPTION OF THE DRAWINGS It is a block diagram of RF coil unit of 1st embodiment, (a) is a bird's-eye view, (b) is the figure seen from the direction facing az axis, (c) is the direction facing ay axis It is the figure seen from.
- (A), (b), and (c) are the figures for demonstrating the state in which the high frequency magnetic field in the RF coil unit of 1st embodiment is linked to a coil.
- (A) And (b) is a figure which shows the equivalent circuit of the coil for electromagnetic coupling prevention. It is a figure which shows the frequency characteristic of the impedance of an electromagnetic coupling prevention coil. It is a figure which shows the equivalent circuit of RF coil unit of 1st embodiment.
- FIG. 1 A), (b), and (c) are the figures for demonstrating the state in which the high frequency magnetic field in the RF coil unit of the modification of 1st embodiment is linked to a coil.
- It is a block diagram of RF coil unit of 2nd embodiment.
- (A), (b), and (c) are figures which show an example of the decoupling circuit of 2nd embodiment.
- (A), (b), and (c) are figures which show the other example of the decoupling circuit of 2nd embodiment.
- It is a block diagram of RF coil unit of 3rd embodiment (a) is a bird's-eye view, (b) is the figure seen from the direction which opposes az axis, (c) is from the direction which opposes a y axis.
- (A), (b), and (c) are the figures for demonstrating the state in which the high frequency magnetic field in the RF coil unit of 3rd embodiment is linked to a coil.
- It is a block diagram of RF coil unit of 4th embodiment (a) is an overhead view, (b) is the figure seen from the direction which opposes az axis.
- (A), (b), and (c) are the figures for demonstrating the state in which the high frequency magnetic field in the RF coil unit of 4th embodiment is linked to a coil.
- It is a block diagram of the modification of the RF coil unit of 4th embodiment (a) is a bird's-eye view, (b) is the figure seen from the direction facing az axis.
- FIG. 1 It is another block diagram of the modification of the RF coil unit of 4th embodiment, (a) is an overhead view, (b) is the figure seen from the direction facing az axis. It is a block diagram of RF coil unit of 5th embodiment, (a) is a bird's-eye view, (b) is the figure seen from the direction which opposes az axis, (c) is this RF coil unit. It is the figure which looked at the example in the case of using two from the direction facing az axis. (A), (b), and (c) are the figures for demonstrating the state in which the high frequency magnetic field in the RF coil unit of 5th Embodiment is linked to a coil.
- FIG. 5th embodiment It is a block diagram of the modification of the RF coil unit of 5th embodiment, (a) is an overhead view, (b) is the figure seen from the direction facing az axis. It is another block diagram of the RF coil unit of 1st embodiment, (a) is a bird's-eye view, (b) is the figure seen from the direction facing az axis, (c) is facing ay axis It is the figure seen from the direction to do. It is a block diagram which shows schematic structure of the MRI apparatus in the case of using the RF coil unit of 1st embodiment as a coil for transmission / reception.
- FIG. 1 is an external view of the MRI apparatus of the present embodiment.
- the z-axis direction of the coordinate system 12 is the static magnetic field direction.
- FIG. 1A shows an MRI apparatus 100 including a horizontal magnetic field type magnet 101.
- a subject 10 is inserted into an imaging space in a bore of the magnet 101 while being laid on a table 301, and is imaged.
- FIG. 1B shows an MRI apparatus 200 provided with a vertical magnetic field type magnet 201, and the subject 10 is inserted into an imaging space between a pair of upper and lower magnets 201 while being laid down on a table 301.
- the in the present embodiment either a horizontal magnetic field method or a vertical magnetic field method may be used.
- the case of the horizontal magnetic field method will be described as an example.
- FIG. 2 is a block diagram showing a schematic configuration of the MRI apparatus 100 of the present embodiment.
- the same elements as those in FIG. 1 are denoted by the same reference numerals.
- the MRI apparatus 100 of the present embodiment includes a horizontal magnetic field type magnet 101, a gradient magnetic field coil 102, a shim coil 112 for adjusting the static magnetic field uniformity, a sequencer 104, a transmission RF coil 107 that generates a high-frequency magnetic field, and a subject 10.
- Receiving RF coil 114 for receiving the magnetic resonance signal generated from the.
- the gradient coil 102 and shim coil 112 are connected to a gradient magnetic field power source 105 and a shim power source 113, respectively.
- the transmission RF coil 107 is connected to the high-frequency magnetic field generator 106, and the reception RF coil 114 is connected to the receiver 108 including a detection circuit and an A / D converter.
- the receiver 108 is connected to each receiving RF coil 114.
- the sequencer 104 sends commands to the gradient magnetic field power source 105, the shim power source 113, and the high frequency magnetic field generator 106 to generate a gradient magnetic field and a high frequency magnetic field, respectively.
- the high frequency magnetic field is applied to the subject 10 through the transmission RF coil 107.
- a magnetic resonance signal generated from the subject 10 by applying a high-frequency magnetic field is detected by the receiving RF coil 114.
- the transmission RF coil 107 and the reception RF coil 114 each have a decoupling circuit and are connected to the decoupling circuit driving device 115.
- the sequencer 104 sends a command to the decoupling circuit driving device 115 to transmit a decoupling signal for controlling the operation and non-operation of the transmission RF coil 107 and the reception RF coil 114. That is, when a high-frequency magnetic field is applied to the subject 10 via the transmission RF coil 107, the decoupling circuit driving device 115 transmits a decoupling signal to the reception RF coil 114 according to a command sent from the sequencer 104. To do.
- the reception RF coil 114 is deactivated by the decoupling circuit, and electromagnetic coupling with the transmission RF coil 107 is prevented.
- the decoupling circuit driving device 115 sends a decoupling signal to the transmission RF coil 107 according to a command transmitted from the sequencer 104. Send.
- the transmitting RF coil 107 is deactivated by the decoupling circuit, and electromagnetic coupling with the receiving RF coil 114 is prevented.
- the magnetic resonance signal detected by the receiving RF coil 114 is amplified by the preamplifier and detected by the receiver 108.
- the sequencer 104 sets a frequency of a magnetic resonance signal (hereinafter referred to as a magnetic resonance frequency) as a reference for detection by the receiver 108.
- the detected signal is sent to the computer 109 through an A / D converter, where signal processing such as image reconstruction is performed.
- the result is displayed on the display 110.
- the detected signals and measurement conditions are stored in the storage medium 111 as necessary.
- the sequencer 104 performs control so that each device operates at a timing and intensity programmed in advance.
- the MRI apparatus 100 includes an RF coil unit that includes two surface coils that are spaced apart from each other and a unit that prevents electromagnetic coupling between the two surface coils as the reception RF coil 114. . Details of the RF coil unit will be described below.
- FIG. 3 is a diagram for explaining the configuration of the RF coil unit 25 of the present embodiment.
- the direction of the static magnetic field 900 generated by the horizontal magnetic field type magnet 101 is the z-axis direction of the coordinate system 12.
- FIG. 3A is an overhead view of the RF coil unit 25, and
- FIG. 3B is a view of the RF coil unit 25 as viewed from the direction facing the z axis.
- FIG. 3C is a view of the RF coil unit 25 as seen from the direction facing the y-axis.
- the RF coil unit 25 of this embodiment includes a first surface coil 5 in which a first capacitor 1 and a second capacitor 2 are inserted in a square loop conductor, and a square loop conductor.
- a second surface coil 6 having a third capacitor 3 and a fourth capacitor 4 inserted therein, an electromagnetic coupling preventing coil 13 having a capacitor 11 inserted into a square loop conductor 9, and a first signal line 7.
- a second signal line 8 Each of the first surface coil 5 and the second surface coil 6 includes a decoupling circuit that prevents electromagnetic coupling with the transmission RF coil 107.
- the description of the decoupling circuit is omitted for easy understanding of the drawing.
- the description of the inductance and resistance of the electromagnetic coupling preventing coil 13 itself of the first surface coil 5 and the second surface coil 6 is omitted.
- the first signal line 7 and the second signal line 8 are connected to both ends of the second capacitor 2 and the fourth capacitor 4, respectively.
- the first signal line 7 and the second signal line 8 are each connected to a balun (balanced-unbalanced converter: not shown) that removes common node noise, and the balun is a preamplifier (preamplifier: not shown). ). Further, the output of the preamplifier is connected to the receiver 108 via a coaxial cable.
- the first surface coil 5 and the second surface coil 6 are perpendicular to the direction of the static magnetic field 900 (here, the x-axis direction of the coordinate system 12). Further, they are arranged in the vicinity of the subject 10 with an interval.
- the electromagnetic coupling preventing coil 13 is disposed between the first surface coil 5 and the second surface coil 6.
- the first surface 22 where the electromagnetic coupling preventing coil 13 is substantially located, and the first surface coil 5 and the second surface coil 6 are substantially formed. It arrange
- the degree refers to an error range of angles caused by a manufacturing error of the coil.
- a part of the loop conductor 9 of the electromagnetic coupling preventing coil 13 is disposed on the second surface 23.
- the value C d is that electromagnetic coupling between the first surface coil 5 and the second surface coil 6 is prevented, and the first surface coil 5 and the second surface coil 6 are made of a predetermined element. Resonance is performed at the magnetic resonance frequency, and the impedance values of both surface coils are adjusted to be the same predetermined value at the magnetic resonance frequency of the predetermined element.
- each of the first surface coil 5 and the second surface coil 6 is a single body, resonates at a magnetic resonance frequency (f H (MHz)) of an element to be detected (for example, proton), and has a predetermined impedance.
- the values C 1 , C 2 , C 3 , and C 4 of the first capacitor 1, the second capacitor 2, the third capacitor 3, and the fourth capacitor 4 are adjusted so that the value (K ( ⁇ )) is obtained.
- the resonance frequency (f d ) of the electromagnetic coupling preventing coil 13 is smaller than f H and satisfies the following formula (1).
- the inductance L d of the loop conductor 9 and the value C d of the capacitor 11 of the electromagnetic coupling preventing coil 13 are determined so that the electromagnetic coupling with the coil 6 is minimized.
- Q H is a Q value when the loop conductor 9 of the electromagnetic coupling preventing coil 13 is resonated at a frequency f H
- the adjustment is performed by arranging the first surface coil 5, the second surface coil 6, and the electromagnetic coupling preventing coil 13 in a state close to the actual arrangement.
- the coil dimensions and arrangement may be modeled, and the respective values may be obtained by numerical calculation using an electromagnetic field simulator. Details of the adjustment will be described later.
- the RF coil unit 25 adjusted as described above prevents the electromagnetic coupling between the first surface coil 5 and the second surface coil 6 and operates as the reception RF coil 114. .
- the manner in which the magnetic flux generated from the first surface coil 5 is linked to the second surface coil 6 in the RF coil unit 25 shown in FIG. 3 will be described with reference to FIG.
- FIG. 4A when the first high-frequency magnetic field 17 is generated in the first surface coil 5, the first high-frequency magnetic field 17 is linked to the second surface coil 6 and electromagnetically coupled. It also links to the loop conductor 9 of the prevention coil 13. As a result, an induced electromotive force that cancels the time change of the magnetic flux linked to the loop conductor 9 of the electromagnetic coupling preventing coil 13 is generated, and the induced current 16 is induced.
- the electromagnetic coupling preventing coil 13 is equivalent to the inductance 19 (L d ) of the loop conductor 9, the capacitor 11 (C d ), the resistance of the loop conductor 9, and the high-frequency loss.
- the resistor 99 (R d ) is represented by an equivalent circuit 14 connected to each other. Note that L d , C d , and R d in parentheses are the inductance, the value of the capacitor, and the resistance value, respectively. The same applies hereinafter.
- the equivalent circuit 14 is represented by a circuit in which the induced electromotive force generated in the loop conductor 9 is inserted as the AC power supply 15 as shown in FIG.
- the equivalent circuit 14 viewed from the AC power supply 15 is a series resonant circuit having a resistance, and the impedance Zd is expressed by the following equation (2).
- the impedance Z d tends to decrease in inverse proportion to the frequency, and operates as a capacitive reactance C ′.
- the value C d of the capacitor 11 is adjusted so that the resonance frequency f d of the electromagnetic coupling preventing coil 13 is lower than the resonance frequency f H of the first surface coil 5.
- the equivalent circuit 14 of the electromagnetic coupling preventing coil 13 at the frequency f H operates as an inductive reactance. Therefore, as shown in FIG. 4B, the second high frequency magnetic field 18 is generated in the electromagnetic coupling preventing coil 13 so as to cancel the first high frequency magnetic field 17.
- the first high-frequency magnetic field 17 and the second high-frequency magnetic field 18 are linked to the second surface coil 6.
- the direction 20 of the first high-frequency magnetic field 17 is opposite to the direction 21 of the second high-frequency magnetic field 18. Therefore, if the amount of magnetic flux between the first high-frequency magnetic field 17 and the second high-frequency magnetic field 18 becomes equal, the two magnetic fluxes linked to the second surface coil 6 are canceled each other, and the first surface coil 5 Electromagnetic coupling with the second surface coil 6 is prevented.
- the electromagnetic coupling between the first surface coil 5 and the second surface coil 6 is adjusted by adjusting the inductance L d of the loop conductor 9 of the coil 13 for preventing electromagnetic coupling and the value C d of the capacitor 11. The prevention of this will be described below.
- the first surface coil 5 includes an equivalent inductance 85 (L 1 ) of the first surface coil 5, a first capacitor 1 (C 1 ), an equivalent resistance composed of a resistance component of the coil conductor and a loss of the subject 10.
- 95 (R 1 ) is connected in series to the second capacitor 2 (C 2 ), and the first signal line 7 is expressed as a circuit connected to both ends of the second capacitor 2.
- the second surface coil 6 is equivalent to the equivalent inductance 86 (L 2 ) of the second surface coil 6, the third capacitor 3 (C 3 ), the resistance component of the coil conductor, and the loss of the subject 10.
- 96 (R 2 ) is connected in series to the fourth capacitor 4 (C 4 ), and the second signal line 8 is expressed as a circuit connected to both ends of the fourth capacitor 4.
- the electromagnetic coupling preventing coil 13 has an equivalent resistance 99 consisting of the inductance 19 (L d ) of the loop conductor 9, the capacitor 11 (C d ), the resistance of the loop conductor 9, and the high-frequency loss. (R d ) and are represented as circuits connected to each other.
- the mutual inductance (M 12 ) is between the first surface coil 5 and the electromagnetic coupling preventing coil 13 and the mutual inductance (M 1d ) is between the second surface coil 6 and the electromagnetic coupling preventing coil 13.
- a mutual inductance (M 2d ) is generated between them.
- Each mutual inductance value (M 12 , M 1d , M 2d ) is determined by taking the direction of the current (I 1 , I 2 , I d ) flowing through each coil as shown in FIG. From the positional relationship, M 2d is a positive value, and M 12 and M 1d are negative values.
- the high-frequency voltage V 1 generated in the first signal line 7 of the first surface coil 5 is expressed by the following equation (3) and generated in the second signal line 8 of the second surface coil 6.
- frequency voltage V 2 which is represented by the following formula (4).
- Equation (6) represents the high-frequency voltage generated in the first surface coil 5 due to electromagnetic coupling with the second surface coil 6, and the second term on the right side of Equation (7) is the first surface coil.
- 5 represents a high-frequency voltage generated in the second surface coil 6 due to electromagnetic coupling with 5.
- Xd is expressed by the following formula (8).
- the ratio (R d / X d ) between the equivalent resistances R d and X d is expressed by the following equation (9).
- Equation (9) at frequency f H matches the left side of equation (1). Therefore, from the formula (1), R d / X d ⁇ 1/20. At this time, since R d + jX d ⁇ jX d can be considered, Equation (6) can be transformed into Equation (1), and Equation (7) can be transformed into Equation (11). As described above, M 2d is a positive value, and M 12 and M 1d are negative values. X d takes a positive value in a range where the resonance frequency (f d ) of the electromagnetic coupling preventing coil 13 is smaller than f H.
- first surface coil 5 and the second surface coil 6 are respectively set to the values of the first capacitor 1 and the second capacitor 2 (C 1 , C 2 ) and the third capacitor so as to resonate at the frequency f H. 3 and the value (C 3 , C 4 ) of the fourth capacitor 4 are adjusted. Therefore, the first surface coil 5 and the second surface coil 6 can simultaneously detect a magnetic resonance signal having a magnetic resonance frequency f H generated from the subject 10 without being electromagnetically coupled.
- the electromagnetic coupling between the first surface coil 5 and the second surface coil 6 of the RF coil unit 25 operating as the reception RF coil 114 is prevented by electromagnetic coupling.
- This can be prevented by adjusting the inductance L d of the loop conductor 9 of the coil 13 and the value C d of the capacitor 11.
- the inductance value L d of the loop conductor 9 is fixed in advance within a range that satisfies the equation (1), only the value C d of the capacitor 11 may be adjusted to satisfy the equation (12). For this reason, adjustment only needs to change the value of one capacitor, and it is easy and reproducibility is high. Therefore, the labor and time required for adjustment can be reduced, and the manufacturing cost of the RF coil can be suppressed.
- the electromagnetic coupling preventing coil 13 is arranged so that a part of the loop conductor 9 is located on the second surface 23.
- the electromagnetic coupling preventing coil 13 includes the mutual inductance (M 12 ) between the first surface coil 5 and the second surface coil 6, and the first surface coil 5 and the electromagnetic coupling preventing coil 13.
- the mutual inductance (M 1d ) and the mutual inductance (M 2d ) between the second surface coil 6 and the electromagnetic coupling preventing coil 13 may be arranged so as to satisfy the following expression (13).
- the case where loop coils are used for the first surface coil 5 and the second surface coil 6 is described as an example, but the shape of the surface coil is not limited to this. It may be a planar coil that can be arranged with a gap in a certain direction. Hereinafter, a modification is shown.
- FIG. 8 is a diagram showing an RF coil unit 25A which is a modification of the RF coil unit 25 of the present embodiment.
- FIG. 8A is an overhead view of the RF coil unit 25A
- FIG. 8B is a view of the RF coil unit 25A as viewed from the direction facing the z axis. These are the figures which looked at RF coil unit 25A from the direction which opposes a y-axis.
- an 8-shaped coil is used for the first surface coil 5A and the second surface coil 6A.
- the first high-frequency magnetic field 17 generated in the first surface coil 5A is closer to the loop nearer to the electromagnetic coupling preventing coil 13 and farther from the intersection 24 of the 8-shaped coil. It is distributed so that the direction of the magnetic field is reversed in the loop. This is due to the shape of the figure 8 coil.
- the electromagnetic coupling preventing coil 13 and the second surface coil 6A are connected to a loop closer to the electromagnetic coupling preventing coil 13 than the intersection 24 of the 8-shaped coil of the first surface coil 5A.
- the resulting first high frequency magnetic field 17 is mainly interlinked.
- the electromagnetic coupling preventing coil 13 has a second high frequency magnetic field 18 so as to cancel the first high frequency magnetic field 17 linked to the electromagnetic coupling preventing coil 13. appear.
- the second surface coil 6A is provided with the first high-frequency magnetic field 17 and the first electromagnetic coupling preventing coil 13 induced by the first high-frequency magnetic field 17.
- the second high-frequency magnetic field 18 is linked.
- the direction 20 of the first high-frequency magnetic field is opposite to the direction 21 of the second high-frequency magnetic field. Accordingly, even in the case of an 8-shaped coil, as in the case of the RF coil unit 25 shown in FIG. 3, the inductance L d of the loop conductor 9 and the value C d of the capacitor 11 are adjusted, so Can be prevented from electromagnetic coupling.
- one of the first surface coil 5 and the second surface coil 6 may be a loop-type coil and the other may be an 8-shaped coil.
- a one-turn loop coil is used as the loop conductor 9 of the electromagnetic coupling preventing coil 13, but a loop coil having a plurality of turns may be used as the loop conductor 9.
- the inductance (L 1 ) of the loop conductor of the first surface coil 5 the values (C 1 , C 2 ) of the first capacitor 1 and the second capacitor 2.
- the inductance (L 2 ) of the loop conductor of the second surface coil 6 the values (C 3 , C 4 ) of the third capacitor 3 and the fourth capacitor 4, and the loop conductor 9 of the electromagnetic coupling preventing coil 13
- a specific adjustment method between the inductance (L d ) and the value (C d ) of the capacitor 11 and an example of the value will be described.
- f H 128 MHz
- the dimensions of the first surface coil 5 and the second surface coil 6 are determined, and the first surface coil 5 and the second surface coil 6 each resonate independently at 128 MHz, and The values of the first capacitor 1 and the second capacitor 2 (C 1 , C 2 ) and the values of the third capacitor 3 and the fourth capacitor 4 (C 3 , C 4 ) so that the impedances of both coils are 50 ⁇ respectively. And adjust.
- the first surface coil 5 and the second surface coil 6 after adjusting the capacitor value are arranged at a predetermined interval, and the first signal line 7 and the second signal line 8 are respectively connected to the first surface coil 5 and the second signal line 8. Connect to one surface coil 5 and second surface coil 6.
- the Q value (Q H ) of the electromagnetic coupling preventing coil 13 is measured.
- an electromagnetic coupling preventing coil 13 is disposed between the first surface coil 5 and the second surface coil 6.
- the value (C d ) of the capacitor 11 of the electromagnetic coupling preventing coil 13 is selected so that the resonance frequency of the electromagnetic coupling preventing coil 13 is lower than 128 MHz.
- the first signal line 7 and the second signal line 8 are connected to two ports of the network analyzer, respectively, and the signal transmission characteristics from the first surface coil 5 to the second surface coil 6 at a frequency of 128 MHz.
- S 12 is the ratio of signal incident from one port is output from the other port, electromagnetic the first surface coil 5 as the value of S 12 is small and the second surface coil 6 The weak bond is weak. Therefore, as the value of S 12 becomes smaller, changing the value of capacitor 11 (C d). Then, a value that makes the value of S 12 equal to or less than a predetermined value or a value that minimizes the electromagnetic coupling between the first surface coil 5 and the second surface coil 6 is the value C d of the capacitor 11. Decide.
- the impedances of the first surface coil 5 and the second surface coil 6 at a frequency of 128 MHz are measured, and the values of the first capacitor 1 and the second capacitor 2 (C 1 , C 2 ) and the values (C 3 , C 4 ) of the third capacitor 3 and the fourth capacitor 4 are adjusted again.
- these values are adjusted so that both coils resonate at 128 MHz and the impedances of both coils become 50 ⁇ respectively.
- the resonance frequency (f d ) of the electromagnetic coupling preventing coil 13 is measured, and the condition of equation (1) is satisfied by the values of f d and Q H Confirm.
- the condition of Expression (1) is not satisfied, the above adjustment is repeated so as to satisfy the condition of Expression (1) by changing the size and arrangement of the electromagnetic coupling preventing coil 13.
- each of the first surface coil 5 and the second surface coil 6 is a square coil with a side of 100 mm, and the electromagnetic coupling preventing coil 13 has a width.
- a rectangular coil having a length of 100 mm (length in the z-axis direction shown in FIG. 3A) and a height of 25 mm (length in the y-axis direction shown in FIG. 3A) is assumed.
- the conductor used for each coil is a copper wire having a diameter of 4 mm, and the distance between the first surface coil 5 and the second surface coil 6 is 10 mm.
- the interval is the distance from the center of the copper wire of both coils.
- a part of the loop conductor 9 of the electromagnetic coupling preventing coil 13 located on the second surface 23 is at a position 5 mm from the side of the first surface coil 5 adjacent to the second surface coil 6.
- the values of the first capacitor 1 and the second capacitor 2 (C 1 , C 2 ) obtained by the simulation by the electromagnetic field simulator, and the values of the third capacitor 3 and the fourth capacitor 4 (C 3 , C 4).
- the value on the left side of Expression (1) is 0.0097, which satisfies the condition of Expression (1), which is less than 1/20.
- FIG. 10 is a diagram for explaining the configuration of the RF coil unit 26 of the present embodiment.
- the electromagnetic coupling preventing coil 13B of the RF coil unit 26 of this embodiment includes a decoupling circuit 48 in the conductor loop 9 for preventing magnetic coupling with the transmitting RF coil 107.
- Other configurations are basically the same as those of the RF coil unit 25 of the first embodiment.
- the z-axis direction of the coordinate system 12 is the direction of the static magnetic field 900 generated by the horizontal magnetic field type magnet 101.
- FIG. 10 shows a decoupling circuit 49 and a decoupling circuit 50 inserted into the first surface coil 5 and the second surface coil 6, which are not shown in FIG.
- RF coil unit 26 will be described as to detect the magnetic resonance signal of the frequency f H.
- the impedance values of the first surface coil 5 and the second surface coil 6 are adjusted to be the same predetermined value K.
- f H is the magnetic resonance frequency 128MHz of protons in the static magnetic field strength 3 Tesla
- the impedance value K may be 50 [Omega.
- the decoupling circuit 48 includes a circuit in which an inductor 51 and a PIN diode 61 are connected in series, and a capacitor 47 connected in parallel to the circuit.
- the PIN diode 61 has a characteristic in which the value of a direct current flowing in the forward direction of the diode becomes a conductive state when the value of the direct current is equal to or greater than a certain value, and ON / OFF is controlled by the direct current.
- the decoupling circuit 49 includes a first capacitor 1 and a circuit in which an inductor 52 and a PIN diode 61 connected in parallel to the first capacitor 1 are connected in series. The Further, as shown in FIG.
- the decoupling circuit 50 includes a third capacitor 3 and a circuit in which an inductor 53 and a PIN diode 61 connected in parallel to the third capacitor 3 are connected in series. Composed.
- the output terminals of the decoupling circuit driving device 115 are connected to both ends of the PIN diode 61.
- the values (C 3 , C 4 ) of the capacitor 3 and the fourth capacitor 4 mean that the first surface coil 5 and the second surface coil 6 resonate at f H , and the impedance values of both surface coils at that time are respectively It is adjusted to be K ⁇ .
- the adjustment method is the same as in the first embodiment.
- the value C 47 of the capacitor 47 and the value L 51 of the inductor 51 are adjusted so that the decoupling circuit 48 resonates at f H MHz when the PIN diode 61 is on, and the value C d of the capacitor 11 is the PIN diode.
- the electromagnetic coupling preventing coil 13 ⁇ / b> B is adjusted so as to prevent electromagnetic coupling between the first surface coil 5 and the second surface coil 6 when 61 is off.
- Method of adjusting the value C d of the capacitor 11 is also similar to the first embodiment.
- the values L 52 and L 53 of the inductors 52 and 53 are adjusted so that the decoupling circuit 49 and the decoupling circuit 50 resonate at f H MHz when the PIN diode 61 is on.
- a control current 66 for preventing magnetic coupling flows from the decoupling circuit driving device 115 to the RF coil unit 26.
- the control current 66 flows to the PIN diode 61 of each of the decoupling circuits 48, 49, 50, and the PIN diode 61 is turned on.
- the decoupling circuit 48, 49, and 50, to resonate at f H MHz becomes each parallel resonant circuit, the first surface coil 5, the conductor loop of the second surface coil 6 and electromagnetic decoupling coil 13B Is almost open.
- the transmission RF coil 107 has f H MHz as a main component without moving the resonance frequency due to the magnetic coupling or lowering the Q value of the coil.
- the subject 10 is irradiated with a high frequency magnetic field.
- the value of the control current 66 flowing from the decoupling circuit driving device 115 to the PIN diode 61 becomes zero.
- the PIN diode 61 in the RF coil unit 26 is turned off, and the decoupling circuits 48, 49, 50 operate as the capacitor 47, the first capacitor 1, and the third capacitor 3, respectively.
- the equivalent circuit of the RF coil unit 26 of this embodiment is the equivalent circuit of the RF coil unit 25 of the first embodiment. Will be the same. Therefore, similarly to the RF coil unit 25 of the first embodiment, the RF coil unit 26 of the present embodiment prevents electromagnetic coupling between the first surface coil 5 and the second surface coil 6 and is used for reception. It operates as the RF coil 114.
- a decoupling signal is sent from the decoupling circuit driving device 115 to the transmitting RF coil 107, and the decoupling circuit inserted in the transmitting RF coil 107 is opened and becomes non-operating. Therefore, when the magnetic resonance signal emitted from the subject 10 is received, the magnetic coupling between the RF coil unit 26 and the transmission RF coil 107 is lost, and the RF coil unit 26 moves the resonance frequency due to the magnetic coupling or the Q of the coil. without reduction of the value, to receive a magnetic resonance signal as a main component f H MHz.
- the electromagnetic coupling between the first surface coil 5 and the second surface coil 6 of the RF coil unit 26 that operates as the reception RF coil 114 is performed by the loop conductor 9.
- This can be prevented by adjusting the inductance L d and the value C d of the capacitor 11.
- the inductance value L d of the loop conductor 9 is fixed in advance within a range satisfying the expression (1), only the value C d of the capacitor 11 may be adjusted to satisfy the expression (12). All you need to do is adjust the value of. Therefore, according to the RF coil unit 26 of the present embodiment, adjustment work for preventing electromagnetic coupling is facilitated. Moreover, it is easy and has high reproducibility.
- the decoupling circuit 48 opens the electromagnetic coupling preventing coil 13B. Therefore, a change in characteristics of the transmission RF coil 107 due to magnetic coupling between the transmission RF coil 107 and the electromagnetic coupling prevention coil 13B is suppressed, and an unnecessary high frequency induced on the electromagnetic coupling prevention coil 13B by a high frequency magnetic field.
- the magnetic field can be made sufficiently small.
- the decoupling circuit is not limited to this.
- the decoupling circuits 48, 49, 50 shown in FIG. 11 instead of the decoupling circuits 48, 49, 50 shown in FIG. 11, the decoupling circuits 48 ', 49', 50 'shown in FIGS. 12 (a), (b), (c) may be used.
- This uses a cross diode 62 instead of the PIN diode 61 shown in FIG.
- the cross diode 62 is turned on by the applied high frequency magnetic field. Therefore, the control current 66 for preventing magnetic coupling with the transmission coil 107 is not required, and a decoupling circuit can be configured more easily.
- FIG. 13 is a diagram for explaining the configuration of the RF coil unit 27 of the present embodiment.
- a part of the loop conductor 9 is constituted by a plate-like conductor 91.
- One surface of the plate-shaped conductor 91 is arranged facing the center of the electromagnetic coupling preventing coil 13C.
- Other configurations are basically the same as those of the RF coil unit 25 of the first embodiment.
- FIG. 13A is an overhead view of the RF coil unit 27, and FIG. 13B is a view of the RF coil unit 27 as viewed from the direction facing the z axis.
- FIG. 13C is a view of the RF coil unit 27 as seen from the direction facing the y-axis.
- the z-axis direction of the coordinate system 12 is the direction of the static magnetic field 900 generated by the horizontal magnetic field type magnet 101.
- RF coil unit 27 will be described as to detect the magnetic resonance signal of the frequency f H.
- the impedance values of the first surface coil 5 and the second surface coil 6 are adjusted to be the same predetermined value K.
- f H is the magnetic resonance frequency 128MHz of protons in the static magnetic field strength 3 Tesla
- the impedance value K may be 50 [Omega.
- the value C d of the capacitor 11 of the electromagnetic decoupling coil 13C is adjusted so that the resonance frequency f d of the electromagnetic decoupling coil 13C is lower than the resonance frequency f H of the surface coil Shall be.
- the first high-frequency magnetic field 17 generated in the first surface coil 5 is linked to the second surface coil 6 and linked to the electromagnetic coupling preventing coil 13C.
- an induced electromotive force is generated on the plate-like conductor 91 of the electromagnetic coupling preventing coil 13C in accordance with the law of electromagnetic induction so as to cancel the time change of the interlinking magnetic flux, and on the surface of the plate-like conductor 91.
- An induced current 16 is induced.
- the value C d of the capacitor 11, the resonant frequency f d of the electromagnetic decoupling coil 13C is adjusted to be lower than the resonance frequency f H of the surface coil, the electromagnetic decoupling coil 13C at the frequency f H is It operates as an inductive reactance. Therefore, as shown in FIG. 14B, the second high-frequency magnetic field 18 is generated in the electromagnetic coupling preventing coil 13C so as to cancel the first high-frequency magnetic field 17.
- the second surface coil 6 has a first high frequency magnetic field 17 and a first electromagnetic coupling preventing coil 13 ⁇ / b> C induced by the first high frequency magnetic field 17.
- the second high-frequency magnetic field 18 is linked.
- the direction 20 of the first high-frequency magnetic field is opposite to the direction 21 of the second high-frequency magnetic field. Therefore, also in the present embodiment, as in the case of the RF coil unit 25 of the first embodiment, the inductance L d of the loop conductor 9 and the value C d of the capacitor 11 are adjusted, so that the electromagnetic wave between the coils is adjusted. Bonding is prevented. Therefore, in the RF coil unit 27 shown in FIG. 13, the electromagnetic coupling between the first surface coil 5 and the second surface coil 6 is prevented, and the first surface coil 5 and the second surface coil 6 are detected. Resonates at the magnetic resonance frequency f H of the target element, and operates as a receiving RF coil 114.
- the electromagnetic coupling between the first surface coil 5 and the second surface coil 6 of the RF coil unit 27 operating as the reception RF coil 114 is prevented from electromagnetic coupling. It is prevented by adjusting the value C d of the inductance L d and the capacitor 11 of the loop conductor 9 of use coil 13C.
- the inductance value L d of the loop conductor 9 is fixed in advance within a range that satisfies the equation (1), only the value C d of the capacitor 11 may be adjusted to satisfy the equation (12). For this reason, adjustment only needs to change the value of one capacitor, and it is easy and reproducibility is high.
- the labor and time required for adjustment can be reduced, and the manufacturing cost of the RF coil can be suppressed. Furthermore, according to the present embodiment, even if the interval between the first surface coil 5 and the second surface coil 6 is increased, the width of the plate conductor 91 is correspondingly increased so that one surface coil can The induced high frequency magnetic field can be efficiently transmitted to the other surface coil 6. Electromagnetic coupling can be effectively prevented even when the distance between the first surface coil 5 and the second surface coil 6 is wide.
- FIG. 15 is a diagram for explaining the RF coil unit 28 of the present embodiment.
- the RF coil unit 28 of the present embodiment is configured as an array coil. Hereinafter, it is referred to as an array coil 28.
- FIG. 15A is an overhead view of the array coil 28
- FIG. 15B is a view of the array coil 28 as viewed from the direction facing the z-axis.
- the array coil 28 includes four RF coil units 25 of the first embodiment, as shown in FIG. These RF coil units 25 are arranged at intervals in the circumferential direction 32 along the side surface of the cylindrical bobbin 31. In this embodiment, when it is not necessary to distinguish between the first surface coil 5 and the second surface coil 6 included in the RF coil unit 25, they are collectively referred to as a surface coil 33. In the array coil 28, the electromagnetic coupling preventing coil 13 provided in the RF coil unit 25 of the first embodiment is also disposed between the RF coil units 25.
- the electromagnetic coupling preventing coil 13 in the RF coil unit 25 and the electromagnetic coupling preventing coil 13 disposed between the RF coil units 25 have a first surface 22 on which they are substantially positioned, the central axis 30 of the bobbin 31. It is arranged on the side surface of the bobbin 31 so as to pass through.
- each surface coil 33 of the RF coil unit 25 is omitted for easy understanding of the drawing. Also, the notation of inductance and resistance of the surface coil 33 and the electromagnetic coupling preventing coil 13 itself is omitted. Note that.
- the output of each surface coil 33 constituting the array coil 28 is connected to a balun (balance-unbalance converter: not shown) that removes common mode noise, and the balun is connected to a preamplifier (preamplifier: not shown). Is done. Further, the output of the preamplifier is connected to a plurality of receivers 108 via coaxial cables. For example, in the present embodiment, since eight surface coils 33 are provided, the eight receivers 108 are connected.
- each surface coil 33 has a predetermined element. It resonates at the magnetic resonance frequency f H, and such that the impedance of each surface coil 33 in the magnetic resonance frequency f H of the predetermined element is a predetermined value (K.OMEGA.), are adjusted respectively.
- the inductance L d and the value C d of the capacitor 11 is the surface coil 33 of the electromagnetic decoupling coil 13 of the loop conductor 9 of the electromagnetic decoupling coil 13 shown in Figure 15 (a)
- the resonance frequency f H is adjusted to be lower than the resonance frequency f H , and the electromagnetic coupling between the two surface coils 33 adjacent to the electromagnetic coupling preventing coil 13 is adjusted.
- Method of adjusting the value C d of the capacitor 11 is similar to the first embodiment.
- f H can be a magnetic resonance frequency of 128 MHz of hydrogen nuclei at a static magnetic field strength of 3 Tesla, and an impedance value K of 50 ⁇ .
- FIG. 16 is a diagram for explaining a state in which the first high-frequency magnetic field generated from the first surface coil 33a is linked to the second surface coil 33b and the third surface coil 33c.
- the electromagnetic coupling preventing coil 13 disposed between the first surface coil 33a and the second surface coil 33b is 13a, and between the first surface coil 33a and the third surface coil 33c.
- the arranged electromagnetic coupling preventing coil 13 is denoted by 13b.
- the first high-frequency magnetic field 17 generated in the first surface coil 33a is interlinked with the second surface coil 33b and the third surface coil 33c, and the first It links to two electromagnetic coupling preventing coils 13a and 13b arranged on both sides of the surface coil 33a.
- an induced electromotive force is generated in the electromagnetic coupling preventing coils 13a and 13b in accordance with the electromagnetic induction law so as to cancel the time change of the interlinking magnetic flux, and the induced current 16 is induced.
- the resonant frequency f d of the electromagnetic decoupling coil 13 is adjusted to be lower than the resonance frequency f H of the respective surface coils 33, for electromagnetic decoupling at the frequency f H
- the coil 13 operates as an inductive reactance. Therefore, as shown in FIG. 16B, the second high frequency magnetic fields 18a and 18b are generated in the electromagnetic coupling preventing coils 13a and 13b so as to cancel the first high frequency magnetic field 17.
- the second surface coil 33b is provided with the first high-frequency magnetic field 17 and the first electromagnetic coupling preventing coil 13a induced by the first high-frequency magnetic field 17.
- the second high-frequency magnetic field 18a is linked.
- first high-frequency magnetic field 17 and the second high-frequency magnetic field 18 b generated by the electromagnetic coupling preventing coil 13 b induced by the first high-frequency magnetic field 17 are linked to the third surface coil 33 c.
- the direction 20 of the first high-frequency magnetic field 17 and the direction 21 of the second high-frequency magnetic fields 18a, 18b that are linked to the surface coils 33b, 33c are opposite to each other.
- the value C d of the inductance L d and the capacitor 11 of the loop conductor 9 of the electromagnetic decoupling coil 13a, and the value C d of the inductance L d and the capacitor 11 of the loop conductor 9 of the electromagnetic decoupling coil 13b By adjusting each, the electromagnetic coupling between the first surface coil 33a and the second surface coil 33b and between the first surface coil 33a and the third surface coil 33c can be prevented.
- the surface coil 33 and the electromagnetic coupling preventing coil 13 are alternately and repeatedly arranged in the circumferential direction 32. Electromagnetic coupling between the surface coils 33 adjacent in the circumferential direction 32, it is possible to prevent the value C d of the capacitor 11 of the electromagnetic decoupling coil 13 by adjusting respectively.
- Each surface coil 33 resonates at f H MHz and is adjusted so that the impedance is K ⁇ , so that a magnetic resonance signal having a frequency f H can be detected.
- the array coil 28 shown in FIG. 15 is prevented electromagnetic coupling between the adjacent surface coils 33, eight each surface coil 33, detectable receive RF magnetic resonance signal frequency is f H It operates as a coil 114.
- the electromagnetic coupling between the adjacent surface coils 33 of the array coil 28 is the same as the inductance L d of the loop conductor 9 of the electromagnetic coupling preventing coil 13 disposed therebetween. it can be prevented by adjusting the value C d of the capacitor 11.
- the inductance value L d of the loop conductor 9 is fixed in advance within a range that satisfies the equation (1), only the value C d of the capacitor 11 may be adjusted to satisfy the equation (12).
- the electromagnetic coupling can be prevented by adjusting only the value of one capacitor, the operation is easy and the reproducibility is high.
- the surface coils 33 are arranged in a circumferential shape, it is possible to perform imaging using the eight surface coils 33 simultaneously by placing the subject inside the bobbin 31. That is, it is possible to capture an image with a high S / N ratio over the entire subject, and is particularly effective for capturing the head and knees.
- phase encoding is performed in the x direction and the y direction of the coordinate system 12 shown in FIG. 15 using the method shown in Non-Patent Document 1.
- the S / N ratio of the acquired image is improved as compared with the case of using a coil in which a part of adjacent surface coils overlap.
- a loop coil is used as the surface coil 33, but the shape of the surface coil to be used is not limited to this. It may be a planar coil that can be arranged with a gap in a certain direction. For example, an 8-shaped coil shown in FIG. 8 may be used. In this embodiment, eight surface coils 33 are used, but the number of surface coils 33 is not limited to this. For example, 16, 24 or 32 may be used.
- the surface coil 33 is arranged in one direction of the circumferential direction 32 of the bobbin 31, but the arrangement of the surface coil 33 is not limited to one direction. It suffices if the surface coils 33 can be arranged at intervals.
- FIG. 17A is an overhead view of the array coil 28A
- FIG. 17B is a view of the array coil 28A viewed from the direction facing the z-axis.
- the array coil 28A is formed by arranging the array coils 28 in two rows at intervals in the z-axis direction.
- the number of surface coils 33 in each row is eight.
- the surface coils 33 in each row are arranged so that the positions of the intervals between adjacent surface coils are aligned in the z direction.
- An electromagnetic coupling preventing coil 13 ′ is also disposed between the surface coils 33 adjacent in the z direction.
- the number of electromagnetic coupling preventing coils 13 ' is also eight.
- the electromagnetic coupling between the adjacent surface coils 33 is prevented by the electromagnetic coupling preventing coil 13 arranged between the surface coils 33, as in the above embodiment.
- the electromagnetic coupling preventing coil 13 ′ is disposed between the surface coils 33 adjacent to each other in the z direction of each row.
- the array coil 28A shown in FIG. 17 prevents electromagnetic coupling between the adjacent surface coils 33. Further, since the entire surface coil 33 simultaneously detects a magnetic resonance signal of a desired nucleus adjusted in advance (for example, a magnetic resonance signal of a hydrogen nucleus at 3 Tesla), the array coil 28A operates as a receiving RF coil 114. To do. In the present modification, the surface coils 33 are arranged at intervals in the x, y, and z3 directions. For this reason, when performing parallel imaging by the method disclosed in Non-Patent Document 1, a part of adjacent surface coils overlap even if the direction of thinning out phase encoding is set to any of the x, y, and z directions. The SN ratio of the acquired image is improved as compared with the coil that is present.
- the surface coil 33 is arranged so that the position of the surface coil is aligned in the circumferential direction and the z direction of the bobbin 31, but the surface coil in the z direction as in the array coil 28B shown in FIG.
- the 33 positions need not be aligned.
- an electromagnetic coupling preventing coil 13 ′ is appropriately disposed in a portion adjacent to the surface coil 33 with a gap.
- the electromagnetic coupling between the adjacent surface coils 33 is prevented by the electromagnetic coupling preventing coil 13 disposed between the surface coils 33 as in the above embodiment.
- an electromagnetic coupling preventing coil 13 ′ is disposed between the surface coils 33 adjacent to each other in the z direction of each row.
- FIG. 19 is a diagram for explaining the array coil 29 used as the reception RF coil 114 of the present embodiment.
- FIG. 19A is a view of the array coil 29 viewed from an oblique direction
- FIG. 19B is a view of the array coil 29 viewed from the direction facing the z-axis
- FIG. It is the figure which looked at the example in the case of using two array coils 29 from the direction facing az axis.
- the array coil 29 includes a first surface coil 33a, a second surface coil 33b, a third surface coil 33c, and two electromagnetic coupling preventing coils 13a and 13b.
- the surface coil 33 when it is not necessary to distinguish between the surface coils, they are collectively referred to as the surface coil 33, and when it is not necessary to distinguish between the electromagnetic coupling preventing coils, they are collectively referred to as the electromagnetic coupling preventing coil 13.
- the first surface coil 33a, the second surface coil 33b, and the third surface coil 33c are connected to the first capacitor 1 and the second surface coil 5 in a rectangular conductor loop.
- the two capacitors 2 are inserted and provided with signal lines 7 connected to both ends of the second capacitor.
- the first surface coil 33a, the second surface coil 33b, and the third surface coil 33c are spaced from each other at intervals in the x direction of the coordinate system 12.
- the coil 33 is disposed so that the surface of the coil 33 faces the subject 10.
- the central coil is the first surface coil 33a
- the surface coils 33 on both sides of the first surface coil 33a are the second surface coils.
- 33b and the third surface coil 33c are respectively provided between the first surface coil 33a and the second surface coil 33b, and between the first surface coil 33a and the third surface coil 33c. It is arranged between.
- the loop conductor 9a constituting the electromagnetic coupling preventing coil 13a includes a first surface 41 on which the first surface coil 33a is substantially located and a second surface coil. 33b is disposed on a surface 44 that includes a line of intersection with the second surface 42 that is substantially located.
- a part of the loop conductor 9b constituting the electromagnetic coupling preventing coil 13b includes a first surface 41 where the first surface coil 33a is substantially positioned and a first surface 41 where the third surface coil 33b is substantially positioned. It is disposed on a surface 45 including a line of intersection with the three surfaces 43.
- the loop conductors 9b are arranged so that the areas of the loop conductors 9b are different on both sides of the intersection line.
- the electromagnetic coupling preventing coil 13a is arranged such that the angle formed by the surface 41 and the surface 44 and the angle formed by the surface 42 and the surface 44 are approximately equal to each other.
- the electromagnetic coupling preventing coil 13b is arranged such that the angle formed by the surface 41 and the surface 45 and the angle formed by the surface 43 and the surface 45 are approximately equal to each other.
- the degree is an error range of an angle caused by a manufacturing error of the coil.
- the inductance of the loop conductor and the value of the capacitor of each surface coil 33 constituting the coil array 29 are between the first surface coil 33a and the second surface coil 33b. And the electromagnetic coupling between the first surface coil 33a and the third surface coil 33c is prevented, and the first surface coil 33a, the second surface coil 33b and the third surface coil 33c are prevented.
- surface coils 33c resonates magnetic resonance frequency f H of the predetermined element, a magnetic resonance frequency f H of the predetermined element, the first surface coil 33a, the impedance of the second surface coil 33b and the third surface coil 33c Are adjusted to a predetermined value K.
- f H can be a magnetic resonance frequency of 128 MHz of hydrogen nuclei at a static magnetic field strength of 3 Tesla and an impedance of 50 ⁇ .
- the electromagnetic decoupling coil 13a, the capacitors 11a, 11b of the value of 13b is such that the electromagnetic decoupling coil 13a, the resonance frequency f d of 13b becomes lower than the resonance frequency f H of the respective surface coils 33 Adjusted to
- the state where the magnetic flux generated from the first surface coil 33a is linked to the second surface coil 33b and the third surface coil 33c will be described with reference to FIG.
- the first high-frequency magnetic field 17 generated in the first surface coil 33a is interlinked with the second surface coil 33b and the third surface coil 33c, and the first surface coil It links to two electromagnetic coupling preventing coils 13a and 13b arranged on both sides of 33a.
- an induced electromotive force is generated in the electromagnetic coupling preventing coils 13a and 13b so as to cancel the time change of the interlinking magnetic flux, and the induced current 16 is induced.
- the electromagnetic decoupling coil 13a, the value of capacitor 11 and 13b are electromagnetic decoupling coils 13a, adjusted so that the resonance frequency f d of 13b becomes lower than the resonance frequency f H of the surface coils 33 because it is, at the frequency f H, the electromagnetic decoupling coils 13a, 13b operates as an inductive reactance. Therefore, as shown in FIG. 20B, the second high frequency magnetic fields 18a and 18b are generated in the electromagnetic coupling preventing coils 13a and 13b so as to cancel the first high frequency magnetic field 17.
- the first high-frequency magnetic field 17 and the electromagnetic coupling preventing coil 13 a induced by the first high-frequency magnetic field 17 are emitted from the second surface coil 33 b.
- the second high-frequency magnetic field 18 a is interlinked, and the second high-frequency magnetic field 17 and the second electromagnetic coupling preventing coil 13 b induced by the first high-frequency magnetic field 17 are emitted from the third surface coil 33 c.
- the high frequency magnetic field 18b is linked.
- the direction 20 of the first high frequency magnetic field 17 and the direction 21 of the second high frequency magnetic fields 18a, 18b linked to the surface coils 33b, 33c are opposite to each other.
- the inductance L db of the loop conductor 9b and the value C db of the capacitor 11b of the electromagnetic coupling preventing coil 13b positioned between the first surface coil 33a and the third surface coil 33c the first surface coil The electromagnetic coupling between 33a and the second surface coil 33b and between the first surface coil 33a and the third surface coil 33c is prevented.
- each surface coil 33 is resonated at f H MHz and adjusted to have an impedance of K ⁇
- the array coil 29 of the present embodiment prevents electromagnetic coupling between adjacent surface coils, and a desired value. It operates as a receiving RF coil 114 that detects a magnetic resonance signal.
- the coupling preventing coil 13 has the same angle between the surface on which the electromagnetic coupling preventing coil 13 is substantially located and the surface on which the three surface coils 33 are substantially located. Although it arrange
- the first surface coil 33a, the second surface coil 33b, and the third surface coil 33c are spaced in the x direction of the coordinate system 12, as shown in FIG. It is arranged with a gap.
- the arrangement of the surface coil 33 is not limited to one direction, and may be any direction as long as the surface coil 33 can be arranged with an interval.
- FIG. 21A is a view of the array coil 29A viewed from an oblique direction
- FIG. 21B is a view of the array coil 29A viewed from the direction facing the z-axis.
- the array coils 29 shown in FIG. 19 are arranged in two rows at intervals in the z-axis direction.
- the surface coils 33 in each row are arranged so as to be aligned in the z direction, and the two surface coils 33 adjacent in the z direction are connected by an electromagnetic coupling preventing circuit 39.
- the electromagnetic coupling prevention circuit 39 is disclosed in, for example, Patent Document 2, and is a circuit arranged so that two inductors are brought close to each other to generate electromagnetic coupling.
- electromagnetic coupling between adjacent coils of the three surface coils 33 arranged at intervals in the x direction of the coordinate system 12 is prevented by the electromagnetic coupling preventing coil 13, and the z of the coordinate system 12 is prevented by an electromagnetic coupling prevention circuit 39.
- the array coil 29A shown in FIG. 21 prevents electromagnetic coupling between the adjacent surface coils 33, and simultaneously detects a desired magnetic resonance signal such as a magnetic resonance signal of a hydrogen nucleus at 3 Tesla for reception. It operates as the RF coil 114.
- the sensitivity region in the z direction can be expanded.
- the electromagnetic coupling preventing circuit 39 the electromagnetic coupling preventing coil 13 may be provided.
- trimmer capacitors may be used for these.
- an example using a trimmer capacitor will be described by taking the first embodiment as an example.
- FIG. 22 illustrates the configuration of an RF coil unit 25 ′ in which the first to fourth capacitors 1, 2, 3, 4, and the capacitor 11 are replaced with trimmer capacitors in the RF coil unit 25 of the first embodiment.
- FIG. 22 (a) is a view of the RF coil unit 25 ′ viewed from an oblique direction
- FIG. 22 (b) is a view of the RF coil unit 25 ′ viewed from the direction facing the z-axis
- FIG. 22C is a view of the RF coil unit 25 ′ viewed from the direction facing the y-axis.
- the RF coil unit 25 ′ includes a first capacitor 1, a second capacitor 2, a third capacitor 3, and a fourth capacitor 4, respectively, a first trimmer capacitor 71, a second trimmer capacitor 72, and a second capacitor.
- the third trimmer capacitor 73 and the fourth trimmer capacitor 74 are replaced, and the capacitor 11 is replaced with the fifth trimmer capacitor 75.
- the resonant frequency and the impedance of the first surface coil 5 and the second surface coil 6 the value C 1 of the first capacitor 1 (71), the value C 2 of the second capacitor 2 (72), first by adjusting the value C 4 of the three capacitors 3 values C 3 and the fourth capacitor 4 (73) (74), a desired value (e.g., resonance frequency 128 MHz, the impedance 50 [Omega) and.
- a desired value e.g., resonance frequency 128 MHz, the impedance 50 [Omega
- prevention of electromagnetic coupling between the surface coils is realized by adjusting the value C d of the capacitor 11 of the electromagnetic decoupling coil 13 (75).
- the transmission characteristic (S 12 ) of the signal from the first surface coil 5 to the second surface coil 6 is measured using a network analyzer, and the value of each capacitor is readjusted while observing the result.
- each capacitor is a trimmer capacitor, the value of the capacitor can be changed without removing and attaching the capacitor. For this reason, the above-described adjustment work can be performed more easily. Accordingly, it is possible to further reduce the labor and time for adjustment, and it is possible to easily prevent electromagnetic coupling between adjacent surface coils.
- the coil to which the present invention is applied is used as a receiving RF coil has been described as an example.
- the coil to which the present invention is applied can also be used as a transmission RF coil and a transmission / reception RF coil.
- the RF coil unit 25 used in the first embodiment is used as the transmission RF coil 107 .
- the schematic configuration of the MRI apparatus 100 of the present embodiment is the same as that of the first embodiment.
- the structure of the RF coil unit 25 and the method for adjusting the element value are the same as those in the first embodiment. Below, a different part from 1st embodiment is demonstrated.
- the first signal line 7 and the second signal line 8 shown in FIG. 3 are respectively baluns (balanced-unbalanced) for removing common node noise.
- the balun is connected to a transmission power amplifier (not shown). Further, the output of the transmission power amplifier is connected to the high-frequency magnetic field generator 106 via a coaxial cable.
- the decoupling circuit for preventing electromagnetic coupling with the receiving RF coil 114 provided in each of the first surface coil 5 and the second surface coil 6 is omitted.
- the high-frequency magnetic field generator 106 is connected to each transmission RF coil 107.
- a surface coil, a birdcage type coil, or an RF coil unit 25 is used for the receiving RF coil 114 depending on the application.
- the RF coil unit 25 adjusted as described above prevents the electromagnetic coupling between the first surface coil 5 and the second surface coil 6 and operates as the transmission RF coil 107. .
- the high-frequency magnetic field sent from the high-frequency magnetic field generator 106 is amplified by the transmission power amplifier and applied to the first signal line 7 and the second signal line 8 of the RF coil unit 25 through the balun.
- the state of electromagnetic coupling between the first surface coil 5 and the second surface coil 6 when a high-frequency magnetic field is applied to the RF coil unit 25 is the case where the RF coil unit 25 detects a high-frequency magnetic field. Is the same. Therefore, as in the case the first embodiment, by adjusting the value C d of the inductance L d and the capacitor 11 of the loop conductor 9 of the electromagnetic decoupling coil 13 of the RF coil unit 25 shown in FIG. 3, Electromagnetic coupling between the first surface coil 5 and the second surface coil 6 can be prevented. Therefore, the RF coil unit 25 applies a high-frequency magnetic field to the subject 10 without causing electromagnetic coupling.
- the electromagnetic coupling between the first surface coil 5 and the second surface coil 6 of the RF coil unit 25 operating as the transmission RF coil 107 is prevented by electromagnetic coupling.
- This can be prevented by adjusting the inductance L d of the loop conductor 9 of the coil 13 and the value C d of the capacitor 11.
- the advance fixed inductance L d of the loop conductor 9 it has be adjusted so as to satisfy the equation (12) only the value C d of the capacitor 11. For this reason, adjustment is only necessary by changing the value of one capacitor, and it is easy and has high reproducibility. Therefore, labor and time required for adjustment can be reduced, and the manufacturing cost of the RF coil can be reduced. Can be suppressed.
- FIG. 23 is a schematic configuration diagram of an MRI apparatus 100 ′ when the RF coil unit 25 of the first embodiment is used as a transmission / reception coil.
- the schematic configuration of the MRI apparatus 100 ′ of the present embodiment is almost the same as that of the first embodiment.
- the decoupling circuit driving apparatus 115 is not necessary, the RF coil for transmission 107 and the reception
- the transmission / reception RF coil 116 is used in place of the transmission / reception RF coil 114, the transmission / reception RF coil 116 is connected to the transmission / reception selector switch 103, and the two outputs of the transmission / reception selector switch 103 are the high-frequency magnetic field generator.
- 106 is different from the first embodiment in that it is connected to the receiver 106. Although omitted in FIG. 23, the transmission / reception selector switch 103 is connected to the sequencer 104.
- the structure of the RF coil unit 25 and the method of adjusting the element value are the same as in the first embodiment. Below, a different part from 1st embodiment is demonstrated.
- the first signal line 7 and the second signal line 8 shown in FIG. 3 each have a balun (balanced-unbalanced) for removing common node noise.
- the output of the balun is connected to two transmission / reception change-over switches 103, respectively.
- the RF coil unit 25 adjusted as described above prevents electromagnetic coupling between the first surface coil 5 and the second surface coil 6 and operates as a transmission / reception RF coil 116. .
- the high frequency magnetic field sent from the high frequency magnetic field generator 106 is amplified by the transmission power amplifier, passes through the transmission / reception changeover switch 103 whose transmission is turned on by the sequencer 104, passes through the balun, and passes through the first of the RF coil unit 25.
- the transmission power amplifier passes through the transmission / reception changeover switch 103 whose transmission is turned on by the sequencer 104, passes through the balun, and passes through the first of the RF coil unit 25.
- the state of magnetic coupling between the first surface coil 5 and the second surface coil 6 when a high frequency magnetic field is applied to the RF coil unit 25 is the case where the RF coil unit 25 detects a high frequency magnetic field. The same.
- the RF coil unit 25 operates as a transmission RF coil by applying a high-frequency magnetic field to the subject 10 without causing electromagnetic coupling. Further, when a magnetic resonance signal generated from the subject 10 is detected by the RF coil unit 25 after applying a high-frequency magnetic field to the subject 10, the RF coil shown in FIG. 3 is used as in the first embodiment.
- the RF coil unit 25 detects a magnetic resonance signal without causing electromagnetic coupling, and the detected signal is transmitted to the receiver 108 through the transmission / reception selector switch 103 whose reception is turned on by the sequencer 104.
- the RF coil unit 25 operates as the transmission / reception RF coil 116 without causing electromagnetic coupling.
- the electromagnetic coupling between the first surface coil 5 and the second surface coil 6 of the RF coil unit 25 operating as the transmission / reception RF coil 116 is prevented by electromagnetic coupling.
- This can be prevented by adjusting the inductance L d of the loop conductor 9 of the coil 13 and the value C d of the capacitor 11.
- the inductance L d of the loop conductor 9 is fixed in advance, only the value C d of the capacitor 11 may be adjusted so as to satisfy the equation (12). For this reason, the adjustment only needs to change the value of one capacitor, and it is easy and has high reproducibility. Therefore, it is possible to reduce the labor and time required for the adjustment, and the manufacturing cost of the RF coil is reduced. Can be suppressed.
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Abstract
Description
以下、本発明を適用する第一の実施形態について説明する。以下、本発明の実施形態を説明するための全図において、同一機能を有するものは同一符号を付し、その繰り返しの説明は省略する。
次に、本発明の第二の実施形態について説明する。本実施形態のMRI装置は基本的に第一の実施形態と同様である。しかし、RFコイルユニットが備える電磁気的結合防止用コイルの構成が異なる。図10は、本実施形態のRFコイルユニット26の構成を説明するための図である。本図に示すように、本実施形態のRFコイルユニット26の電磁気的結合防止用コイル13Bは、送信用RFコイル107との磁気結合を防止するデカップリング回路48を、その導体ループ9に備える。他の構成は、第一の実施形態のRFコイルユニット25と基本的に同様である。なお、本実施形態においても、座標系12のz軸方向を水平磁場方式のマグネット101が発生する静磁場900の向きとする。また、図3では図示を省略した第一の表面コイル5および第二の表面コイル6にそれぞれ挿入されたデカップリング回路49およびデカップリング回路50を図10では図示する。以下、RFコイルユニット26は、周波数fHの磁気共鳴信号を検出するものとして説明する。また、第一の実施形態同様、第一の表面コイル5および第二の表面コイル6のインピーダンス値は、それぞれ同じ所定の値Kとなるよう調整されているものとする。例えば、fHは、静磁場強度3テスラにおける水素原子核の磁気共鳴周波数128MHz、インピーダンス値Kは50Ωとすることができる。
次に、本発明の第三の実施形態について説明する。本実施形態のMRI装置は基本的に第一の実施形態と同様である。しかし、RFコイルユニットの構成が異なる。図13は、本実施形態のRFコイルユニット27の構成を説明するための図である。本図に示すように、本実施形態のRFコイルユニット27の電磁気的結合防止用コイル13Cは、ループ導体9の一部が板状導体91で構成される。この板状導体91の一方の面は、電磁気的結合防止用コイル13Cの中心を向いて配置される。他の構成は、第一の実施形態のRFコイルユニット25と基本的に同様である。
次に、本発明の第四の実施形態について説明する。本実施形態のMRI装置は基本的に第一の実施形態と同様である。しかし、RFコイルユニットの構成が異なる。図15は、本実施形態のRFコイルユニット28を説明するための図である。本実施形態のRFコイルユニット28は、アレイコイルとして構成される。以下、アレイコイル28と呼ぶ。図15(a)は、アレイコイル28を斜めから俯瞰した図であり、図15(b)は、アレイコイル28をz軸に対向する方向から見た図である。
次に、本発明の第五の実施形態について説明する。本実施形態のMRI装置は基本的に第一の実施形態と同様である。しかし、本実施形態では、受信用RFコイル114は、アレイコイルで構成される。図19は、本実施形態の受信用RFコイル114として用いられるアレイコイル29を説明するための図である。図19(a)は、アレイコイル29を斜めから俯瞰した図であり、図19(b)は、アレイコイル29をz軸に対向する方向から見た図であり、図19(c)は、アレイコイル29を2個用いる場合の例を、z軸に対向する方向から見た図である。
Claims (18)
- 複数の表面コイルを備え、共振周波数が所定の核の磁気共鳴信号の周波数である磁気共鳴撮像装置の高周波コイルであって、
前記複数の表面コイルの中の隣接した表面コイル間の電磁気的結合を防止する電磁気的結合防止手段を備え、
前記複数の表面コイルは、第一の方向に間隔を空けて配列され、
前記電磁気的結合防止手段は、キャパシタを備えるループ導体を備え、
前記ループ導体は、隣接する2つの前記表面コイルと磁気結合を生じさせ、かつ、前記隣接する2つの表面コイルの一方の表面コイルから生じた磁束であって他方の表面コイルに鎖交する磁束を打ち消す方向の磁束を発生する位置に当該隣接する両表面コイルに接触しないよう配置され、
前記ループ導体のインダクタンスと前記キャパシタの値とは、他方の前記表面コイルに鎖交する磁束の総和が最小となり、かつ、当該電磁気的結合防止手段の共振周波数が当該高周波コイルの共振周波数より小さくなるよう調整されること
を特徴とする高周波コイル。 - 請求項1記載の高周波コイルであって、
前記ループ導体は、前記隣接する2つの表面コイルの間に配置され、かつ、前記隣接する表面コイルの一方が実質的に位置する第一面と他方が実質的に位置する第二面との交線を含む第三面に実質的に配置されること
を特徴とする高周波コイル。 - 請求項3記載の高周波コイルであって、
前記第一面と前記第三面とが成す角度と、前記第二面と前記第三面とが成す角度とは等しいこと
を特徴とする高周波コイル。 - 請求項3記載の高周波コイルであって、
前記ループ導体の一部が、前記第一面と前記第二面とが交差する部分に配置されること
を特徴とする高周波コイル。 - 請求項1記載の高周波コイルであって、
前記第一の方向は、円周方向であること
を特徴とする高周波コイル。 - 請求項1記載の高周波コイルであって、
前記表面コイルは、前記第一の方向に加え、当該第一の方向と異なる第二の方向に配列されること
を特徴とする高周波コイル。 - 請求項7記載の高周波コイルであって、
前記電磁気的結合防止手段は、前記第一の方向および前記第二の方向の少なくとも1方向の、前記隣接する表面コイル間に配置されること
を特徴とする高周波コイル。 - 請求項1記載の高周波コイルであって、
前記表面コイルは、ループコイルであること
を特徴とする高周波コイル。 - 請求項1記載の高周波コイルであって、
前記表面コイルは、8の字型コイルであること
を特徴とする高周波コイル。 - 請求項1記載の高周波コイルであって、
前記電磁気的結合防止手段が備えるキャパシタの少なくとも1つは、トリマキャパシタであること、
を特徴とする高周波コイル。 - 請求項1記載の高周波コイルであって、
前記電磁気的結合防止手段の前記ループ導体は、少なくとも一部が板状導体で構成され、
前記板状導体の一方の面が、前記ループ導体によるループの中心を向いていること
を特徴とする高周波コイル。 - 請求項1記載の高周波コイルであって、
当該高周波コイルは、前記所定の核の磁気共鳴信号を検出する受信用コイルとして動作し、
前記電磁気的結合防止手段の前記ループ導体は、送信用コイルとの磁気結合を防止するデカップリング手段を備えること
を特徴とする高周波コイル。 - 請求項13記載の高周波コイルであって、
前記デカップリング手段は、PINダイオードとインダクタとを直列接続した回路にキャパシタが並列に接続された回路であること
を特徴とする高周波コイル。 - 請求項13記載の高周波コイルであって、
前記デカップリング手段は、クロスダイオードとインダクタとを直列接続した回路にキャパシタが並列に接続された回路であること
を特徴とする高周波コイル。 - 静磁場を形成する静磁場形成手段と、傾斜磁場を形成する傾斜磁場形成手段と、高周波磁場を形成する高周波磁場形成手段と、被検体に前記高周波磁場を照射する送信用コイルと、前記被検体から発生する磁気共鳴信号を検出する受信用コイルと、前記検出した磁気共鳴信号を受信する受信手段と、前記傾斜磁場形成手段、前記高周波磁場形成手段および前記受信手段を制御する制御手段と、を備える磁気共鳴撮像装置であって、
前記受信用コイルは、請求項1記載の高周波コイルであり、
前記高周波コイルは、前記送信用コイルとの磁気結合を防止するデカップリング手段を備えること
を特徴とする磁気共鳴撮像装置。 - 静磁場を形成する静磁場形成手段と、傾斜磁場を形成する傾斜磁場形成手段と、高周波磁場を形成する高周波磁場形成手段と、被検体に前記高周波磁場を照射する送信用コイルと、前記被検体から発生する磁気共鳴信号を検出する受信用コイルと、前記検出した磁気共鳴信号を受信する受信手段と、前記傾斜磁場形成手段、前記高周波磁場形成手段および前記受信手段を制御する制御手段と、を備える磁気共鳴撮像装置であって、
前記送信用コイルは、請求項1記載の高周波コイルであり、
前記高周波コイルは、前記受信用コイルとの磁気結合を防止するデカップリング手段を備えること
を特徴とする磁気共鳴撮像装置。 - 静磁場を形成する静磁場形成手段と、傾斜磁場を形成する傾斜磁場形成手段と、高周波磁場を形成する高周波磁場形成手段と、被検体に前記高周波磁場を照射するとともに前記被検体から発生する磁気共鳴信号を検出する送受信用コイルと、前記検出した磁気共鳴信号を受信する受信手段と、前記傾斜磁場形成手段、前記高周波磁場形成手段および前記受信手段を制御する制御手段と、を備える磁気共鳴撮像装置であって、
前記送受信用コイルは、請求項1記載の高周波コイルであること
を特徴とする磁気共鳴撮像装置。
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Cited By (7)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
JP2013530019A (ja) * | 2010-07-01 | 2013-07-25 | メドラッド インコーポレーテッド | 多チャンネル直腸内コイルおよびそのためのインターフェース装置 |
CN103344927A (zh) * | 2013-06-26 | 2013-10-09 | 深圳市特深电气有限公司 | 磁共振射频线圈以及磁共振成像系统 |
JP5705884B2 (ja) * | 2011-02-14 | 2015-04-22 | 株式会社日立製作所 | Rfコイル及び磁気共鳴撮像装置 |
KR20180062755A (ko) * | 2016-12-01 | 2018-06-11 | 가천대학교 산학협력단 | Z-축 방향 어레이 구조의 자기공명 영상용 새장형 코일 조립체 |
WO2018225484A1 (ja) * | 2017-06-09 | 2018-12-13 | 株式会社日立製作所 | アレイコイル及び磁気共鳴撮像装置 |
CN112394308A (zh) * | 2019-08-15 | 2021-02-23 | 西门子(深圳)磁共振有限公司 | 发射射频线圈单元及磁共振系统 |
WO2021097940A1 (zh) * | 2019-11-20 | 2021-05-27 | 深圳先进技术研究院 | 多通道射频线圈装置及核磁共振成像系统 |
Families Citing this family (22)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
JP5247214B2 (ja) * | 2008-04-04 | 2013-07-24 | 株式会社日立製作所 | 高周波磁場コイル及び磁気共鳴撮影装置 |
EP2745131A1 (en) * | 2011-09-07 | 2014-06-25 | Koninklijke Philips N.V. | Mode splitter/combiner for noise figure minimization and control of power in rf coil arrays |
US20180278079A1 (en) * | 2012-01-11 | 2018-09-27 | Wheel Charge Technologies LLC | Apparatus for Wireless Power Transmission Between an External Power Source and an Electric Mobility Vehicle |
JP2013158589A (ja) * | 2012-02-08 | 2013-08-19 | Toshiba Corp | 医用画像診断装置 |
DE102012205664B4 (de) * | 2012-04-05 | 2013-10-31 | Siemens Aktiengesellschaft | Verfahren und Steuervorrichtung zur Ansteuerung eines Magnetresonanzsystems |
US9885766B2 (en) | 2012-04-17 | 2018-02-06 | Transarray LLC | Magnetic-resonance transceiver-phased array that compensates for reactive and resistive components of mutual impedance between array elements and circuit and method thereof |
FR3002699B1 (fr) * | 2013-02-27 | 2016-07-01 | Commissariat Energie Atomique | Antenne haute frequence a voies multiples, notamment pour appareil d'imagerie par resonance magnetique nucleaire. |
US10107878B2 (en) * | 2013-10-17 | 2018-10-23 | Hitachi, Ltd. | Magnetic resonance imaging apparatus and antenna device |
WO2015099509A1 (ko) * | 2013-12-27 | 2015-07-02 | 삼성전자 주식회사 | 알에프 코일 및 이를 포함하고 있는 알에프 코일 어셈블리 |
KR102125551B1 (ko) * | 2013-12-27 | 2020-06-22 | 삼성전자주식회사 | 알에프 코일 장치 |
KR102125554B1 (ko) * | 2014-01-08 | 2020-06-22 | 삼성전자주식회사 | 알에프 코일 구조물 |
WO2015102434A1 (ko) * | 2014-01-03 | 2015-07-09 | 삼성전자 주식회사 | 알에프 코일 |
EP3387456B1 (en) | 2015-12-08 | 2024-02-28 | Koninklijke Philips N.V. | Radio frequency coil-array for magnetic resonance examination system |
FR3046701B1 (fr) * | 2016-01-08 | 2018-03-23 | Commissariat A L'energie Atomique Et Aux Energies Alternatives | Antenne reseau, en particulier pour imagerie par resonance magnetique nucleaire, comprenant des resonateurs electromagnetiques lineaires et au moins un dispositif de decouplage |
JP6590736B2 (ja) * | 2016-03-04 | 2019-10-16 | 株式会社日立製作所 | 高周波コイル及びそれを用いた磁気共鳴撮像装置 |
CN106140046B (zh) * | 2016-07-06 | 2019-02-22 | 江南大学 | 阵列式感应电场流体反应系统及其应用 |
KR101842576B1 (ko) | 2016-10-31 | 2018-03-29 | 가천대학교 산학협력단 | Rf 송신 효율이 개선된 자기공명 영상용 rf 코일 |
US11467236B2 (en) * | 2019-03-12 | 2022-10-11 | Canon Medical Systems Corporation | Biological information monitoring apparatus and MRI apparatus |
US11204402B2 (en) * | 2019-03-12 | 2021-12-21 | Quality Electrodynamics, Llc | Minimizing coupling in multi-row cylindrical-shaped magnetic resonance imaging (MRI) radio frequency (RF) coil |
KR20210094343A (ko) * | 2020-01-21 | 2021-07-29 | 고려대학교 산학협력단 | 전기장 기반 암치료 장치 |
US11442125B2 (en) * | 2020-09-22 | 2022-09-13 | Quality Electrodynamics, Llc | Gapped multi-birdcage MRI RF coil |
US20240036127A1 (en) * | 2022-08-01 | 2024-02-01 | Zepp Europe Holding B.V. | Quadrature RF Transmit Coil At A Vertical Main Field MRI System |
Citations (2)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
JP2000225104A (ja) * | 1999-02-05 | 2000-08-15 | Toshiba Corp | Rfコイルおよびmri装置 |
JP2003180659A (ja) * | 2001-11-21 | 2003-07-02 | Koninkl Philips Electronics Nv | 磁気共鳴撮像装置用のrfコイル系 |
Family Cites Families (19)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4825162A (en) | 1987-12-07 | 1989-04-25 | General Electric Company | Nuclear magnetic resonance (NMR) imaging with multiple surface coils |
JPH02261428A (ja) | 1989-03-31 | 1990-10-24 | Yokogawa Medical Syst Ltd | Mri用表面コイルのデカップリング回路 |
JPH03216938A (ja) | 1990-01-19 | 1991-09-24 | Matsushita Electric Ind Co Ltd | 画像表示装置 |
JP3197262B2 (ja) | 1990-02-28 | 2001-08-13 | 株式会社東芝 | 磁気共鳴映像装置 |
US5280246A (en) * | 1990-11-16 | 1994-01-18 | Hitachi, Ltd. | Nuclear magnetic resonance apparatus |
JPH04180733A (ja) * | 1990-11-16 | 1992-06-26 | Hitachi Ltd | 核磁気共鳴装置用表面コイル |
JPH0763459B2 (ja) * | 1991-12-13 | 1995-07-12 | 株式会社日立メディコ | 磁気共鳴イメージング装置の高周波受信コイル |
US5327898A (en) * | 1991-10-11 | 1994-07-12 | Hitachi Medical Corp. | Signal receiving coil device for MRI apparatus |
JPH05269108A (ja) * | 1992-03-25 | 1993-10-19 | Toshiba Corp | 磁気共鳴映像装置 |
JP3216938B2 (ja) | 1993-06-08 | 2001-10-09 | 株式会社日立製作所 | Mri用rfプローブ及び磁気共鳴撮影装置 |
JPH0779948A (ja) | 1993-09-14 | 1995-03-28 | Toshiba Corp | 磁気共鳴映像装置 |
JPH08229019A (ja) * | 1995-02-28 | 1996-09-10 | Toshiba Corp | 中和回路及びそれを用いた磁気共鳴イメージング装置 |
US5804969A (en) * | 1995-07-28 | 1998-09-08 | Advanced Mammography Systems, Inc. | MRI RF coil |
DE60127382T2 (de) * | 2000-11-24 | 2007-12-06 | Koninklijke Philips Electronics N.V. | Verfahren zum erhalt von bildern magnetischer resonanz durch unterabtastung in einem mri-gerät mit vertikalem feld |
JP2002169374A (ja) | 2000-12-05 | 2002-06-14 | Fuji Xerox Co Ltd | 現像剤担持体の再生方法 |
DE10244172A1 (de) * | 2002-09-23 | 2004-03-11 | Siemens Ag | Antennenanordnung für ein Magnetresonanzgerät |
WO2006137946A2 (en) * | 2004-11-23 | 2006-12-28 | M2M Imaging Corp. | Coil decoupling in magnetic resonance imaging |
WO2007117604A2 (en) * | 2006-04-07 | 2007-10-18 | The Government Of The United States Of America, Represented By The Secretary, Department Of Health And Human Services | Inductive decoupling of an rf coil array |
DE102010005666B4 (de) | 2010-01-26 | 2024-05-08 | Dr. Ing. H.C. F. Porsche Aktiengesellschaft | Batteriemanagementvorrichtung |
-
2009
- 2009-07-22 WO PCT/JP2009/063107 patent/WO2010021222A1/ja active Application Filing
- 2009-07-22 JP JP2010525645A patent/JP5179588B2/ja active Active
- 2009-07-22 US US13/054,474 patent/US8742759B2/en not_active Expired - Fee Related
Patent Citations (2)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
JP2000225104A (ja) * | 1999-02-05 | 2000-08-15 | Toshiba Corp | Rfコイルおよびmri装置 |
JP2003180659A (ja) * | 2001-11-21 | 2003-07-02 | Koninkl Philips Electronics Nv | 磁気共鳴撮像装置用のrfコイル系 |
Non-Patent Citations (2)
Title |
---|
P.QU ET AL.: "A Shielding-based Decoupling Technique for Coil Array Design", PROCEEDINGS OF THE INTERNATIONAL SOCIETY FOR MAGNETIC RESONANCE IN MEDICINE, 21 May 2004 (2004-05-21), pages 1605 * |
Z.XIE ET AL.: "A novel decoupling technique for non-overlapped microstrip array coil at 7T MR imaging", PROCEEDINGS OF THE INTERNATIONAL SOCIETY FOR MAGNETIC RESONANCE IN MEDICINE, 9 May 2008 (2008-05-09), pages 1068 * |
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JP2013530019A (ja) * | 2010-07-01 | 2013-07-25 | メドラッド インコーポレーテッド | 多チャンネル直腸内コイルおよびそのためのインターフェース装置 |
US9817090B2 (en) | 2010-07-01 | 2017-11-14 | Bayer Healthcare Llc | Multi-channel endorectal coils and interface devices therefor |
US10197645B2 (en) | 2010-07-01 | 2019-02-05 | Bayer Healthcare Llc | Multi-channel endorectal coils and interface devices therefor |
JP5705884B2 (ja) * | 2011-02-14 | 2015-04-22 | 株式会社日立製作所 | Rfコイル及び磁気共鳴撮像装置 |
CN103344927A (zh) * | 2013-06-26 | 2013-10-09 | 深圳市特深电气有限公司 | 磁共振射频线圈以及磁共振成像系统 |
KR20180062755A (ko) * | 2016-12-01 | 2018-06-11 | 가천대학교 산학협력단 | Z-축 방향 어레이 구조의 자기공명 영상용 새장형 코일 조립체 |
KR101890261B1 (ko) | 2016-12-01 | 2018-08-22 | 가천대학교 산학협력단 | Z-축 방향 어레이 구조의 자기공명 영상용 새장형 코일 조립체 |
WO2018225484A1 (ja) * | 2017-06-09 | 2018-12-13 | 株式会社日立製作所 | アレイコイル及び磁気共鳴撮像装置 |
CN112394308A (zh) * | 2019-08-15 | 2021-02-23 | 西门子(深圳)磁共振有限公司 | 发射射频线圈单元及磁共振系统 |
CN112394308B (zh) * | 2019-08-15 | 2024-01-30 | 西门子(深圳)磁共振有限公司 | 发射射频线圈单元及磁共振系统 |
WO2021097940A1 (zh) * | 2019-11-20 | 2021-05-27 | 深圳先进技术研究院 | 多通道射频线圈装置及核磁共振成像系统 |
Also Published As
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US20110121834A1 (en) | 2011-05-26 |
US8742759B2 (en) | 2014-06-03 |
JPWO2010021222A1 (ja) | 2012-01-26 |
JP5179588B2 (ja) | 2013-04-10 |
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