JP2019202088A - Magnetic resonance imaging device and receiving coil - Google Patents

Abstract

To transmit MR signals between a receiving coil and a rack without going through a communication cable.SOLUTION: A magnetic resonance imaging device includes a rack, a receiving coil, rack communication units 171, 172, and coil communication units 181, 182. The rack has a bore 91 in which a subject is placed. The receiving coil is placed in the bore 91 and receives a magnetic resonance signal from the subject. The rack communication units 171, 172 are provided in the bore 91. The coil communication units 181, 182 are provided in the receiving coil, perform near field communication with the rack communication units 171, 172, and transmit magnetic resonance signals to the rack communication units 171, 172.SELECTED DRAWING: Figure 3

Description

  Embodiments described herein relate generally to a magnetic resonance imaging apparatus and a receiving coil.

  A magnetic resonance imaging (MRI) apparatus applies a radio frequency (RF) magnetic field to a subject placed in a static magnetic field, and generates magnetic resonance (Magnetic) generated from the subject under the influence of the RF magnetic field. This is a device that generates an image in a subject based on a Resonance (MR) signal.

  For example, the MRI apparatus includes a gantry having a hollow bore formed in a cylindrical shape, and generates a static magnetic field in a space in the bore. At the time of imaging, the MRI apparatus applies an RF magnetic field to the subject arranged in the bore, and receives MR signals generated from the subject by a receiving coil arranged in the bore together with the subject. Here, the MR signal received by the receiving coil is transmitted to the signal processing unit via a communication cable connected to the receiving coil, and is subjected to processing for image generation.

JP 2006-054931 A JP-A-2018-008105 JP-A-2006-101202

  The problem to be solved by the present invention is to transmit the MR signal between the receiving coil and the gantry without using a communication cable.

  The MRI apparatus according to the embodiment includes a gantry, a receiving coil, a gantry communication unit, and a coil communication unit. The gantry has a bore in which a subject is arranged. The receiving coil is disposed in the bore and receives a magnetic resonance signal from the subject. The gantry communication unit is provided in the bore. The coil communication unit is provided in the receiving coil, performs near field communication with the gantry communication unit, and transmits the magnetic resonance signal to the gantry communication unit.

FIG. 1 is a diagram illustrating a configuration example of an MRI apparatus according to the first embodiment. FIG. 2 is a perspective view showing a configuration example of the body coil according to the first embodiment. FIG. 3 is a front view illustrating the configuration of the body coil, the spine coil, and the gantry according to the first embodiment. FIG. 4 is a side view showing the configuration of the body coil, the spine coil, and the gantry according to the first embodiment. FIG. 5 is a perspective view illustrating a configuration example of a body coil according to the second embodiment. FIG. 6 is a front view showing configurations of a body coil, a spine coil, and a gantry according to the second embodiment. FIG. 7 is a side view showing configurations of a body coil, a spine coil, and a gantry according to the second embodiment. FIG. 8 is a perspective view illustrating a configuration example of a body coil according to the third embodiment. FIG. 9 is a front view illustrating configurations of a body coil, a spine coil, and a gantry according to the third embodiment. FIG. 10 is a side view showing configurations of a body coil, a spine coil, and a gantry according to the third embodiment. FIG. 11 is a perspective view illustrating a configuration example of a head coil according to the fourth embodiment. FIG. 12 is a front view illustrating the configuration of the head coil and the gantry according to the fourth embodiment. FIG. 13 is a side view showing configurations of a head coil and a gantry according to the fourth embodiment. FIG. 14 is a perspective view illustrating a configuration example of a head coil according to the fifth embodiment. FIG. 15 is a front view illustrating the configuration of the head coil and the gantry according to the fifth embodiment. FIG. 16 is a side view showing configurations of a head coil and a gantry according to the fifth embodiment. FIG. 17 is a perspective view illustrating a configuration example of a head coil according to the sixth embodiment. FIG. 18 is a front view showing configurations of a head coil and a gantry according to the sixth embodiment. FIG. 19 is a side view showing configurations of a body coil and a gantry according to the sixth embodiment.

  Hereinafter, embodiments of an MRI apparatus and a receiving coil will be described in detail with reference to the drawings.

(First embodiment)
FIG. 1 is a diagram illustrating a configuration example of an MRI apparatus according to the first embodiment.

  As shown in FIG. 1, the MRI apparatus 100 according to the first embodiment includes a static magnetic field magnet 1, a gradient magnetic field coil 2, a gradient magnetic field power supply 3, a whole body coil 4, a local coil 5, a bed 6, and a transmission circuit 7. , Receiving circuit 8, frame 9, interface 10, display 11, storage circuit 12, and processing circuits 13-16.

  The static magnetic field magnet 1 generates a static magnetic field in the imaging space where the subject S is arranged. Specifically, the static magnetic field magnet 1 is formed in a hollow, substantially cylindrical shape (including one having a cross-sectional shape orthogonal to the central axis that is elliptical), and in an imaging space disposed on the inner peripheral side. Generate a static magnetic field. For example, the static magnetic field magnet 1 includes a cooling container formed in a substantially cylindrical shape, and a magnet such as a superconducting magnet immersed in a coolant (for example, liquid helium) filled in the cooling container. The static magnetic field magnet 1 may generate a static magnetic field using a permanent magnet, for example.

  The gradient magnetic field coil 2 generates a gradient magnetic field in the imaging space where the subject S is arranged. Specifically, the gradient magnetic field coil 2 is formed in a hollow, substantially cylindrical shape (including one having a cross-sectional shape orthogonal to the central axis that is elliptical), and is supplied with a current supplied from the gradient magnetic field power supply 3. Based on this, a gradient magnetic field is generated in the imaging space arranged on the inner circumference side. The gradient magnetic field coil 2 has an X coil, a Y coil, and a Z coil corresponding to the X axis, the Y axis, and the Z axis, respectively, and corresponds to the current supplied from the gradient magnetic field power supply 3 to each coil. Thus, gradient magnetic fields are generated in the imaging space along the directions of the X, Y, and Z axes orthogonal to each other.

  Here, the X axis, the Y axis, and the Z axis constitute an apparatus coordinate system unique to the MRI apparatus 100. For example, the X axis is set along the horizontal direction, the Y axis is set along the vertical direction, and the Z axis coincides with the axial direction of the gradient coil 2 and is generated by the static magnetic field magnet 1. It is set along the magnetic flux of the static magnetic field.

  The gradient magnetic field power supply 3 supplies current to each of the X coil, the Y coil, and the Z coil of the gradient magnetic field coil 2 so that the gradient magnetic field along each of the X axis, Y axis, and Z axis directions. Is generated in the imaging space. As described above, the gradient magnetic field power supply 3 appropriately supplies currents to the X coil, the Y coil, and the Z coil, so that the gradient magnetic fields along the readout direction, the phase encoding direction, and the slice direction orthogonal to each other are obtained. Can be generated.

  Here, the axis along the readout direction, the axis along the phase encoding direction, and the axis along the slice direction constitute a logical coordinate system for defining a slice area or a volume area to be imaged. Specifically, the gradient magnetic field along each of the readout direction, the phase encoding direction, and the slice gradient magnetic field is superimposed on the static magnetic field generated by the static magnetic field magnet 1, thereby causing the MR signal generated from the subject S to be generated. Give spatial location information. The gradient magnetic field in the lead-out direction gives position information along the lead-out direction to the MR signal by changing the frequency of the MR signal according to the position in the lead-out direction. The phase encoding gradient magnetic field changes the phase of the MR signal along the phase encoding direction, thereby giving position information along the phase encoding direction to the MR signal. The slice gradient magnetic field gives position information along the slice direction to the MR signal. For example, the slice gradient magnetic field is used to determine the direction, thickness, and number of slice areas when the imaging area is a slice area, and according to the position in the slice direction when the imaging area is a volume area. And used to change the phase of the MR signal.

  The whole-body coil 4 is an RF coil that applies an RF magnetic field to an imaging space in which the subject S is arranged and receives MR signals generated from the subject S due to the influence of the RF magnetic field. Specifically, the whole-body coil 4 is formed in a hollow, substantially cylindrical shape (including one that has an elliptical cross-sectional shape perpendicular to the central axis), and an RF pulse signal supplied from the transmission circuit 7. Based on the above, an RF magnetic field is applied to the imaging space arranged on the inner peripheral side. The whole body coil 4 receives an MR signal generated from the subject S due to the influence of the RF magnetic field, and outputs the received MR signal to the receiving circuit 8. For example, the whole body coil 4 is a QD (quadrature) coil.

  The local coil 5 is an RF coil that receives MR signals generated from the subject S. Specifically, the local coil 5 is an RF coil prepared for each region of the subject S, and is disposed in the vicinity of the region to be imaged when the subject S is imaged. The local coil 5 receives the MR signal generated from the subject S due to the influence of the RF magnetic field applied by the whole body coil 4, and outputs the received MR signal to the receiving circuit 8. The local coil 5 may further have a function of a transmission coil that applies an RF magnetic field to the subject S. In that case, the local coil 5 is connected to the transmission circuit 7 and applies an RF magnetic field to the subject S based on the RF pulse signal supplied from the transmission circuit 7. For example, the local coil 5 is an array coil composed of a surface coil or a plurality of surface coils.

  The bed 6 includes a top plate 61 on which the subject S is placed, and when the subject S is imaged, the top plate 61 on which the subject S is placed moves to the imaging space. For example, the bed 6 is installed so that the longitudinal direction of the top plate 61 is parallel to the central axis of the static magnetic field magnet 1.

  The transmission circuit 7 outputs an RF pulse signal corresponding to the Larmor frequency specific to the target nucleus placed in the static magnetic field to the whole body coil 4. Specifically, the transmission circuit 7 includes a pulse generator, an RF generator, a modulator, and an amplifier. The pulse generator generates an RF pulse signal waveform. The RF generator generates an RF signal having a resonance frequency. The modulator generates an RF pulse signal by modulating the amplitude of the RF signal generated by the RF generator with the waveform generated by the pulse generator. The amplifier amplifies the RF pulse signal generated by the modulator and outputs it to the whole body coil 4.

  The receiving circuit 8 generates MR signal data based on the MR signals received by the whole body coil 4 and the local coil 5, and outputs the generated MR signal data to the processing circuit 14. Specifically, the receiving circuit 8 includes a detector, and MR signal data is obtained by subtracting the resonance frequency component from the MR signal received by the whole body coil 4 and the local coil 5 by the detector. And the generated MR signal data is output to the processing circuit 14.

  The gantry 9 has a hollow bore 91 formed in a substantially cylindrical shape (including one having a cross section perpendicular to the central axis is elliptical), and includes a static magnetic field magnet 1, a gradient magnetic field coil 2, and a whole body. The coil 4 is supported. Specifically, the gantry 9 has the gradient magnetic field coil 2 disposed on the inner peripheral side of the static magnetic field magnet 1, the whole body coil 4 disposed on the inner peripheral side of the gradient magnetic field coil 2, and the inner periphery of the whole body coil 4. The static magnetic field magnet 1, the gradient magnetic field coil 2, and the whole body coil 4 are supported in a state where the bore 91 is disposed on the side. Here, the space in the bore 91 of the gantry 9 is an imaging space in which the subject S is arranged when the subject S is imaged.

  Here, an example in which the MRI apparatus 100 has a so-called tunnel type configuration in which the static magnetic field magnet 1, the gradient magnetic field coil 2, and the whole body coil 4 are each formed in a substantially cylindrical shape will be described. The form is not limited to this. For example, the MRI apparatus 100 has a so-called open type configuration in which a pair of static magnetic field magnets, a pair of gradient magnetic field coils, and a pair of RF coils are disposed so as to face each other with an imaging space in which the subject S is disposed. You may do it. In this case, the space between the pair of static magnetic field magnets, the pair of gradient magnetic field coils, and the pair of RF coils corresponds to the bore in the tunnel type configuration.

  The interface 10 receives various instructions and various information input operations from the operator. Specifically, the interface 10 is connected to the processing circuit 16, converts an input operation received from the operator into an electrical signal, and outputs the electrical signal to the processing circuit 16. For example, the interface 10 includes a trackball, a switch button, a mouse, a keyboard, a touch pad for performing an input operation by touching an operation surface, and a display screen for setting an imaging condition, a region of interest (ROI), and the like. And a touch pad integrated with each other, a non-contact input circuit using an optical sensor, a voice input circuit, and the like. In the present specification, the interface 10 is not limited to one having physical operation components such as a mouse and a keyboard. For example, an example of the interface 10 includes an electric signal processing circuit that receives an electric signal corresponding to an input operation from an external input device provided separately from the apparatus and outputs the electric signal to the control circuit.

  The display 11 displays various information and various images. Specifically, the display 11 is connected to the processing circuit 16, converts various information and various image data sent from the processing circuit 16 into electrical signals for display, and outputs them. For example, the display 11 is realized by a liquid crystal monitor, a CRT (Cathode Ray Tube) monitor, a touch panel, or the like.

  The storage circuit 12 stores various data. Specifically, the storage circuit 12 stores MR signal data and image data. For example, the storage circuit 12 is realized by a semiconductor memory device such as a RAM (Random Access Memory) or a flash memory, a hard disk, an optical disk, or the like.

  The processing circuit 13 has a bed control function 131. The bed control function 131 controls the operation of the bed 6 by outputting a control electric signal to the bed 6. For example, the bed control function 131 receives an instruction to move the table 61 in the longitudinal direction, the vertical direction, or the horizontal direction from the operator via the interface 10 and moves the table 61 according to the received instruction. The moving mechanism of the top plate 61 of 6 is operated.

  The processing circuit 14 has a data collection function 141. The data collection function 141 collects MR signal data of the subject S by driving the gradient magnetic field power supply 3, the transmission circuit 7 and the reception circuit 8. Specifically, the data collection function 141 collects MR signal data by executing various pulse sequences based on the sequence execution data output from the processing circuit 16. Here, the sequence execution data includes the timing at which the gradient magnetic field power supply 3 supplies current to the gradient magnetic field coil 2 and the strength of the supplied current, and the strength and supply timing of the RF pulse signal supplied to the whole body coil 4 by the transmission circuit 7. The information defines the detection timing and the like at which the receiving circuit 8 detects the MR signal. The data collection function 141 receives MR signal data from the receiving circuit 8 as a result of executing various pulse sequences, and stores the received MR signal data in the storage circuit 12. Here, the set of MR signal data received by the data collection function 141 is arranged in two dimensions or three dimensions according to the position information given by the readout gradient magnetic field, phase encoding gradient magnetic field, and slice gradient magnetic field described above. As a result, it is stored in the storage circuit 12 as data constituting the k space.

  The processing circuit 15 has an image generation function 151. The image generation function 151 generates an image based on the MR signal data stored in the storage circuit 12. Specifically, the image generation function 151 reads the MR signal data stored in the storage circuit 12 by the data collection function 141, and performs post-processing, that is, reconstruction processing such as Fourier transform on the read MR signal data. To generate an image. Further, the image generation function 151 causes the storage circuit 12 to store the image data of the generated image.

  The processing circuit 16 has a main control function 161. The main control function 161 performs overall control of the MRI apparatus 100 by controlling each component included in the MRI apparatus 100. Specifically, the main control function 161 displays on the display 11 a GUI (Graphical User Interface) for accepting various instructions and various information input operations from the operator. The main control function 161 controls each component included in the MRI apparatus 100 in accordance with an input operation received via the interface 10. For example, the main control function 161 receives input of imaging conditions from the operator via the interface 10. The main control function 161 generates sequence execution data based on the accepted imaging conditions, and transmits the sequence execution data to the processing circuit 14 to execute various pulse sequences. For example, the main control function 161 reads out image data from the storage circuit 12 and outputs it to the display 11 in response to a request from the operator.

  Here, the processing circuits 13 to 16 described above are realized by, for example, a processor. In this case, the processing function of each processing circuit is stored in the storage circuit 12 in the form of a program that can be executed by a computer, for example. Each processing circuit implements a function corresponding to each program by reading each program from the storage circuit 12 and executing it. Here, each processing circuit may be constituted by a plurality of processors, and each processing function may be realized by each processor executing a program. In addition, the processing functions of each processing circuit may be realized by being appropriately distributed or integrated into a single or a plurality of processing circuits. Also, here, a single storage circuit 12 has been described as storing a program corresponding to each processing function. However, a plurality of storage circuits are arranged in a distributed manner, and the processing circuits correspond to individual storage circuits. It may be configured to read the program.

  The overall configuration of the MRI apparatus 100 according to the first embodiment has been described above. Under such a configuration, at the time of imaging, the MRI apparatus 100 applies an RF magnetic field to the subject S disposed in the bore 91, and the local coil 5 disposed in the bore 91 together with the subject S An MR signal generated from the subject S is received. Here, the MR signal received by the local coil 5 is transmitted to the receiving circuit 8 and subjected to the above-described processing for image generation.

  In general, in such a configuration, the MR signal received by the local coil 5 is often transmitted to the receiving circuit 8 via a communication cable connected to the local coil 5. For example, a plurality of coil ports for connecting a communication cable connected to the local coil 5 are provided at the front and rear and the left and right ends of the top plate 61, and via the cables arranged in the bed 6, MR signals input from the coil ports are transmitted to the receiving circuit 8.

  However, when the cable is arranged in the bed 6, the cable is moved in accordance with the movement of the top plate 61, so that the length of the cable is longer than the shortest distance between the local coil 5 and the receiving circuit 8. There is a need to. Further, a plurality of cables are used according to the number of coil ports provided on the top board 61. However, since the space under the top board 61 and the bed 6 is limited, the thickness of the cable is reduced. There is a need to. As described above, when cables are arranged in the bed 6, it is necessary to arrange a large number of long and thin cables in the bed 6. Further, a movable mechanism for moving the cables is provided under the top plate 61. Since it is necessary to provide, the structure of the top plate 61 and the bed 6 will be complicated. Further, providing the movable mechanism for the cable under the top plate 61 limits the securing of the imaging space in which the subject S is arranged.

  For this reason, the MRI apparatus 100 according to the present embodiment transmits the MR signal between the local coil 5 and the gantry 9 without using a communication cable by using the proximity wireless communication technology. It is configured to be able to.

  Specifically, the MRI apparatus 100 is provided in the bore 91 of the gantry 9, and is provided in the gantry communication unit connected to the receiving circuit 8 that processes the MR signal, and in the local coil 5. A coil communication unit that performs close proximity wireless communication and transmits an MR signal to the gantry communication unit. The local coil 5 is an example of a receiving coil, and the receiving circuit 8 is an example of a signal processing unit.

  Hereinafter, the MRI apparatus 100 having such a configuration will be described in detail. In the present embodiment, an example in which a body coil for body imaging, a spine coil for spine imaging, and a head coil for head imaging are used as examples of the local coil 5 will be described.

  FIG. 2 is a perspective view showing a configuration example of the body coil according to the first embodiment. FIG. 3 is a front view showing configurations of the body coil, the spine coil, and the gantry according to the first embodiment. FIG. 4 is a side view showing configurations of the body coil, the spine coil, and the gantry according to the first embodiment.

  As shown in FIG. 2, the body coil 51 according to the present embodiment is an array coil formed in a rectangular flat plate shape, and is used by being mounted on the body of the subject S at the time of imaging. Specifically, the body coil 51 has a longitudinal direction (direction of arrow LD shown in FIG. 2) along the body axis direction of the body of the subject S, and a short side direction (direction of arrow SD shown in FIG. 2). It is used by being aligned along the width direction of the body of the specimen S. The body coil 51 is flexible so that it can be bent in accordance with the body surface of the subject S.

  In the present embodiment, the body coil 51 is provided with two first coil communication units 181. Specifically, a first coil communication unit 181 is provided at each of both side portions of the body coil 51 in the short direction. In FIG. 2, only the first coil communication unit 181 on one side portion is shown because of the arrangement.

  Here, in the present embodiment, the first coil communication unit 181 is disposed at a substantially central position in the longitudinal direction of the body coil 51 on the side portion of the body coil 51.

  3 and 4, the spine coil 52 according to the present embodiment is built in the top plate 61, and the subject S is used on the upper side during imaging. Specifically, the spine coil 52 is an array coil formed in an elongated rectangular flat plate shape, and is disposed so as to extend along the longitudinal direction of the top plate 61.

  In the present embodiment, the spine coil 52 is provided with one second coil communication unit 182. Specifically, the second coil communication unit 182 is provided at a substantially central position in the short direction of the spine coil 52.

  Here, in the present embodiment, the second coil communication unit 182 is disposed at a substantially central position in the longitudinal direction of the spine coil 52.

  As shown in FIGS. 3 and 4, the gantry 9 includes a gantry rail 92 that supports the top plate 61 on which the subject S is placed movably in the bore 91. The gantry rail 92 is provided on the lower side in the bore 91 of the gantry 9 so as to extend along the axial direction of the bore 91. The gantry rail 92 is formed such that a cross section along the short direction is curved along the circumferential direction of the bore 91, and both side portions in the short direction are short sides of the top plate 61. The lower side of both ends in the direction is supported so as to be movable along the axial direction of the bore 91.

  In this embodiment, two first gantry communication units 171 and one second gantry communication unit 172 are provided in the bore 91 of the gantry 9. Specifically, the first gantry communication unit 171 is provided in the vicinity of both side portions in the short direction of the gantry rail 92 on the inner wall of the bore 91 of the gantry 9. Further, on the upper surface side of the gantry rail 92, a second gantry communication unit 172 is provided at a substantially central position in the lateral direction of the gantry rail 92. In FIG. 4, the illustration of the first gantry communication unit 171 is omitted for the sake of illustration.

  Here, the first gantry communication unit 171 and the second gantry communication unit 172 are each disposed at a substantially central position in the axial direction of the bore 91. That is, each of the first gantry communication unit 171 and the second gantry communication unit 172 has a position along the axial direction of the bore 91 at the position of the magnetic field center (the center of the static magnetic field generated by the static magnetic field magnet 1 ( It is arranged so as to substantially coincide with the position of the one-dot chain line shown in FIG.

  Under such a configuration, at the time of imaging, the subject S is arranged on the top 61 so that the site to be imaged is aligned with the approximate center in the longitudinal direction of the spine coil 52. The body coil 51 is attached to the subject S so that the approximate center of the body coil 51 is aligned with the region to be imaged. Then, the subject S is moved into the bore 91 together with the body coil 51 and the spine coil 52 by the movement of the top plate 61.

  At this time, since the uniformity of the static magnetic field is usually highest at the center of the magnetic field, the subject S is moved so that the region to be imaged is arranged near the center of the magnetic field. As a result, the first coil communication unit 181 provided in the body coil 51 and the second coil communication unit 182 provided in the spine coil 52 are respectively disposed in the vicinity of the magnetic field center. Become. Thereby, in the axial direction of the bore 91, the first coil communication unit 181 and the second coil communication unit 182 are respectively provided with the first frame communication unit 171 and the second frame communication unit provided in the frame 9. It is arranged at a position close to 172.

  Here, since the first coil communication unit 181 is disposed on both side portions of the body coil 51 on the side close to the inner wall of the bore 91, the first coil communication unit 181 is compared with the second frame communication unit 172. It will be arranged at a position closer to the portion 171. Therefore, the first coil communication unit 181 performs close proximity wireless communication with the first gantry communication unit 171 and transmits the MR signal received by the body coil 51 to the first gantry communication unit 171. .

  On the other hand, since the second coil communication unit 182 is disposed at a substantially central position in the short direction of the spine coil 52, the second coil communication unit 172 is compared with the first frame communication unit 171. In contrast, they are arranged closer to each other. For this reason, the second coil communication unit 182 performs close proximity wireless communication with the second gantry communication unit 172 and transmits the MR signal received by the spine coil 52 to the second gantry communication unit 172. .

  In this embodiment, each of the body coil 51 and the spine coil 52 includes an amplifier that amplifies the received MR signal, and an analog-digital (Analog to Digital) that converts the MR signal amplified by the amplifier from an analog signal to a digital signal. Digital: A / D) conversion circuit. Then, the first coil communication unit 181 transmits the MR signal converted into a digital signal by the A / D conversion circuit to the first gantry communication unit 171 by proximity wireless communication. Further, the second coil communication unit 182 transmits the MR signal converted into the digital signal by the A / D conversion circuit to the second gantry communication unit 172 by the proximity wireless communication.

  Here, as a technique for performing close proximity wireless communication, for example, Transfer Jet (registered trademark), NFC (Near Field Communication), or the like is used.

  On the other hand, the first gantry communication unit 171 and the second gantry communication unit 172 provided on the gantry 9 are each connected to the receiving circuit 8 by an optical cable 19. Then, the first gantry communication unit 171 and the second gantry communication unit 172 each transmit an MR signal to the receiving circuit 8 via the optical cable 19. In this way, by transmitting the MR signal via the optical cable 19, it is possible to reduce the mixing of noise into the MR signal.

  As described above, in the first embodiment, close proximity wireless communication is performed between the gantry communication unit provided in the bore and the coil communication unit provided in the reception coil to transmit the MR signal.

  According to such a configuration, MR signals can be transmitted between the local coil 5 and the gantry 9 without using a communication cable. As a result, a communication cable connected to the local coil 5 becomes unnecessary, and the workflow can be improved. Moreover, the movable mechanism of the cable provided under the top plate 61 becomes unnecessary, and the freedom degree for ensuring patient space can be increased. Moreover, the structure of the top plate 61 and the bed 6 can be simplified, and the weight and simplification of the bed 6, improvement in reliability, cost reduction, and the like can be realized. In addition, a bed with a simple configuration such as a dockable bed or a stretcher can be used. Further, by simplifying the structures of the top board 61 and the bed 6, it is possible to add other added values such as providing the top board 61 or the bed 6 with lighting or the like. Moreover, since the bed 6 is lightened, the installation period can be shortened.

  Although the first embodiment has been described above, the above-described MRI apparatus and receiving coil can be implemented by appropriately changing some of the components according to the purpose and application. Therefore, in the following, other embodiments of the MRI apparatus and the receiving coil will be described in detail. In each of the embodiments described below, the description will be focused on differences from the above-described embodiment, and detailed description of the same contents as those of the above-described embodiment will be omitted.

(Second Embodiment)
For example, in the first embodiment described above, the example in which the coil communication unit and the gantry communication unit perform proximity communication near the magnetic field center has been described. The proximity communication may be performed at a shifted position. Hereinafter, an example of such a configuration will be described as a second embodiment.

  FIG. 5 is a perspective view illustrating a configuration example of a body coil according to the second embodiment. FIG. 6 is a front view showing configurations of a body coil, a spine coil, and a gantry according to the second embodiment. FIG. 7 is a side view showing configurations of a body coil, a spine coil, and a gantry according to the second embodiment.

  As shown in FIG. 5, in the present embodiment, the body coil 51 is provided with two first coil communication units 281. Specifically, a first coil communication unit 281 is provided on each of both side portions of the body coil 51 in the short direction. In FIG. 5, only the first coil communication unit 281 on one side portion is shown because of the arrangement.

  Here, in the present embodiment, the first coil communication unit 281 is configured to be able to change the position with respect to the body coil 51. Specifically, the first coil communication unit 281 is configured such that the position along the longitudinal direction can be changed in the side part of the body coil 51 within the entire length of the body coil 51. Thereby, the first coil communication unit 281 can be arranged at a position shifted from a substantially central position in the longitudinal direction of the body coil 51.

  Also, as shown in FIGS. 6 and 7, in the present embodiment, the spine coil 52 is provided with one second coil communication unit 282. Specifically, a second coil communication unit 282 is provided at a substantially central position in the short direction of the spine coil 52.

  Here, in this embodiment, the 2nd coil communication part 282 is comprised so that a position with respect to the spine coil 52 can be changed. Specifically, the second coil communication unit 282 is configured to be able to change the position along the longitudinal direction of the spine coil 52 within the range of the entire length of the spine coil 52. Accordingly, the second coil communication unit 282 can be disposed at a position shifted from a substantially central position in the longitudinal direction of the spine coil 52.

  As shown in FIGS. 6 and 7, in this embodiment, two first gantry communication units 271 and one second gantry communication unit 272 are provided in the bore 91 of the gantry 9. . Specifically, a first gantry communication unit 271 is provided in the vicinity of both side portions in the lateral direction of the gantry rail 92 on the inner wall of the bore 91 of the gantry 9. Further, a second pedestal communication unit 272 is provided on the upper surface side of the gantry rail 92 at a substantially central position in the lateral direction of the gantry rail 92. In FIG. 7, the first gantry communication unit 271 is not shown.

  Here, in the present embodiment, the first gantry communication unit 271 and the second gantry communication unit 272 are each configured to be able to change the position with respect to the gantry 9. Specifically, the first gantry communication unit 271 and the second gantry communication unit 272 are configured to be able to change the position along the axial direction of the bore 91 within the range of the length of the bore 91. Accordingly, the first gantry communication unit 271 and the second gantry communication unit 272 can be arranged at positions shifted from the substantially central position in the axial direction of the bore 91. That is, the first gantry communication unit 271 and the second gantry communication unit 272 can be arranged at positions shifted from the position of the magnetic field center (the position of the dashed line in FIG. 7) along the axial direction of the bore 91. It has become.

  Under such a configuration, during imaging, as in the first embodiment, the body coil 51 and the spine coil 52 are moved together with the subject S by the movement of the top plate 61, and the approximate center of each is centered on the magnetic field. Located in the vicinity. At this time, the first coil communication unit 281 provided in the body coil 51 and the second coil communication unit 282 provided in the spine coil 52 are magnetic fields along the axial direction of the bore 91, respectively. It is arranged at a position shifted from the center position. Accordingly, in the present embodiment, the first coil communication unit 281 and the first gantry communication unit 271, and the second coil communication unit 282 and the second gantry communication unit 272 are displaced from the magnetic field center. Proximity communication will be performed.

(Third embodiment)
Further, for example, in the above-described second embodiment, the example in which the positions of the coil communication unit and the gantry communication unit can be changed along the axial direction of the bore 91 has been described. However, the coil communication unit and the gantry communication unit May be provided at a plurality of positions in the axial direction of the bore 91. Hereinafter, an example of such a configuration will be described as a third embodiment.

  FIG. 8 is a perspective view illustrating a configuration example of a body coil according to the third embodiment. FIG. 9 is a front view showing configurations of a body coil, a spine coil, and a gantry according to the third embodiment. FIG. 10 is a side view showing configurations of a body coil, a spine coil, and a gantry according to the third embodiment.

  As shown in FIG. 8, in the present embodiment, the body coil 51 is provided with six first coil communication units 381. Specifically, three first coil communication units 381 are provided side by side along the longitudinal direction of the body coil 51 on each side portion of the body coil 51 in the short direction. In FIG. 8, only the first coil communication unit 381 on one side portion is shown because of the arrangement.

  Here, in the present embodiment, the first coil communication unit 381 is provided at a plurality of positions in the body coil 51. Specifically, the first coil communication unit 381 is arranged on the side portion of the body coil 51 at a substantially central position in the longitudinal direction of the body coil 51 and on both sides thereof. As a result, in the body coil 51, the first coil communication unit 381 is disposed along the longitudinal direction of the body coil 51 at a substantially central position and a position shifted from the substantially central position. become.

  Also, as shown in FIGS. 9 and 10, in the present embodiment, the spine coil 52 is provided with three second coil communication units 382. Specifically, a second coil communication unit 382 is provided along the longitudinal direction of the spine coil 52 at a substantially central position in the short direction of the spine coil 52.

  Here, in the present embodiment, the second coil communication unit 382 is provided at a plurality of positions in the spine coil 52. Specifically, the second coil communication unit 382 is disposed at a substantially central position in the longitudinal direction of the spine coil 52 and positions on both sides thereof. Thereby, in the spine coil 52, the second coil communication unit 382 is disposed at a substantially central position and a position shifted from the substantially central position along the longitudinal direction of the spine coil 52, respectively. become.

  Also, as shown in FIGS. 9 and 10, in the present embodiment, ten first gantry communication units 371 and five second gantry communication units 372 are provided in the bore 91 of the gantry 9. Yes. Specifically, five first gantry communication units 371 are arranged along the axial direction of the bore 91 in the vicinity of both side portions in the short direction of the gantry rail 92 on the inner wall of the bore 91 of the gantry 9. Is provided. In addition, on the upper surface side of the gantry rail 92, five second gantry communication units 372 are provided side by side along the axial direction of the bore 91 at a substantially central position in the short direction of the gantry rail 92. In FIG. 10, the first gantry communication unit 371 is not shown.

  Here, in the present embodiment, the first gantry communication unit 371 and the second gantry communication unit 372 are respectively provided at a plurality of positions on the gantry 9. Specifically, the first gantry communication unit 371 and the second gantry communication unit 372 are respectively disposed at a substantially central position in the axial direction of the bore 91, positions on both sides thereof, and positions on both sides thereof. ing. Thereby, in the gantry 9, along the axial direction of the bore 91, the position substantially coincident with the position of the magnetic field center (the position of the one-dot chain line shown in FIG. 10), the positions on both sides thereof, The first gantry communication unit 371 and the second gantry communication unit 372 are respectively arranged.

  According to such a configuration, at the time of imaging, along the axial direction of the bore 91, a plurality of first coil communication units 381, a plurality of second coil communication units 382, a plurality of first gantry communication units 371, In addition, a plurality of second gantry communication units 372 are arranged. Thereby, for example, even when the imaging region is changed and the top 61 is moved, the first coil communication unit 381 and the first gantry communication unit 371 that are in a close position and the first position that is in a close position. Proximity communication can be performed between the second coil communication unit 382 and the second gantry communication unit 372.

(Fourth embodiment)
For example, in the above-described embodiment, an example in which the body coil 51 and the spine coil 52 are used as an example of the local coil 5 has been described. However, a head coil for head imaging may be used. Hereinafter, an example of such a configuration will be described as a fourth embodiment.

  FIG. 11 is a perspective view illustrating a configuration example of a head coil according to the fourth embodiment. FIG. 12 is a front view showing the configuration of the head coil and the gantry according to the fourth embodiment. FIG. 13 is a side view showing the configuration of the head coil and the gantry according to the fourth embodiment.

  As shown in FIG. 11, the head coil 53 according to the present embodiment is an array coil formed in a substantially cylindrical shape with a bottom, and is used by being mounted so as to cover the head of the subject S during imaging. Specifically, the head coil 53 has a longitudinal direction (direction of arrow LD shown in FIG. 11) along the vertical direction of the head of the subject S, and a short side direction (direction of arrow SD shown in FIG. 11). The specimen S is used by being aligned along the left-right direction of the head. The head coil 53 is used by being fixed to the top plate 61 at the time of imaging.

  In the present embodiment, the head coil 53 is provided with one third coil communication unit 483. Specifically, a third coil communication unit 483 is provided at a substantially central position in the short direction of the head coil 53 below the head coil 53. In FIG. 11, for convenience of illustration, a third coil communication unit 483 is shown on the side of the head coil 53.

  Here, in the present embodiment, the third coil communication unit 483 is disposed at a substantially central position in the longitudinal direction of the head coil 53 below the head coil 53.

  As shown in FIGS. 12 and 13, in the present embodiment, as in the first embodiment, two first gantry communication units 171 and one second gantry are provided in the bore 91 of the gantry 9. A communication unit 172 is provided. Specifically, the first gantry communication unit 171 is provided in the vicinity of both side portions in the short direction of the gantry rail 92 on the inner wall of the bore 91 of the gantry 9. Further, on the upper surface side of the gantry rail 92, a second gantry communication unit 172 is provided at a substantially central position in the lateral direction of the gantry rail 92. In FIG. 13, the illustration of the first gantry communication unit 171 is omitted for the sake of illustration.

  Under such a configuration, at the time of imaging, the subject S is disposed on the top plate 61, and the head coil 53 is fixed to the top plate 61 while being mounted on the head of the subject S. Then, the subject S is moved into the bore 91 together with the head coil 53 by the movement of the top plate 61.

  At this time, as described above, since the uniformity of the static magnetic field is usually highest at the center of the magnetic field, the subject S is moved so that the head to be imaged is arranged near the center of the magnetic field. As a result, the third coil communication unit 483 provided in the head coil 53 is disposed in the vicinity of the center of the magnetic field. Accordingly, the third coil communication unit 483 is disposed at a position close to the second gantry communication unit 172 provided on the gantry 9 in the axial direction of the bore 91. Therefore, the third coil communication unit 483 performs close proximity wireless communication with the second gantry communication unit 172 and transmits the MR signal received by the head coil 53 to the second gantry communication unit 172. .

  In the present embodiment, each of the head coils 53 includes an amplifier that amplifies the received MR signal, and an A / D conversion circuit that converts the MR signal amplified by the amplifier from an analog signal to a digital signal. Yes. Then, the third coil communication unit 483 transmits the MR signal converted into the digital signal by the A / D conversion circuit to the second gantry communication unit 172 by proximity wireless communication.

  Here, as a technique for performing close proximity wireless communication, for example, Transfer Jet (registered trademark), NFC, or the like is used.

(Fifth embodiment)
Further, for example, in the above-described fourth embodiment, an example in which the coil communication unit and the gantry communication unit perform proximity communication near the center of the magnetic field has been described. The proximity communication may be performed at a position deviated from the center. Hereinafter, an example of such a configuration will be described as a fifth embodiment.

  FIG. 14 is a perspective view illustrating a configuration example of a head coil according to the fifth embodiment. FIG. 15 is a front view showing configurations of a head coil and a gantry according to the fifth embodiment. FIG. 16 is a side view showing configurations of a head coil and a gantry according to the fifth embodiment.

  As shown in FIG. 14, in the present embodiment, one third coil communication unit 583 is provided in the head coil 53. Specifically, a third coil communication unit 583 is provided at a substantially central position in the short direction of the head coil 53 below the head coil 53. In FIG. 11, for convenience of illustration, a third coil communication unit 583 is shown on the side of the head coil 53.

  Here, in the present embodiment, the third coil communication unit 583 is configured to be able to change the position with respect to the head coil 53. Specifically, the third coil communication unit 583 is configured to be able to change the position along the longitudinal direction within the entire length of the head coil 53 at the lower portion of the head coil 53. Thereby, the third coil communication unit 583 can be arranged at a position shifted from the substantially central position in the longitudinal direction of the head coil 53.

  As shown in FIGS. 15 and 16, in the present embodiment, two first gantry communication units 271 and one second gantry are provided in the bore 91 of the gantry 9 as in the second embodiment. A communication unit 272 is provided. Specifically, a first gantry communication unit 271 is provided in the vicinity of both side portions in the lateral direction of the gantry rail 92 on the inner wall of the bore 91 of the gantry 9. Further, a second pedestal communication unit 272 is provided on the upper surface side of the gantry rail 92 at a substantially central position in the lateral direction of the gantry rail 92. In FIG. 16, the first gantry communication unit 271 is not shown.

  Here, in the present embodiment, as in the second embodiment, the second gantry communication unit 272 is configured to be able to change the position with respect to the gantry 9. Specifically, the second gantry communication unit 272 is configured to be able to change the position along the axial direction of the bore 91 within the range of the length of the bore 91. Accordingly, the second gantry communication unit 272 can be disposed at a position shifted from a substantially central position in the axial direction of the bore 91. That is, the second gantry communication unit 272 can be arranged at a position shifted from the position of the magnetic field center (the position of the one-dot chain line shown in FIG. 16) along the axial direction of the bore 91.

  Under such a configuration, at the time of imaging, the head coil 53 is moved together with the subject S by the movement of the top plate 61 as in the fourth embodiment, and the approximate center of the head coil 53 is near the center of the magnetic field. Placed in. At this time, the third coil communication unit 583 provided in the head coil 53 is arranged at a position shifted from the position of the magnetic field center along the axial direction of the bore 91. Accordingly, in the present embodiment, the third coil communication unit 583 and the second gantry communication unit 272 perform proximity communication at a position that is shifted from the magnetic field center.

  Further, as shown in FIG. 16, in the present embodiment, the head coil 53 has a tilt mechanism 531 that changes the relative angle between the head coil 53 and the top plate 61, and the third coil communication. The part 583 is provided in the tilt mechanism 531. Here, the tilt mechanism 531 is provided below the head coil 53 and is fixed to the top plate 61 when the head coil 53 is used. The third coil communication unit 583 is provided below the tilt mechanism 531, and the position on the top plate 61 does not change even when the angle of the head coil 53 with respect to the top plate 61 is changed by the tilt mechanism 531. It is configured as follows.

(Sixth embodiment)
In the fifth embodiment described above, the example in which the coil communication unit and the gantry communication unit perform proximity communication at a position shifted from the center of the magnetic field has been described. You may comprise so that it may arrange | position outside the range to which RF magnetic field is applied with the coil 4 for whole body. Hereinafter, an example of such a configuration will be described as a sixth embodiment.

  FIG. 17 is a perspective view illustrating a configuration example of a head coil according to the sixth embodiment. FIG. 18 is a front view showing the configuration of the head coil and the gantry according to the sixth embodiment. FIG. 19 is a side view showing configurations of a body coil and a gantry according to the sixth embodiment.

  As shown in FIG. 17, in the present embodiment, one third coil communication unit 683 is provided in the head coil 53. A third coil communication unit 683 is provided at a substantially central position in the short direction of the head coil 53 below the head coil 53. In FIG. 17, for convenience of illustration, a third coil communication unit 683 is shown on the side of the head coil 53.

  Here, in the present embodiment, the head coil 53 extends from the end of the head coil 53, and the extending portion 532 is disposed outside the range in which the RF magnetic field is applied by the WB coil 4 at the tip. Have. The third coil communication unit 683 is provided at the distal end portion of the extending portion 532. The WB coil 4 is an example of a transmission coil.

  Specifically, as shown in FIGS. 18 and 19, the extending portion 532 of the head coil 53 is arranged along the axial direction of the bore 91 when the approximate center of the head coil 53 is arranged near the center of the magnetic field. The tip of the WB coil 4 is configured to be disposed outside the entire length in the axial direction. As a result, the third coil communication unit 683 has a full length in the axial direction of the WB coil 4 along the axial direction of the bore 91 when the approximate center of the head coil 53 is arranged near the center of the magnetic field during imaging. It comes to be arranged on the outer side.

  As shown in FIGS. 18 and 19, in this embodiment, two first gantry communication units 671 and one second gantry communication unit 672 are provided in the bore 91 of the gantry 9. . Specifically, a first gantry communication unit 671 is provided in the vicinity of both side portions in the lateral direction of the gantry rail 92 on the inner wall of the bore 91 of the gantry 9. In addition, a second gantry communication unit 672 is provided on the upper surface side of the gantry rail 92 at a substantially central position in the lateral direction of the gantry rail 92. In FIG. 19, the first gantry communication unit 671 is not shown.

  Here, in the present embodiment, the first gantry communication unit 671 and the second gantry communication unit 672 are arranged outside the range in which the RF magnetic field is applied by the WB coil 4 during imaging. Specifically, each of the first gantry communication unit 671 and the second gantry communication unit 672 has tip portions arranged outside the entire length in the axial direction of the WB coil 4 along the axial direction of the bore 91. Yes.

  With this configuration, during imaging, the head coil 53 is moved together with the subject S by the movement of the top plate 61 as in the fourth and fifth embodiments, and the approximate center of the head coil 53 is a magnetic field. Located near the center. At this time, the third coil communication unit 683 provided in the head coil 53 and the second frame communication unit 672 provided in the frame 9 are respectively arranged along the axial direction of the bore 91 with the WB coil. 4 is arranged outside the full length in the axial direction. Thus, in the present embodiment, the third coil communication unit 683 and the second gantry communication unit 672 perform close proximity communication outside the range where the RF magnetic field is applied by the WB coil 4. According to such a configuration, it is possible to avoid electromagnetic wave interference between the RF magnetic field and the proximity wireless.

(Other embodiments)
In addition, for example, in the above-described first to sixth embodiments, an example in which the second gantry communication unit is provided on the upper surface side of the gantry rail 92 has been described. The lower surface of the gantry rail 92 may be provided. In that case, for example, the gantry rail 92 is formed of a material having a low dielectric constant, and the second gantry communication unit and the second coil communication unit or the third coil communication unit include the gantry rail 92. Proximity wireless communication over.

  Further, for example, in the second and fifth embodiments described above, the coil communication unit is configured to be able to change the position with respect to the local coil 5, and in the third embodiment, the coil communication unit is used for local use. The example in the case of being provided at a plurality of positions in the coil 5 has been described. As described above, when the position of the coil communication unit can be changed, for example, the main control function 161 included in the processing circuit 16 may determine the imaging position based on the position of the coil communication unit. Good. For example, the main control function 161 displays the positioning image of the subject S on the display 11 when the imaging condition is set by the operator, and on the positioning image at a position corresponding to the position of the coil communication unit. The ROI indicating the imaging position is displayed.

  In addition, for example, in the first to sixth embodiments described above, the coil communication unit and the gantry communication unit perform close proximity wireless communication using a technology such as Transfer Jet (registered trademark) or NFC (Near Field Communication). Although the case example has been described, the coil communication unit and the gantry communication unit may perform optical wireless communication as proximity wireless communication.

  Further, for example, in the first to sixth embodiments described above, examples of the body coil, the spine coil, and the head coil have been described as examples of the local coil 5, but other types of local coils 5 are used. Even in such a case, a similar embodiment can be applied.

  The term “processor” used in the above description is, for example, a CPU (Central Processing Unit), a GPU (Graphics Processing Unit), an application-specific integrated circuit (ASIC), or a programmable logic device. For example, it means a circuit such as a simple programmable logic device (SPLD), a complex programmable logic device (CPLD), and a field programmable gate array (FPGA). Instead of storing the program in the storage circuit, the program may be directly incorporated in the processor circuit. In this case, the processor realizes the function by reading and executing the program incorporated in the circuit. In addition, each processor of the present embodiment is not limited to being configured as a single circuit for each processor, but may be configured as a single processor by combining a plurality of independent circuits to realize its function. Good. Furthermore, a plurality of components in FIG. 1 may be integrated into one processor to realize the function.

  Here, the program executed by the processor is provided by being incorporated in advance in a ROM (Read Only Memory), a storage circuit, or the like, for example. This program is a file in a format installable or executable in these devices, and is a computer such as a CD (Compact Disk) -ROM, FD (Flexible Disk), CD-R (Recordable), DVD (Digital Versatile Disk), etc. And may be provided by being recorded on a storage medium readable by the computer. The program may be provided or distributed by being stored on a computer connected to a network such as the Internet and downloaded via the network. For example, this program is composed of modules including the above-described functional units. As actual hardware, the CPU reads a program from a storage medium such as a ROM and executes it, whereby each module is loaded on the main storage device and generated on the main storage device.

  According to at least one embodiment described above, an MR signal can be transmitted between the receiving coil and the gantry without using a communication cable.

  Although several embodiments of the present invention have been described, these embodiments are presented by way of example and are not intended to limit the scope of the invention. These embodiments can be implemented in various other forms, and various omissions, replacements, and changes can be made without departing from the spirit of the invention. These embodiments and modifications thereof are included in the invention described in the claims and equivalents thereof as well as included in the scope and gist of the invention.

DESCRIPTION OF SYMBOLS 100 Magnetic Resonance Imaging (MRI) apparatus 5 Local coil 51 Body coil 52 Spine coil 53 Head coil 9 Mount 91 Bore 92 Mount rail 171,271,371,671 First mount communication part 172,272,372 , 672 Second frame communication unit 181, 281, 381 First coil communication unit 182, 282, 382 Second coil communication unit 483, 583, 683 Third coil communication unit 19 Optical cable

Claims (12)

A gantry having a bore in which the subject is placed;
A receiving coil disposed in the bore and receiving a magnetic resonance signal from the subject;
A gantry communication unit provided in the bore;
A magnetic resonance imaging apparatus, comprising: a coil communication unit that is provided in the reception coil and performs proximity wireless communication with the gantry communication unit and transmits the magnetic resonance signal to the gantry communication unit. The coil communication unit is configured to be able to change a position with respect to the receiving coil.
The magnetic resonance imaging apparatus according to claim 1. The coil communication unit is provided at a plurality of positions in the receiving coil.
The magnetic resonance imaging apparatus according to claim 1 or 2. The gantry communication unit is configured to be able to change a position with respect to the gantry.
The magnetic resonance imaging apparatus according to claim 1. The gantry communication unit is provided at a plurality of positions in the gantry.
The magnetic resonance imaging apparatus according to claim 1. A control unit that determines an imaging position based on the position of the coil communication unit;
The magnetic resonance imaging apparatus according to any one of claims 2 to 5. The gantry has a gantry rail that supports a top plate on which the subject is placed so as to be movable in the bore.
The gantry communication unit and the coil communication unit perform the proximity wireless communication through the gantry rail.
The magnetic resonance imaging apparatus according to claim 1. The receiving coil is a spine coil built in a top plate on which the subject is placed.
The magnetic resonance imaging apparatus according to claim 1. The receiving coil has an analog-digital conversion circuit that converts the magnetic resonance signal from an analog signal to a digital signal;
The coil communication unit transmits a magnetic resonance signal converted into a digital signal by the analog-digital conversion circuit to the gantry communication unit by the proximity wireless communication.
The magnetic resonance imaging apparatus according to claim 1. The coil communication unit and the gantry communication unit perform optical wireless communication as the proximity wireless communication.
The magnetic resonance imaging apparatus according to claim 1. The gantry communication unit transmits the magnetic resonance signal to a signal processing unit via an optical cable.
The magnetic resonance imaging apparatus according to claim 1. In a magnetic resonance imaging apparatus including a gantry having a bore in which a subject is disposed, a receiving coil disposed in the bore and receiving a magnetic resonance signal from the subject,
A receiving coil, comprising: a coil communication unit that performs close proximity wireless communication with a gantry communication unit provided in the bore and transmits the magnetic resonance signal to the gantry communication unit.

Images