JP7257947B2 - Magnetic resonance imaging device and bed device - Google Patents

Description

The embodiments disclosed in the specification and drawings relate to a magnetic resonance imaging apparatus and a couch apparatus.

A magnetic resonance imaging apparatus excites the nuclear spins of a subject placed in a static magnetic field with a radio frequency (RF) signal of the Larmor frequency, and emits a magnetic resonance signal (MR (Magnetic It is an imaging device that reconstructs the resonance (resonance) signal) to generate an image.

A magnetic resonance imaging apparatus receives MR signals generated by excitation by RF signals with an RF coil. The received MR signal is an analog signal. This MR signal is transmitted from the RF coil through the inside of the tabletop of the bed on which the subject is placed and the inside of the bed body that moves the tabletop in the horizontal/vertical direction, and then passes through a predetermined area in the shield room. or to an AD conversion circuit installed in a machine room or the like outside the shield room, using a signal line such as a coaxial cable.
An analog signal is transmitted from the RF coil to the AD conversion circuit, but since the transmission path is long, the MR signal is attenuated and the signal quality deteriorates.

In addition, the top plate is usually provided with coil ports at a plurality of locations so that a plurality of RF coils can be attached to the top plate. Furthermore, many of today's RF coils have a plurality of element coils inside, and a plurality of MR signals from each RF coil are input to one coil port. For this reason, the number of signal cables passing through the inside of the top plate and the inside of the main body of the bed becomes very large, and the laying work and maintenance work of the cables become complicated.

WO2009/139287

One of the problems to be solved by the embodiments disclosed in this specification and drawings is to improve the transmission quality of the MR signal output from the RF coil, reduce the number of signal cables that transmit the MR signal, An object of the present invention is to improve workability related to laying and maintenance workability of a signal cable. However, the problems to be solved by the embodiments disclosed in this specification and drawings are not limited to the above problems. A problem corresponding to each effect of each configuration shown in each embodiment to be described later can also be positioned as another problem.

A magnetic resonance imaging apparatus according to one embodiment includes a magnet pedestal, a bed top, a transducer, and an apparatus main body. The magnet mount includes at least a static magnetic field magnet that generates a static magnetic field, a gradient magnetic field coil that generates a gradient magnetic field, and a transmission coil that applies a high frequency to the subject. The bed top plate is provided with a plurality of coil ports, which are connected to RF coils each having a plurality of element coils and outputting a plurality of channels of magnetic resonance signals received by the plurality of element coils. A transducer is provided on the bed top and connected to the plurality of coil ports. The converter also includes a selector for selectively reducing the number of signals output from the plurality of coil ports. The device body generates a magnetic resonance image based on the magnetic resonance signals output from the transducer.

1 is a configuration diagram showing an example of the overall configuration of a magnetic resonance imaging apparatus according to an embodiment; FIG. FIG. 2 is a diagram schematically showing a conventional MR signal transmission system; FIG. 2 is a diagram illustrating a bed of the magnetic resonance imaging apparatus according to the first embodiment; FIG. FIG. 2 is a block diagram showing the MR signal transmission system in the first embodiment; The figure which illustrates the bed of the magnetic resonance imaging apparatus of the modification of 1st Embodiment. FIG. 4 is a block diagram showing a transmission system of MR signals in the second embodiment; The figure which illustrates the bed of the magnetic resonance imaging apparatus of 2nd Embodiment. The figure which illustrates the bed of the magnetic resonance imaging apparatus of the 1st modification of 2nd Embodiment. FIG. 11 is a block diagram showing the MR signal transmission system in the second modification of the second embodiment; The figure which illustrates the bed of the magnetic resonance imaging apparatus of 3rd Embodiment. FIG. 11 is a block diagram showing a transmission system for MR signals in the third embodiment; The figure which illustrates the bed of the magnetic resonance imaging apparatus of the modification of 3rd Embodiment.

An embodiment of the present invention will be described below with reference to the accompanying drawings.

(First embodiment)
FIG. 1 is a block diagram showing the overall configuration of a magnetic resonance imaging apparatus 1 according to the first embodiment. The magnetic resonance imaging apparatus 1 of the embodiment is configured including a magnet pedestal 100, a control cabinet 300, a console 400, a bed 500, and the like.

The magnet pedestal 100 and bed 500 are usually placed in a shield room. On the other hand, the control cabinet 300 is arranged, for example, in a room called a machine room, and the console 400 is arranged in an operation room. The control cabinet 300 and the console 400 are collectively referred to as an apparatus main body 600. FIG.

The magnet mount 100 has a static magnetic field magnet 10, a gradient magnetic field coil 11, a WB (Whole Body) coil 12, etc., and these components are housed in a cylindrical housing. The bed 500 has a bed body 50 and a bed top plate 51 . The magnetic resonance imaging apparatus 1 also has an RF coil 20 arranged close to the subject. In the following description, the RF coil 20 is one component of the magnetic resonance imaging apparatus 1 , but the RF coil 20 may not be included in the configuration of the magnetic resonance imaging apparatus 1 . In this case, although the RF coil 20 is not included in the configuration of the magnetic resonance imaging apparatus 1, the RF coil 20 and the magnetic resonance imaging apparatus 1 are configured to be connectable to each other. More specifically, as will be described later, the RF coil 20 and the bed top plate 51 of the magnetic resonance imaging apparatus 1 are configured to be connectable to each other.

The control cabinet 300 includes a gradient magnetic field power supply 31 (31x for X axis, 31y for Y axis, 31z for Z axis), RF receiver 32, RF transmitter 33, and sequence controller .

The static magnetic field magnet 10 of the magnet pedestal 100 has a substantially cylindrical shape, and generates a static magnetic field in a bore (a space inside the cylinder of the static magnetic field magnet 10), which is an imaging region of a subject (for example, a patient). The static magnetic field magnet 10 incorporates a superconducting coil, and the superconducting coil is cooled to an extremely low temperature by liquid helium. The static magnetic field magnet 10 generates a static magnetic field by applying a current supplied from a static magnetic field power supply (not shown) to the superconducting coil in the excitation mode, and then, when shifting to the persistent current mode, the static magnetic field power supply is separated. Once transferred to the persistent current mode, the static magnetic field magnet 10 continues to generate a large static magnetic field for a long time, for example, over one year. Note that the static magnetic field magnet 10 may be configured as a permanent magnet.

The gradient magnetic field coil 11 also has a substantially cylindrical shape and is fixed inside the static magnetic field magnet 10 . The gradient magnetic field coil 11 applies a gradient magnetic field to the subject in the directions of the X-axis, Y-axis, and Z-axis by means of currents supplied from gradient magnetic field power sources (31x, 31y, 31z).

The bed main body 50 of the bed 500 can move the bed top plate 51 vertically and horizontally, and moves the subject placed on the bed top plate 51 to a predetermined height before imaging. After that, during imaging, the patient is moved into the bore by moving the bed top plate 51 in the horizontal direction. As will be described later, the bed top plate 51 is provided with a plurality of coil ports 220 for connecting the RF coils 20 .

The WB coil 12 is fixed in a substantially cylindrical shape inside the gradient magnetic field coil 11 so as to surround the subject. The WB coil 12 transmits an RF pulse transmitted from the RF transmitter 33 toward the subject, and receives magnetic resonance signals (that is, MR signals) emitted from the subject by excitation of hydrogen nuclei.

The RF transmitter 33 transmits RF pulses to the WB coil 12 based on instructions from the sequence controller 34 . On the other hand, the RF receiver 32 detects the MR signals received by the WB coil 12 and sends raw data obtained by digitizing the detected MR signals to the sequence controller 34 .

The RF coil 20 receives MR signals emitted from the subject at a position close to the subject. The RF coil 20 includes, for example, multiple element coils. There are various types of RF coils 20, such as for the head, for the chest, for the spine, for the legs, or for the whole body, depending on the imaging region of the subject. A plurality of RF coils 20 can be placed on the subject at the same time. FIG. 1 illustrates a state in which RF coils 20 for the chest and legs are placed. Each RF coil 20 is provided with a coil connector 210 via a cable. When using the RF coil 20 , the coil connector 210 is connected to the coil port 220 of the bed top plate 51 .

The sequence controller 34 scans the subject by driving the gradient magnetic field power supply 31 , the RF transmitter 33 and the RF receiver 32 under the control of the console 400 . Then, when the sequence controller 34 scans and receives raw data from the RF receiver 32 , it sends the raw data to the console 400 .

The sequence controller 34 has a processing circuit (not shown). This processing circuit is composed of, for example, a processor that executes a predetermined program, and hardware such as FPGA (Field Programmable Gate Array) and ASIC (Application Specific Integrated Circuit).
Console 400 is configured as a computer having processing circuitry 40 , memory circuitry 41 , display 42 and input device 43 .

The storage circuit 41 is a storage medium including a ROM (Read Only Memory), a RAM (Random Access Memory), and an external storage device such as a HDD (Hard Disk Drive) and an optical disk device. The storage circuit 41 stores various kinds of information and data, as well as various programs executed by the processor included in the processing circuit 40 .

The display 42 is a display device such as a liquid crystal display panel, plasma display panel, or organic EL panel. The input device 43 is, for example, a mouse, keyboard, trackball, touch panel, etc., and includes various devices for the operator to input various information and data.

The processing circuit 40 is, for example, a circuit including a CPU or a dedicated or general-purpose processor. The processor implements various functions described later by executing various programs stored in the storage circuit 41 . The processing circuit 40 may be configured by hardware such as FPGA (field programmable gate array) or ASIC (application specific integrated circuit). These hardware can also realize various functions described later. Also, the processing circuit 40 can realize various functions by combining software processing by a processor and a program and hardware processing.

The console 400 controls the entire magnetic resonance imaging apparatus 1 by these components. The processing circuit 40 causes the sequence controller 34 to perform scanning based on the input imaging conditions, while reconstructing an image based on raw data input from the sequence controller 34, that is, digitized MR signals. The reconstructed image is displayed on display 42 or stored in memory circuit 41 .

FIG. 2 is a diagram schematically showing a conventional MR signal transmission system. FIG. 2(a) is a front view of the magnet pedestal 100 of the magnetic resonance imaging apparatus, and a bed 500 is arranged on the front side of FIG. 2(a). FIG. 2(b) is a side view of the magnet pedestal 100 and the bed 500. FIG. A coil connector 210 of the RF coil 20 is connected to a coil port 220 of the bed top plate 51 . In a conventional transmission system, the MR signal, which is an analog signal received by the RF coil 20, is normally transmitted via a coaxial cable from the coil port 220 of the bed 500 into the housing of the magnet gantry 100, for example, as illustrated in FIG. is transmitted to a repeater located in a part of the A repeater may be installed in a machine room away from the magnet mount 100 . An AD converter is built in the repeater.

As described above, in the conventional transmission system, the analog signal is transmitted through a long transmission line from the RF coil 20 to the repeater, so that the MR signal is attenuated and the signal quality is degraded. could have happened.

Also, usually, the bed top plate 51 is provided with coil ports 220 at a plurality of locations so that a plurality of RF coils 20 can be attached to the bed top plate 51 . Furthermore, many of today's RF coils 20 have a plurality of element coils inside, and a plurality of MR signals from each element coil are input to one coil port. For this reason, the number of signal cables passing through the interior of the bed top plate and the interior of the bed body is extremely large, and cable laying work and maintenance work are complicated.

Now, assuming that the path of the MR signal output from one element coil is called a "channel", one RF coil outputs MR signals of up to the same number of channels as the number of built-in element coils. be. As a result, assuming that the number of coil ports 220 of the bed top plate 51 is N and the number of channels of the RF coil 20 connected to each coil port 220 is M, the flow from the bed top plate 51 through the inside of the bed main body 50 is The total number of channels transmitted to the repeater is N×M.

For example, if the number of coil ports is 8 and the number of RF coil channels is 16, the total number of channels is 128 (8×16), and the number of coaxial cables for transmitting all MR signals is 128. In other words, 128 coaxial cables must be laid inside the top plate and inside the main body of the bed. Furthermore, since the bed top plate 51 and the bed body 50 move horizontally and vertically, it is necessary to lay a large number of coaxial cables to withstand these movements. For example, a method of bundling a plurality of coaxial cables and laying the cable bundle along a flexible support member such as a caterpillar structure is used. As a result, the work related to laying cables has become very complicated.

Each embodiment described below aims at improving such inconveniences. 3 and 4 are diagrams illustrating the bed 500, the MR signal transmission system, etc. of the magnetic resonance imaging apparatus 1 according to the first embodiment. FIG. 3(a) is a top view of the bed top plate 51 and the bed body 50, and FIG. 3(b) is a side view.

As shown in FIG. 3A, the bed top plate 51 is provided with a plurality of coil ports 220 for connecting the RF coils 20 . In the example shown in FIG. 3A, eight coil ports 220 are provided and eight RF coils 20 can be connected simultaneously.

On the other hand, each coil port 220 is provided with an AD converter group 230 as shown in FIG. 3(b). The AD converter group 230 converts the MR signal output from each RF coil 20 from an analog signal to a digital signal. The MR signal converted into a digital signal is transmitted to a converter 200 provided at one end of the bed top plate 51 .

FIG. 4 is a block diagram showing the MR signal transmission system in the first embodiment. As shown in FIG. 4, each RF coil 20 incorporates multiple element coils 21 . The number of built-in element coils 21 is not particularly limited, but, for example, 16 element coils 21 are arranged in a planar array in each RF coil 20 as illustrated in FIG. Since each RF coil 20 outputs MR signals of channels corresponding to the number of element coils 21, MR signals of 16 channels are output from the RF coils 20 in this example. Therefore, the AD converter group 230 provided for each coil port 220 is provided with 16 AD converters corresponding to each channel.

Signals from each coil port 220 are collected in a converter 200 provided at the end of the bed top plate 51 . The converter 200 has a selector 240, a parallel-to-serial converter (P/S converter) 250, and an electro-optical converter (EO converter) 270, as illustrated in FIG.

Selector 240 selectively reduces the number of signals output from each coil port. For example, from among all channels input to the selector 240, a signal of a channel designated by a selection signal sent from the apparatus body 600 is selected. RF coils 20 are not necessarily connected to all coil ports 220 . When the RF coil 20 is connected, each coil port 220 transmits a connection detection signal indicating the fact to the device main body 600 . Further, each RF coil 20 outputs an identification signal indicating the type of the coil. This identification signal is also transmitted to the device body 600 . The above connection detection signal and identification information can be transmitted to the device main body 600 using part of the channel shown in FIG. Alternatively, the connection detection signal and the identification information may be transmitted to the device body 600 using a route independent of the channels shown in FIG.

Device main body 600 determines a channel to be selected by selector 240 based on these connection detection signals and coil identification information. The transducer 200 receives signals of all channels, that is, signals of the number of channels obtained by multiplying the number of RF coils 20 by the number of element coils 21, for example, signals of 128 channels.

Based on the connection detection signal, device main body 600 sends a selection signal to selector 240 so as to select only the signal of the channel from coil port 220 to which RF coil 20 is actually connected. As a result, the selector 240 can reduce the number of channels by eliminating transmission of signals in channels to which the RF coils 20 are not connected, that is, unnecessary channels.

Further, the device main body 600 selects the necessary coils for imaging from among the plurality of RF coils 20 connected to the coil port 220 based on the identification information of the RF coils 20 and the imaging conditions of the subject to be imaged. The RF coil 20 can be selected, and the element coil 21 necessary for imaging can be selected from among the plurality of element coils 21 built into the selected RF coil 20 . Such selection allows selector 240 to further reduce the number of channels.

The MR signals of the number of channels reduced by the selector 240 may be converted from parallel signals to serial signals by the P/S converter 250 . As a result, not only the number of logical channels, but also the number of physical channels, that is, the number of transmission cables can be reduced to, for example, one. Also, the electrical signal converted into a serial signal may be further converted into an optical signal by the EO converter 270 .

As shown in FIG. 3B, the signal output from the converter 200 is guided from the bed top plate 51 into the bed main body 50 and transmitted to the device main body 600 . As described above, the output of converter 200 is reduced in number of channels, and furthermore physical transmission cables are reduced to, for example, one.

As described above, according to the magnetic resonance imaging apparatus 1 of the first embodiment, the signal cables passing through the interior of the bed top plate 51 and the interior of the bed main body 50 are greatly simplified as compared with the conventional art. As a result, the work for laying the signal cable and the maintenance work for replacing the signal cable can be greatly reduced.

Further, in the first embodiment, the transmission path of the analog signal output from the RF coil 20 has a short path length from the output end of the element coil 21 to the position of the coil port 220 of the bed top plate 51. Attenuation of the MR signal due to propagation is also greatly suppressed compared to .

(Modification of the first embodiment)
FIG. 5(a) is a top view of a bed top plate 51 and a bed main body 50 according to a modification of the first embodiment, and FIG. 5(b) is a side view. In the first embodiment described above, the converter 200 is arranged at one end of the bed top plate 51 as shown in FIG. On the other hand, in a modification of the first embodiment, as illustrated in FIG. ing.

The configuration of the converter 200 in the modified example of the first embodiment is the same as that of the first embodiment shown in FIG. You can get the same effect.

(Second embodiment)
FIG. 6 is a block diagram showing an MR signal transmission system according to the second embodiment. The difference between the second embodiment and the first embodiment is the position of the AD converter. In the first embodiment, the AD converter group 230 is provided in each coil port 220 as shown in FIG. One AD converter group 230 is provided with AD converters corresponding in number to the element coils 21 of the RF coil 20 . Therefore, the number of AD converters provided in all coil ports 220 is the product of the total number of RF coil 20 channels and the number of all coil ports 220. For example, in the above example, 120 AD converters corresponding to 120 total channels. AD converter must be provided.

On the other hand, in the second embodiment, the AD converter 260 is provided after the selector 240 in the converter 200, as shown in FIG. With this configuration, the number of AD converters 260 can be made smaller than in the first embodiment.

It is sufficient that the number of AD converters 260 in the second embodiment matches the maximum number of output channels of the selector 240 . If the maximum number of output channels is 32, the number of AD converters 260 is 32.

FIG. 7(a) is a top view of the bed top plate 51 and the bed main body 50 of the second embodiment, and FIG. 7(b) is a side view. The number and positions of the coil ports 220 on the bed top plate 51 are the same as in the first embodiment, and the positions of the converters 200 are also the same as in the first embodiment. Also, the type of signal cable from the converter 200 to the device main body 600 and the layout of the signal cable are substantially the same as in the first embodiment. However, as described above, the AD converter is provided in the coil port 220 in the first embodiment, whereas the AD converter is provided inside the converter 200 in the second embodiment. There is a difference between the two.

Here, the transducer 200 is installed at the longitudinal end of the bed top plate 51 and farther from the magnet mount 100 (that is, the right end of the bed top plate 51 in FIG. 7). Note that The end portion where the transducer 200 is installed is positioned outside the imaging space (that is, the bore) of the magnet mount 100 even during imaging of the subject. Similarly, the transducer 200 will also be located remotely from the RF coil 20 that rests on the subject. Therefore, the possibility that digital noise that may be generated from the AD converter 260 built in the converter 200 and its surroundings leaks into the imaging space or is induced in the RF coil 20 is eliminated as much as possible. can do.

(First modification of the second embodiment)
FIG. 8(a) is a top view of a bed top plate 51 and a bed main body 50 according to a modification of the second embodiment, and FIG. 8(b) is a side view. In the modification of the second embodiment, similar to the modification of the first embodiment (see FIG. 5), the transducer 200 is integrated with one coil port 220 of the plurality of coil ports 220. provided in the form However, in the modification of the second embodiment, the AD converter 260 is built in the converter 200 .

The configuration of the converter 200 in the modified example of the second embodiment is the same as that of the second embodiment shown in FIG. You can get the same effect.

(Second modification of the second embodiment)
FIG. 9 is a block diagram showing an MR signal transmission system according to a second modification of the second embodiment. A difference between the second embodiment and the modification of the second embodiment is that the modification of the second embodiment incorporates a coil detection circuit 242 .

As described above, each coil port 220 transmits a connection detection signal indicating that the RF coil 20 is connected to the apparatus body 600 . If this connection detection signal is included in the signal transmitted from each coil port 220 to the converter 200 , the coil detection circuit 242 can extract the connection detection signal from the input signal of the selector 240 . Then, the coil detection circuit 242 can cause the selector 240 to select only the channel signal from the coil port 220 to which the RF coil 20 is actually connected. In an embodiment in which a selection signal for the selector 240 is supplied from the device main body 600 , such a coil detection circuit 242 or a function equivalent to this circuit may be provided in the device main body 600 .

(Third embodiment)
FIG. 10(a) is a top view of a bed top plate 51 and a bed body 50 according to the third embodiment, and FIG. 10(b) is a side view. FIG. 11 is a block diagram showing the MR signal transmission system according to the third embodiment.

In the third embodiment, signal transmission from the converter 200 to the apparatus body 600 is performed wirelessly. Therefore, as shown in FIGS. 10A and 10B, the converter 200 is provided with an antenna 290 for transmission and reception. Further, the device main body 600 is also provided with an antenna 610 for wirelessly transmitting and receiving signals to and from the converter 200 .

The transmission system of the third embodiment is similar to the transmission system of the second embodiment, but as shown in FIG. Instead, it has a transmission/reception circuit 280 .

In the third embodiment, signal transmission/reception between the converter 200 and the device main body 600 is performed wirelessly, so a signal cable from the converter 200 to the device main body 600 becomes unnecessary.

(Modification of the third embodiment)
FIG. 12(a) is a top view of a bed top plate 51 and a bed body 50 according to a modification of the third embodiment, and FIG. 12(b) is a side view. A modification of the third embodiment has a configuration in which the bed top plate 51 has conductive rails 202 . The conductive rails 202 are arranged, for example, on the sides of the bed top plate 51 along the longitudinal direction. The bed body 50 has a power source 206 and conductive contacts 204 that slidably contact the conductive rails 202 .

With this configuration, regardless of the position of the bed top 51 in the horizontal direction, or even when the bed top 51 is moving in the horizontal direction, the power source 206 provided in the bed body 50 can Power can always be supplied to the converter 200 installed on the bed top plate 51 .

In the third embodiment, signal transmission/reception between the converter 200 and the device main body 600 is performed wirelessly. Since it has active elements such as the device 260, an external power supply is required. Therefore, in the modification of the third embodiment, the power supply system via the conductive rails 202 and the conductive contacts 204 as described above stably supplies power to the converter 200 with a simple configuration. It becomes possible to

According to at least one embodiment described above, the transmission quality of the MR signal output from the RF coil 20 is improved, the number of signal cables for transmitting the MR signal is reduced, workability related to laying the signal cable, and It is possible to improve the maintenance workability of the signal cable.

While several embodiments have been described, these embodiments are provided 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, changes, and combinations of embodiments can be made without departing from the scope of the invention. These embodiments and their modifications are included in the scope and spirit of the invention, as well as the scope of the invention described in the claims and equivalents thereof.

1 Magnetic Resonance Imaging Apparatus 12 WB Coil 20 RF Coil 21 Element Coil 50 Bed Body 51 Bed Top Plate 200 Converter 210 Coil Connector 220 Coil Port 230 AD Converter Group 240 Selector 242 Coil Detection Circuit 250 P/S Converter 260 AD Conversion device 270 EO converter 280 transmission/reception circuit 290 converter antenna 600 device body 602 device body antenna

Claims (14)

a magnet pedestal comprising at least a static magnetic field magnet that generates a static magnetic field, a gradient magnetic field coil that generates a gradient magnetic field, and a transmission coil that applies a high frequency to a subject;
a bed top plate having a plurality of element coils and provided with a plurality of coil ports connected to RF coils for outputting magnetic resonance signals of a plurality of channels respectively received by the plurality of element coils;
a converter provided on the bed top plate and connected to the plurality of coil ports;
a device main body that generates a magnetic resonance image based on the magnetic resonance signals output from the transducer;
with
the converter selectively reduces the number of signals output from the plurality of coil ports;
comprising a
Magnetic resonance imaging equipment. The selector selects the magnetic resonance signals so as to reduce the total number of channels defined by the product of the number of output channels of the RF coil and the number of the coil ports provided on the bed top. ,
The magnetic resonance imaging apparatus according to claim 1. The coil port is provided with an AD converter that converts the magnetic resonance signal output from each of the element coils into a digital signal,
3. The magnetic resonance imaging apparatus according to claim 1 or 2. The converter is provided with an AD converter that converts the magnetic resonance signal selected by the selector into a digital signal.
3. The magnetic resonance imaging apparatus according to claim 1 or 2. The selector selects the magnetic resonance signal from a coil port to which the RF coil is connected, from among the plurality of coil ports.
5. The magnetic resonance imaging apparatus according to claim 1. A detection circuit that detects which of the plurality of coil ports the RF coil is connected to,
the selector selects the magnetic resonance signal based on the output signal of the detection circuit;
6. A magnetic resonance imaging apparatus according to claim 5. wherein the detection circuit is provided in the converter;
7. A magnetic resonance imaging apparatus according to claim 6. The detection circuit is provided in the device body,
7. A magnetic resonance imaging apparatus according to claim 6. The transducer is disposed at the longitudinal end of the bed top plate and farther from the magnet pedestal.
9. The magnetic resonance imaging apparatus according to claim 1. the transducer is integrated with at least one of the plurality of coil ports;
9. The magnetic resonance imaging apparatus according to claim 1. The transducer transmits the magnetic resonance signal converted into a digital signal to the device main body as an optical signal.
A magnetic resonance imaging apparatus according to any one of claims 1 to 10. The transducer wirelessly transmits the magnetic resonance signal converted into a digital signal to the device main body.
A magnetic resonance imaging apparatus according to any one of claims 1 to 10. The bed top comprises conductive rails,
the transducer is powered via the conductive rail;
A magnetic resonance imaging apparatus according to any one of claims 1 to 12. a bed top plate having a plurality of element coils and provided with a plurality of coil ports connected to RF coils for outputting magnetic resonance signals of a plurality of channels respectively received by the plurality of element coils;
A transducer provided at a specific position on the top plate of the bed, the transducer comprising a selector for selecting the magnetic resonance signals so as to reduce the number of channels of the magnetic resonance signals output from the plurality of coil ports. and,
A sleeper apparatus comprising:

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