JP2008000484A - Magnetic resonance imaging apparatus - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To raise S/N so as to raise image quality by cooling an RF coil and an amplifier to be connected to the RF coil in a magnetic resonance imaging apparatus. <P>SOLUTION: A coolant cooled by a cooling part 34 passes a transfer hose 35 and is transferred to an RF coil part 14 and an amplifier storage part 28a, so as to cool the RF coil 14b and the amplifier 28b respectively stored inside. <P>COPYRIGHT: (C)2008,JPO&INPIT

Description

  The present invention relates to a magnetic resonance imaging apparatus.

  2. Description of the Related Art A magnetic resonance imaging (MRI) apparatus is known as an apparatus that can take a tomographic image of a subject by using a nuclear magnetic resonance (NMR) phenomenon. Magnetic resonance imaging apparatuses are used in various fields such as medical applications and industrial applications.

  When taking a tomographic image of a subject using a magnetic resonance imaging apparatus, first, the subject is transported into a static magnetic field space in which a static magnetic field is formed, and the direction of spin of protons in the subject Are aligned in the direction of the static magnetic field to obtain a magnetization vector. Thereafter, by irradiating an electromagnetic wave having a resonance frequency, a nuclear magnetic resonance phenomenon is generated to change the magnetization vector of the proton. Then, the magnetic resonance imaging apparatus receives a magnetic resonance signal from a proton that returns to the original magnetization vector, and generates a tomographic image of the subject based on the received magnetic resonance signal.

In such a magnetic resonance imaging apparatus, a magnetic field is generated by applying a large current to the RF coil, and an image of the subject is taken. Further, in order to meet the need for shortening the photographing time, an image can be obtained in a short time by applying a large current to the RF coil (for example, Patent Document 1).
JP 2003-290169 A

  However, application of a large current also increases Joule heat generated in the RF coil, and a stable magnetic field cannot be obtained due to heat generation of the coil, resulting in a decrease in the S / N ratio. Therefore, it is necessary to suppress the heat generation of the coil.

  Accordingly, an object of the present invention is to provide a magnetic resonance imaging apparatus capable of improving the S / N ratio and improving the image quality even when a large current is applied to the RF coil.

  In order to achieve the above object, the magnetic resonance imaging apparatus of the present invention irradiates an object in a static magnetic field space with an RF pulse, and thereby an image of the object based on a magnetic resonance signal generated in the object. An RF coil that receives the magnetic resonance signal, and a cooling unit that supplies a coolant that cools the RF coil.

  According to the present invention, it is possible to provide a magnetic resonance imaging apparatus capable of improving the S / N ratio and improving the image quality even when a large current is applied to the RF coil.

  Embodiments according to the present invention will be described below with reference to the drawings.

<First Embodiment>
FIG. 1 is a configuration diagram showing a configuration of an embodiment of a magnetic resonance imaging apparatus according to the present invention.
FIG. 2 is a diagram showing a relationship among the RF coil unit 14, the cradle 26, and the cooling unit 34 in the first embodiment of the magnetic resonance imaging apparatus according to the present invention. 2A is a plan view, and FIG. 2B is a side view. In addition, the part shown with a broken line shows that it exists in the inside of an apparatus.

  As shown in FIGS. 1 and 2, the magnetic resonance imaging apparatus 1 includes a static magnetic field magnet unit 12, a gradient coil unit 13, an RF coil unit 14, an RF drive unit 22, a gradient drive unit 23, and data collection. The unit 24, the subject transport unit 25, the control unit 30, the data processing unit 31, the operation unit 32, the display unit 33, and the cooling unit 34 are included.

  Hereinafter, each component will be sequentially described.

  The static magnetic field magnet unit 12 is provided to form a static magnetic field in the static magnetic field space 11 in which the subject is accommodated. The static magnetic field magnet unit 12 is an open type. For example, a pair of permanent magnets are arranged so as to sandwich the static magnetic field space 11, and the direction of the static magnetic field is in a direction Z perpendicular to the body axis direction of the subject 40. It is configured to be along. Although not shown in FIG. 1, the static magnetic field magnet unit 12 includes an upper yoke, a lower yoke, and a side yoke, and ends of the upper yoke and the lower yoke are supported by the side yoke. A pair of permanent magnets is disposed on each of the upper yoke and the lower yoke.

  The gradient coil unit 13 forms a gradient magnetic field in the static magnetic field space 11 so that the magnetic resonance signal received by the RF coil unit 14 has three-dimensional position information. The gradient coil unit 13 has three systems of gradient coils to form three types of gradient magnetic fields: a slice selection gradient magnetic field, a read gradient magnetic field, and a phase encoding gradient magnetic field.

  The RF coil unit 14 is disposed so as to surround the entire head, which is an imaging region of the subject 40, for example. The RF coil unit 14 transmits an RF signal, which is an electromagnetic wave, to the subject in the static magnetic field space 11 to form a high-frequency magnetic field, and excites proton spins in the imaging region of the subject 40. The RF coil unit 14 receives an electromagnetic wave generated from the excited proton as a magnetic resonance signal.

  Here, FIG. 3 is a view showing the RF coil unit 14 installed on the mounting surface of the cradle 26. 3, FIG. 3 (a) is a cross-sectional view, and FIG. 3 (b) is a side view.

  As shown in FIG. 3, the RF coil unit 14 includes an accommodation unit 14a, an RF coil 14b, a support unit 14c, a first coupling unit 14d, a supply port 14e, a second coupling unit 14f, And an outlet 14g.

The accommodating part 14a accommodates the RF coil 14b in the space.
The RF coil 14 b receives an electromagnetic wave generated from the subject as a magnetic resonance signal by the electromagnetic wave irradiated to the subject in the static magnetic field space 11.
The support portion 14c stably supports the housing portion 14a that houses the RF coil 14b. The support portion 14c has a first coupling portion 14d and a second coupling portion 14f.

The first coupling portion 14d includes a supply port 14e and is coupled to a first coupled portion 29a formed on a cradle 26 described later. For example, the first coupling portion 14d is a plug, the first coupled portion 29a is a socket, and the first coupling portion 14d is fitted to the first coupled portion 29a.
The supply port 14e is formed in the first coupling portion 14d. The supply port 14e supplies the refrigerant cooled by the cooling unit 34 described later to the support unit 14c.

The second coupling portion 14f includes a discharge port 14g and is coupled to a second coupled portion 29c formed in the cradle 26 described later. For example, the second coupling portion 14f is a plug, the second coupled portion 29c is a socket, and the second coupling portion 14f is fitted to the first coupled portion 29c.
The discharge port 14g is formed in the second coupling portion 14f. The discharge port 14g discharges the refrigerant (medium) that has cooled the RF coil 14b in the accommodating portion 14a to a receiving port 29d described later.

  The RF coil unit 14 is configured such that the first coupling unit 14d and the first coupled unit 29a are coupled, and the second coupling unit 14f and the second coupled unit 29c are coupled to each other. It becomes detachable.

  Although not shown in FIG. 3, the supply port 14e is provided with a check valve in order to prevent the medium in the support portion 14c from flowing back to a later-described delivery hose 35a. The discharge port 14g is provided with a check valve in order to prevent the medium discharged to the receiving hose 35b described later from flowing back to the support portion 14c.

  The RF drive unit 22 drives the RF coil unit 14 to form a high-frequency magnetic field in the static magnetic field space 11, and a gate modulator (not shown), an RF power amplifier (not shown), and an RF oscillator (not shown). And have. Based on an instruction from the control unit 30, the RF drive unit 22 modulates an RF signal from the RF oscillator into a signal having a predetermined timing and a predetermined envelope using a gate modulator. The RF signal modulated by the gate modulator is amplified by the RF power amplifier and then output to the RF coil unit 14.

  The gradient driving unit 23 drives the gradient coil unit 13 based on an instruction from the control unit 30 to generate a gradient magnetic field in the static magnetic field space 11. The gradient driving unit 23 includes three systems of driving circuits (not shown) corresponding to the three systems of gradient coils of the gradient coil unit 13.

  The data collection unit 24 includes a phase detector (not shown) and an analog / digital converter (not shown) in order to collect magnetic resonance signals received by the RF coil unit 14. The data collection unit 24 detects the phase of the magnetic resonance signal from the RF coil unit 14 using a phase detector using the output of the RF oscillator of the RF drive unit 22 as a reference signal, and outputs the detected signal to the analog / digital converter. The magnetic resonance signal, which is an analog signal phase-detected by the phase detector, is converted to a digital signal by the analog / digital converter and output to the data processing unit 31.

  The subject transport unit 25 includes a cradle 26 and a cradle moving unit 27.

The cradle 26 is a table that supports the subject 40 on the placement surface.
As shown in FIG. 2, the cradle 26 includes a coupled portion 29 and a transfer hose 35.

  The cradle moving unit 27 moves the cradle 26 between the inside and outside of the static magnetic field space 11.

The coupled portion 29 includes a first coupled portion 29a and a second coupled portion 29c.
The first coupled portion 29a forms a delivery port 29b. The first coupled portion 29a is coupled to the first coupling portion 14d.

  The second coupled portion 29c forms a receiving port 29d. The second coupled portion 29c is coupled to the second coupling portion 14f.

  As shown in FIG. 2, the delivery port 29 b and the reception port 29 d are formed at arbitrary positions on the surface of the cradle 26 as a medium for the refrigerant flowing between the RF coil unit 14 and the cooling unit 34. Here, the refrigerant is preferably a gas from the viewpoint of handling. A liquid may be used.

The transfer hose 35 includes a sending hose 35a and a receiving hose 35b. The transfer hose 35 is a hose for transferring the refrigerant between the RF coil unit 14 and the cooling unit 34.
The delivery hose 35a supplies the refrigerant from the cooling unit 34 to the delivery port 29b. The receiving hose 35b discharges the refrigerant from the receiving port 29d to the cooling unit 34.

  The control unit 30 is configured by a computer. The control unit 30 controls each unit of the RF drive unit 22, the gradient drive unit 23, the data collection unit 24, and the cradle moving unit 27 based on a command sent from the operation unit 32 via the data processing unit 31. In addition, the control unit 30 controls the data processing unit 31 based on a command from the operation unit 32 in order to obtain a desired image.

  The data processing unit 31 is configured by a computer. The data processing unit 31 is connected to the control unit 30, processes an operation signal input to the operation unit 32, and transmits the operation signal to the control unit 30. The data processing unit 31 is connected to the data collecting unit 24 and performs various image processing on the magnetic resonance signal output from the data collecting unit 24 to generate image data.

  The operation unit 32 includes an operation device such as a keyboard and a mouse, and outputs an operation signal corresponding to the operation of the operator to the data processing unit 31.

  The display unit 33 includes a display device such as a graphic display, and displays a tomographic image of the subject generated by the data processing unit 31.

  The cooling unit 34 supplies a refrigerant for cooling the RF coil 14b and an amplifier 28b described later.

  Here, FIG. 4 is a plan sectional view showing the configuration of the cooling section 34 in the embodiment according to the present invention.

  As shown in FIG. 4, the cooling unit 34 includes a casing 34a, an evaporator 34b, a compressor 34c, a propeller fan 34d, a condenser 34e, and a cross fan 34f.

The housing 34 a is a container that houses equipment that constitutes the cooling unit 34.
The evaporator 34b evaporates liquid chlorofluorocarbon inside, and cools the medium by taking away the surrounding heat by latent heat of vaporization.
The compressor 34c compresses the chlorofluorocarbon gas evaporated in the evaporator 34b.
The propeller fan 34d supplies air from the outside of the housing 34a in order to cool the warmed evaporator.
The condenser 34e cools the chlorofluorocarbon gas compressed by the compressor 34c to form liquid chlorofluorocarbon.
The cross fan 34f supplies refrigerant from the outside of the housing 34a to the surface of the evaporator 34b.

  In the cooling unit 34, an evaporator 34b, a compressor 34c, and a condenser 34e are connected as a closed circuit. The closed circuit normally contains chlorofluorocarbon as a refrigerant.

Here, the operation of the cooling unit 34 will be described.
Liquid chlorofluorocarbon is sent from the condenser 34e to the evaporator 34b. Then, the liquid chlorofluorocarbon is evaporated in the evaporator 34b to become chlorofluorocarbon gas, and the evaporator 34b is cooled by latent heat of evaporation. The medium supplied from the receiving hose 35b by the cross fan 34f passes between the cooled evaporators 34b, thereby being cooled on the surface of the evaporator 34b and discharged to the delivery hose 35a.

  Thereafter, the chlorofluorocarbon gas in the evaporator 34b warmed by the medium is sent to the compressor 34c and compressed in the compressor 34c to become high-temperature chlorofluorocarbon gas.

  Thereafter, the hot chlorofluorocarbon gas is sent to the condenser 34e. The condenser 34e is cooled by the air supplied from the outside of the housing 34a by the propeller fan 34d. At that time, the high-temperature chlorofluorocarbon gas in the condenser 34e is also cooled and becomes liquid chlorofluorocarbon. The air that has cooled the condenser 34e is discharged to the outside of the housing 34a. Then, the cooled liquid freon is sent again from the condenser 34e to the evaporator 34b.

  Hereinafter, an operation of cooling the RF coil 14b in the first embodiment with the refrigerant cooled by the cooling unit 34 will be described.

  As shown in FIGS. 2 and 3, the refrigerant that cools the RF coil 14 b is cooled by the cooling unit 34. And it passes the delivery hose 35a, the delivery port 29b, the supply port 14e, and the support part 14c, and arrives at the accommodating part 14a.

  And the refrigerant | coolant which reached | attained the accommodating part 14a cools the RF coil 14b. Thereafter, the air passes through the outlet 14g, the receiving port 29d, and the receiving hose 35b, and returns to the cooling unit 34.

The medium returned to the cooling unit 34 is cooled by the cooling unit 34. The cooled refrigerant is again supplied to the accommodating portion 14a. The transfer hose 35 passes through the inside of the subject transport unit 25 and is connected to the cooling unit 34.
As shown in FIG. 4, the refrigerant that cools the RF coil 14 b is transferred from the cooling unit 34 to the housing unit 14 a by the cross fan 34 f formed in the cooling unit 34.

  As described above, in the first embodiment, the refrigerant cooled by the cooling unit 34 is supplied to the storage unit 14a through the delivery hose 35a, the delivery port 29b, the supply port 14e, and the support unit 14c. And the heat_generation | fever by the Joule heat which generate | occur | produces in RF coil 14b is suppressed by cooling RF coil 14b with the refrigerant | coolant supplied to the accommodating part 14a. Therefore, the S / N ratio can be improved and the image quality can be improved.

<Second Embodiment>
5 and 6 are diagrams showing an apparatus used in the second embodiment of the magnetic resonance imaging apparatus according to the present invention. In the second embodiment, the constituent devices other than the RF coil unit 14 are the same as those in the first embodiment. Therefore, description is abbreviate | omitted about the location which overlaps.

  Here, FIG. 5 is a diagram illustrating a relationship among the RF coil unit 14, the cradle 26, and the cooling unit 34 in the second embodiment. 5A is a plan view, and FIG. 5B is a side view. In addition, the part shown with a broken line shows that it exists in the inside of an apparatus.

  On the other hand, FIG. 6 is a diagram showing the RF coil unit 14 installed on the mounting surface of the cradle 26 in the second embodiment. 6A is a front view, and FIG. 6B is a side view.

  In the second embodiment, as shown in FIGS. 5 and 6, the RF coil unit 14 includes an accommodation unit 14 a, an RF coil 14 b, a support unit 14 c, a supply hose 14 h, a discharge hose 14 i, and a connector. It has a box 14j, a supply port 14k, a discharge port 14l, and an RF coil connector 14m. That is, unlike the first embodiment, it has a supply hose 14h, a discharge hose 14i, and a connector box 14j.

The supply hose 14h and the discharge hose 14i are connected to the support portion 14c.
The connector box 14j is connected to the other ends of the supply hose 14h and the discharge hose 14i. The connector box 14j forms a supply port 14k and a discharge port 14l.

The supply port 14k is formed in the connector box. The supply port 14k supplies the refrigerant cooled by the cooling unit 34 to the support unit 14c.
The discharge port 14l is formed in the connector box 14j. The discharge port 14l discharges the refrigerant (medium) that has cooled the RF coil 14b to the cooling unit 34 in the accommodating unit 14a.
The RF coil connector 14m is a receiving connector for transmitting a magnetic resonance signal received by the RF coil to the outside.
Although not shown in FIG. 6, the connector box 14j is connected to an RF coil connector cable.

  Hereinafter, an operation of cooling the RF coil 14b with the refrigerant cooled by the cooling unit 34 in the second embodiment will be described.

  As shown in FIGS. 5 and 6, the connector box 14 j is connected to the cooling unit 34. The refrigerant that cools the RF coil 14 b is cooled by the cooling unit 34. Then, it passes through the connector box 14j, the supply hose 14h, and the support portion 14c and reaches the accommodating portion 14a.

  And the refrigerant | coolant which reached | attained the accommodating part 14a cools the RF coil 14b. Then, it passes through the discharge hose 14i and the connector box 14j and returns to the cooling unit 34. The medium returned to the cooling unit 34 is cooled by the cooling unit 34. The cooled refrigerant is again supplied to the accommodating portion 14a. In FIG. 5, the delivery port 29b and the receiving port 29d are not formed on the surface of the cradle 26. However, even if the sending port 29b and the receiving port 29d are formed, the implementation of the present invention is not affected.

  As described above, in the second embodiment, the refrigerant cooled by the cooling unit 34 is supplied to the storage unit 14a through the connector box 14j, the supply hose 14h, and the support unit 14c. And the heat_generation | fever by the Joule heat which generate | occur | produces in RF coil 14b is suppressed by cooling RF coil 14b with the refrigerant | coolant supplied to the accommodating part 14a. Therefore, as in the first embodiment, the S / N ratio can be improved and the image quality can be improved.

<Third Embodiment>
FIG. 7 is a diagram illustrating a relationship among the RF coil unit 14, the cradle 26, the amplifier accommodating unit 28a, and the cooling unit 34 according to the third embodiment. 7A is a plan view, and FIG. 7B is a side view. In addition, the part shown with a broken line shows that it exists in the inside of an apparatus.

  The third embodiment has an amplifier accommodating portion 28a. Except for this point, the second embodiment is the same as the first embodiment. Therefore, description is abbreviate | omitted about the location which overlaps.

  As shown in FIG. 7, the amplifier accommodating portion 28a includes an amplifier 28b, a delivery hose coupling portion 28c, a supply port 28d, a receiving hose coupling portion 28e, and a discharge port 28f.

The amplifier housing portion 28 a is formed inside the cradle 26. The amplifier accommodating part 28a accommodates the amplifier 28b inside. The amplifier accommodating portion 28a forms a delivery hose coupling portion 28c and a receiving hose coupling portion 28e.
The amplifier 28b amplifies the magnetic resonance signal received by the RF coil 14b.
The delivery hose coupling portion 28c includes a supply port 28d and is coupled to the delivery hose 35a.
The supply port 28d is formed in the delivery hose coupling part 28c, and supplies the refrigerant cooled by the cooling part 34 into the amplifier accommodating part 28a.
The receiving hose coupling portion 28e includes a discharge port 28f and is coupled to the receiving hose 35b.
The discharge port 28f is formed in the receiving hose coupling portion 28e, and discharges the refrigerant (medium) that has cooled the amplifier 28b to the receiving hose 35b in the amplifier housing portion 28a.

Although not shown in FIG. 7, the supply port 28d is provided with a check valve in order to prevent the medium in the amplifier accommodating portion 28a from flowing back to the delivery hose 35a.
The discharge port 28f is provided with a check valve in order to prevent the medium discharged to the receiving hose 35b from flowing back to the amplifier accommodating portion 28a.

  The operation of cooling the amplifier 28b in the third embodiment with the refrigerant cooled by the cooling unit 34 will be described below.

  As shown in FIG. 7, the refrigerant that cools the amplifier 28 b is cooled by the cooling unit 34. Then, it passes through the delivery hose 35a and the supply port 28d and reaches the amplifier accommodating portion 28a.

  And the refrigerant | coolant which reached | attained the amplifier accommodating part 28a cools the amplifier 28b. Thereafter, the air passes through the discharge port 28f and the receiving hose 35b, and returns to the cooling unit 34.

  The medium returned to the cooling unit 34 is cooled by the cooling unit 34. The cooled refrigerant is supplied again to the amplifier accommodating portion 28a. The transfer hose 35 passes through the inside of the subject transport unit 25 and is connected to the cooling unit 34.

  As described above, in the third embodiment, the refrigerant cooled by the cooling unit 34 is supplied to the amplifier accommodating unit 28a through the delivery hose 35a and the supply port 28d. Then, by cooling the amplifier 28b with the refrigerant supplied to the amplifier accommodating portion 28a, heat generation due to Joule heat generated in the amplifier 28b is suppressed. Therefore, as in the first embodiment, the S / N ratio can be improved and the image quality can be improved.

  Note that the magnetic resonance imaging apparatus 1 in the present embodiment corresponds to the magnetic resonance imaging apparatus of the present invention. Further, the RF coil unit 14 of the present embodiment corresponds to the RF coil unit or the RF coil unit of the present invention. Moreover, the accommodating part 14a of this embodiment is corresponded to the accommodating part of this invention. Further, the RF coil 14b of the present embodiment corresponds to the RF coil of the present invention. Moreover, the support part 14c of this embodiment is corresponded to the support part of this invention. In addition, the first coupling portion 14d of the present embodiment corresponds to the first coupling portion of the present invention. Further, the supply port 14e of the present embodiment corresponds to the supply port of the present invention. The second coupling portion 14f of the present embodiment corresponds to the second coupling portion of the present invention. Further, the discharge port 14g of the present embodiment corresponds to the discharge port of the present invention. Further, the connector box 14j of the present embodiment corresponds to the connector box of the present invention. Further, the supply port 14k of the present embodiment corresponds to the supply port of the present invention. Further, the discharge port 14l of the present embodiment corresponds to the discharge port of the present invention. Further, the cradle 26 of the present embodiment corresponds to the cradle of the present invention. Moreover, the amplifier accommodating part 28a of this embodiment is corresponded to the amplifier accommodating part of this invention. Further, the amplifier 28b of the present embodiment corresponds to the amplifier of the present invention. Further, the first coupled portion 29a of the present embodiment corresponds to the first coupled portion of the present invention. Moreover, the delivery port 29b of this embodiment is corresponded to the delivery port of this invention. The second coupled portion 29c of the present embodiment corresponds to the second coupled portion of the present invention. Further, the receiving port 29d of the present embodiment corresponds to the receiving port of the present invention.

  In implementing the present invention, the present invention is not limited to the above-described embodiment, and various modifications can be employed.

  In the first embodiment, the medium that has cooled the RF coil 14b in the accommodating portion 14a passes through the discharge port 14g, the receiving port 29d, and the receiving hose 35b, and returns to the cooling unit 34, but is not limited thereto. The medium need not be discharged from the outlet provided in the storage portion 14 a to the outside of the storage portion 14 a and returned to the cooling portion 34. At this time, the refrigerant (medium) is supplied to the cooling unit 34 from the outside.

  In 2nd Embodiment, although the supply hose 14h and the discharge hose 14i are connected to the support part 14c, it is not limited to this, For example, you may connect with the accommodating part 14a. In the second embodiment, the connector box 14j is directly connected to the cooling unit 34. However, the present invention is not limited to this. The connector box 14j may be connected to the cooling unit 34 via the sending hose 35a and the receiving hose 35b. Good.

  In the third embodiment, the amplifier accommodating portion 28 a is formed inside the cradle 26, but is not limited thereto, and may be formed inside the cradle moving portion 27, for example. In the third embodiment, the amplifier 28b is accommodated in the amplifier accommodating portion 28a. However, the present invention is not limited to this. For example, the amplifier 28b may be accommodated in the accommodating portion 14a along with the RF coil 14b.

FIG. 1 is a configuration diagram showing a configuration of a magnetic resonance imaging apparatus according to an embodiment of the present invention. FIG. 2 is a diagram illustrating a relationship among the RF coil unit, the cradle, and the cooling unit in the magnetic resonance imaging apparatus according to the first embodiment of the present invention. FIG. 3 is a diagram showing the configuration of the RF coil unit in the magnetic resonance imaging apparatus according to the first embodiment of the present invention. FIG. 4 is a plan sectional view showing a configuration of a cooling unit in the magnetic resonance imaging apparatus according to the embodiment of the present invention. FIG. 5 is a diagram showing a relationship among the RF coil unit, the cradle, and the cooling unit in the magnetic resonance imaging apparatus according to the second embodiment of the present invention. FIG. 6 is a diagram showing the configuration of the RF coil unit in the magnetic resonance imaging apparatus according to the second embodiment of the present invention. FIG. 7 is a diagram showing a relationship among the RF coil unit, the cradle, the amplifier housing unit, and the cooling unit in the magnetic resonance imaging apparatus according to the third embodiment of the present invention.

Explanation of symbols

1: Magnetic resonance imaging apparatus 11: Static magnetic field space 12: Static magnetic field magnet unit 13: Gradient coil unit 14: RF coil unit 22: RF drive unit 23: Gradient drive unit 24: Data collection unit 25: Subject transport unit 26: Cradle 28a: Amplifier housing unit 29: Coupled unit 30: Control unit 31: Data processing unit 32: Operation unit 33: Display unit 34: Cooling unit 35: Transfer hose 40: Subject

Claims (11)

A magnetic resonance imaging apparatus that generates an image of the subject based on a magnetic resonance signal generated in the subject by irradiating the subject in a static magnetic field space with an RF pulse,
An RF coil for receiving the magnetic resonance signal;
A magnetic resonance imaging apparatus, comprising: a cooling unit that supplies a refrigerant for cooling the RF coil. A cradle that supports the subject on a mounting surface;
An RF coil part including the RF coil, and
On the placement surface of the cradle, a delivery port for sending out the refrigerant supplied from the cooling unit is formed,
The magnetic resonance imaging apparatus according to claim 1, wherein a supply port for supplying the refrigerant fed from a delivery port formed on a placement surface of the cradle to the RF coil unit is formed in the RF coil unit. A discharge port for discharging the refrigerant supplied from the supply port to the RF coil unit is formed in the RF coil unit,
The magnetic resonance imaging apparatus according to claim 2, wherein a receiving port for receiving the refrigerant discharged from the discharge port formed in the RF coil unit is formed on the mounting surface of the cradle. The RF coil section is
A first coupling portion formed with the supply port and coupled to the cradle;
The discharge port is formed and has a second coupling portion coupled to the cradle;
The cradle is
A first coupled portion formed with the delivery port and coupled to the first coupling portion;
The magnetic resonance imaging apparatus according to claim 3, further comprising: a second coupled portion in which the receiving port is formed and the second coupling portion is coupled. The RF coil section is
An accommodating portion for accommodating the RF coil;
A support part for supporting the housing part,
The support part is
The first coupling part;
The second coupling portion; and
The supply port is formed in the first coupling portion,
The magnetic resonance imaging apparatus according to claim 3, wherein the discharge port is formed in the second coupling portion. The RF coil section is
A connector box connected to the RF coil;
A supply port for supplying the refrigerant sent from the cooling unit to the connector box to the RF coil unit;
The magnetic resonance imaging apparatus according to claim 1, wherein a discharge port for discharging the refrigerant supplied from the supply port to the RF coil unit is formed. The magnetic resonance imaging apparatus according to claim 4, wherein the RF coil unit is formed so as to be detachable from a mounting surface of the cradle. 8. The magnetic resonance imaging apparatus according to claim 2, wherein each of a supply port and a discharge port formed in the RF coil unit includes a check valve that prevents a back flow of the refrigerant. Having an amplifier connected to the RF coil section;
The magnetic resonance imaging apparatus according to claim 1, wherein the cooling unit cools the amplifier by supplying the refrigerant to the amplifier. The cradle includes an amplifier housing portion that houses the amplifier,
The amplifier is housed in an amplifier housing portion of the cradle;
The magnetic resonance imaging apparatus according to claim 9, wherein the cooling unit supplies a refrigerant to the amplifier housed in the amplifier housing part of the cradle. The magnetic resonance imaging apparatus according to claim 1, wherein the refrigerant is a gas.

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