Pressurized gas-powered magnetic resonance imaging antenna

Abstract

A magnetic resonance imaging antenna (114) including one or more coil elements (115) is disclosed. The magnetic resonance imaging antenna further includes a radio frequency system (116) coupled to the one or more coil elements. The magnetic resonance imaging antenna further includes a gas inlet (200) configured to receive pressurized gas. The magnetic resonance imaging antenna further includes a gas outlet (202) configured to discharge the pressurized gas. The magnetic resonance imaging antenna further includes a generator (117) configured to convert mechanical energy generated by the transfer of the pressurized gas from the gas inlet to the gas outlet in the presence of an external magnetic field into electrical energy. The generator is configured to use the electrical energy to power the radio frequency system.

Description

Technical Field

[0001] The present invention relates to magnetic resonance imaging, and more particularly to an antenna for magnetic resonance imaging. Background Art

[0002] As part of the process for generating images within a patient's body, a large static magnetic field is used by a magnetic resonance imaging (MRI) scanner to align the nuclear spins of atoms. This large static magnetic field is referred to as the B0 field or the main magnetic field. Various physical quantities or properties of an object, such as proton density or various relaxation times, such as T1, T2 or T2-star values, can be measured spatially using MRI.

[0003] In addition to using the B0 field, there are also antennas for transmitting and receiving radio frequency (RF) signals. The transmitted RF signal (B1 field) is used to manipulate the orientation of the spins. The received RF signal (recorded as magnetic resonance imaging data) is received from the spins and used to reconstruct a magnetic resonance image. When receiving the RF signal, it is beneficial to place electronics, such as preamplifiers and digital converters, as close as possible to the respective antenna elements. However, the presence of the large magnetic field and RF field can make powering these circuits difficult.

[0004] U.S. Patent Publication US10175313 B2 discloses an MRI apparatus including a power transmission unit, a signal reception unit, and an image reconstruction unit. The power transmission unit wirelessly transmits electrical power to an RF coil device by magnetic resonance type wireless power transmission through magnetic coupling. The signal reception unit wirelessly receives digitized nuclear magnetic resonance signals wirelessly transmitted from the RF coil device. The image reconstruction unit obtains the nuclear magnetic resonance signals received by the signal reception unit and reconstructs image data of an object based on the nuclear magnetic resonance signals. Summary of the Invention

[0005] The present invention provides a magnetic resonance imaging antenna and a magnetic resonance imaging system.

[0006] As described above, it can be difficult to supply power to electronic circuits within the imaging area of a magnetic resonance imaging system. Embodiments of the present invention can provide an improved means of powering a magnetic resonance imaging antenna by using a generator powered by compressed gas. This has the advantage that there are no electrical wires that need to be protected from RF signals within the magnetic resonance imaging system. In addition, the presence of the B0 field eliminates the need for the generator to have its own magnet. Using compressed gas allows the generator to be powered as needed and even constantly supplied during long magnetic resonance imaging examinations. This can eliminate the need for having batteries or capacitors to store energy to power the magnetic resonance imaging antenna.

[0007] In one aspect, the present invention provides a magnetic resonance imaging antenna including one or more coil elements. The magnetic resonance imaging antenna further includes a radio frequency system connected to the one or more coil elements. The magnetic resonance imaging antenna further includes a gas inlet configured to receive pressurized gas. The magnetic resonance imaging antenna further includes a gas outlet configured to discharge the pressurized gas. The magnetic resonance imaging antenna further includes a generator configured to convert mechanical energy generated by the pressurized gas transferred from the gas inlet to the gas outlet into electrical energy in the presence of an external magnetic field.

[0008] The generator is configured to use the electrical energy to power the magnetic resonance imaging antenna including the radio frequency system. Depending on the configuration, the magnetic resonance imaging antenna may include components such as: tuning / detuning circuits, AD converters, DA converters, digital-to-digital optical converters, sensors, and / or other electrical accessories. All of them can be powered by the generator.

[0009] The uniqueness of the generator is that it does not have its own magnet. A magnetic resonance imaging system typically includes a main magnet that generates the large magnetic field necessary to perform magnetic resonance imaging. The external magnetic field can be the main magnetic field of the magnetic resonance imaging system. This embodiment can be beneficial because it provides a means for supplying power to the magnetic resonance imaging antenna that is fully compatible with the large magnetic field and radio frequency field present in the magnetic resonance imaging system. It can avoid the problems and difficulties of charging a battery or capacitor to power the magnetic resonance imaging antenna.

[0010] In another embodiment, the generator includes a turbine configured to be rotated by the pressurized gas transferred from the gas inlet to the gas outlet. The turbine is configured to rotate a conductive element. The conductive element is configured to generate electrical energy when rotated in an external magnetic field. This embodiment can be beneficial because it provides an intuitive means for supplying electrical power to the radio frequency system.

[0011] In another embodiment, the conductive element is a conductive loop. For example, since the loop is rotated by the turbine, it can act as a generator.

[0012] In another embodiment, the turbine includes paddles. The conductive loop is attached to at least two of the paddles. For example, the conductive loop can be integrated into the paddles of the turbine. This can be beneficial because it can reduce the size of the turbine and make it more compact. Incorporating the conductive loop into the paddles can also make them more durable.

[0013] In another embodiment, the generator includes a switching circuit in series with a conductive loop. The switching circuit is configured to be powered by the conductive loop. The switching circuit is configured to electronically open and electronically close the conductive loop at a predetermined frequency. The generator further includes one or more stationary pick-up coils configured to receive electrical energy switched at the predetermined frequency. At least one stationary pick-up coil is configured to power a radio frequency system. This embodiment can be beneficial because it can eliminate the need for brushes in the generator. Also, by using a circuit to open and close the loop at a predetermined frequency, a frequency can be selected that is, for example, very efficient and outside the range used for magnetic resonance imaging procedures. For example, 1 MHz would be very efficient in transferring energy from the conductive loop to the stationary pick-up coil. 10 MHz could work even better.

[0014] In another embodiment, the generator includes a brush for supplying electrical energy from the conductive loop to the radio frequency system.

[0015] In another embodiment, the turbine has a rotating shaft. The conductive element is asymmetric with respect to the rotating shaft. The generator further includes one or more stationary pick-up coils. The stationary pick-up coils are configured to receive electrical energy caused by the rotation of the conductive element. At least one stationary pick-up coil is configured to supply electrical energy to the radio frequency system. In this embodiment, an object that is asymmetric with respect to the rotating shaft can have the effect of eddy currents when it rotates. These eddy currents can generate a radio frequency field that can be picked up by the stationary pick-up coils. For example, a disk-shaped structure can be rotated. For example, this may not be as efficient as using a loop, but it is still an extremely durable option.

[0016] In another embodiment, the turbine includes a rotor. The rotor has a diameter of less than 2 mm and, in some cases, less than 1 mm. Using a rotor with a diameter of less than 2 mm or 1 mm means that the rotor can have a very high rotational speed. This means that the noise generated by it can be above the audible range.

[0017] In another embodiment, the turbine is configured to have a rotational speed of at least 1.2 million revolutions per minute. This embodiment can be beneficial because the noise generated by the turbine can then be above 20,000 Hz, which is above the normal human hearing range.

[0018] In another embodiment, the magnetic resonance imaging antenna includes a plurality of turbines. For example, the turbines can be mounted such that their axes of rotation are perpendicular to each other. This can be advantageous when the magnetic resonance imaging antenna can be placed in different orientations relative to the magnetic resonance imaging magnet. Having a plurality of turbines can have the advantage that, regardless of the position of the magnetic resonance imaging antenna, it can still generate electrical energy for powering the radio frequency system.

[0019] In another embodiment, the generator includes a resonance cavity configured to generate acoustic resonance in response to the conveyance of pressurized gas from a gas inlet to a gas outlet. The generator further includes a mechanical member configured to vibrate in response to the acoustic resonance. The mechanical member is suspended within the resonance cavity. The generator also includes at least one conductive path configured such that movement of the mechanical member causes electrical energy to be generated in an external magnetic field. For example, this can take different forms. In some examples, the conductive path at least partially travels above the mechanical member such that as the mechanical member moves in the external magnetic field, it causes electrical energy to be generated in the at least one conductive path.

[0020] In other examples, the mechanical member can, for example, have a torsional or rotational movement within the resonance cavity, and its movement within the magnetic field can result in a radio frequency perturbation that can be picked up, and in such a case, the at least one conductive path is a pick-up coil configured to collect such electrical energy.

[0021] In another embodiment, the resonance cavity is a whistle up to ultrasonic frequencies. This embodiment can be beneficial because then the resonance cavity can be constructed such that it cannot be heard by a typical person.

[0022] In another embodiment, the mechanical member includes a conductive element. The conductive element is configured to vibrate and / or vibrate torsionally with a rotating member. Vibrationally and / or torsionally vibrating the mechanical member can be equivalent to a translational or rotational movement. This can result in a perturbation in the magnetic field. The at least one conductive path is one or more stationary pick-up coils configured to receive the electrical energy generated by the vibration of the conductive element.

[0023] The at least one stationary pick-up coil is configured to supply electrical energy to a radio frequency system. This embodiment can be beneficial because it does not require any electrical connection between the mechanical member and the at least one stationary pick-up coil. For example, when the mechanical member becomes worn, it may be possible to replace the part without making any changes to the circuitry of the magnetic resonance imaging antenna.

[0024] In another embodiment, each of the at least one conductive paths is at least partially on the mechanical member. As the mechanical member vibrates, the area enclosed by the conductive path can change because when the magnetic resonance imaging antenna is placed in an external magnetic field (such as a field from a magnetic resonance imaging system), this movement of the conductive path on the mechanical member will cause electrical energy to be generated. In other words, each of the at least one conductive paths is configured such that movement of the mechanical member causes the area enclosed by the conductive path to change.

[0025] In another embodiment, at least one conductive path is two conductive paths. The two conductive paths are electrically isolated. When the two conductive paths are configured, the two conductive paths are configured to generate electrical energy independently. For example, the mechanical member can be placed such that two vertical regions each surrounded by a conductive path can be defined. This can enable the generator to function regardless of the orientation with respect to the magnetic field of the magnetic resonance imaging system.

[0026] In another embodiment, the generator is arranged such that pressurized gas conveyed from a gas inlet to a gas outlet cools the radio frequency system. For example, the generator can also act as a heat sink. This can be beneficial as it can provide an effective means of reducing the amount of heat near the object during a magnetic resonance imaging examination.

[0027] In another embodiment, the radio frequency system includes a receiver coupled to at least a portion of one or more coil elements.

[0028] In another embodiment, the radio frequency system further includes a transmitter coupled to at least a portion of one or more coil elements. For example, the coil can act as a transmitter, a receiver, or a transceiver.

[0029] In another embodiment, the magnetic resonance imaging antenna includes an optical fiber communication system configured to control the radio frequency system. This can be beneficial as optical fibers do not interfere with the electric or magnetic fields present during a magnetic resonance examination.

[0030] In another embodiment, the magnetic resonance imaging antenna includes a wireless communication system configured to control the radio frequency system. This can be beneficial as it can provide a means of illuminating the wires going to and from the magnetic resonance imaging antenna.

[0031] In another aspect, the present invention provides a magnetic resonance imaging system including a magnetic resonance imaging antenna according to an embodiment. The magnetic resonance imaging system includes a main magnet. The main magnet is configured to generate an external magnetic field. The magnetic resonance imaging system further includes a pressurized gas system for supplying pressurized gas to the magnetic resonance imaging coil. This embodiment can be beneficial as the magnetic resonance imaging system provides the pressurized gas and the external magnetic field required for the generator to generate electrical energy.

[0032] In another embodiment, the magnetic resonance imaging system further includes a memory storing machine-executable instructions and pulse sequence commands. The pulse sequence commands are configured to control the magnetic resonance imaging system to acquire magnetic resonance imaging data using the magnetic resonance imaging antenna. The magnetic resonance imaging system further includes a processor configured to control the magnetic resonance imaging system.

[0033] The running of the machine-executable instructions causes the processor to acquire magnetic resonance imaging data by commanding a magnetic resonance imaging system with a pulse sequence. The running of the machine-executable instructions also causes the processor to power a magnetic resonance imaging coil by controlling a pressurized gas system to supply pressurized gas during the acquisition of magnetic resonance imaging data.

[0034] It should be understood that one or more of the above-described embodiments of the present invention can be combined, provided that the combined embodiments are not mutually exclusive.

[0035] As those skilled in the art will recognize, various aspects of the present invention can be implemented as an apparatus, a method, or a computer program product. Accordingly, various aspects of the present invention can take the form of an entirely hardware embodiment, an entirely software embodiment (including firmware, resident software, microcode, etc.), or an embodiment combining software and hardware aspects (collectively referred to herein as "circuitry," "module," or "system"). Additionally, various aspects of the present invention can take the form of a computer program product implemented in one or more computer-readable media having computer-executable code embodied thereon.

[0036] Any combination of one or more computer-readable media can be utilized. The computer-readable media can be a computer-readable signal medium or a computer-readable storage medium. As used herein, "computer-readable storage medium" encompasses any tangible storage medium that can store instructions executable by a processor of a computing device. The computer-readable storage medium can be referred to as a computer-readable non-transitory storage medium. The computer-readable storage medium can also be referred to as a tangible computer-readable medium. In some embodiments, the computer-readable storage medium can also be capable of storing data that can be accessed by a processor of a computing device. Examples of computer-readable storage media include, but are not limited to: floppy disks, magnetic hard disk drives, solid state drives, flash memory, USB thumb drives, random access memory (RAM), read only memory (ROM), optical disks, magneto-optical disks, and register files of a processor. Examples of optical disks include compact disks (CDs) and digital versatile disks (DVDs), e.g., CD-ROM, CD-RW, CD-R, DVD-ROM, DVD-RW, or DVD-R disks. The term computer-readable storage medium also refers to various types of recording media that can be accessed by a computing device via a network or communication link. For example, data can be retrieved over a modem, the Internet, or a local area network. Any suitable medium can be used to transmit the computer-executable code embodied on the computer-readable medium, including but not limited to wireless, wired, fiber optic cable, RF, etc., or any suitable combination of the foregoing.

[0037] A computer-readable signal medium may include a propagated data signal having computer-executable code embodied therein, for example, in baseband or as part of a carrier wave. Such a propagated signal may take any of a variety of forms, including but not limited to electromagnetic, optical, or any suitable combination thereof. A computer-readable signal medium may be any computer-readable medium that is not a computer-readable storage medium and that can communicate, propagate, or transport a program for use by or in connection with an instruction execution system, apparatus, or device.

[0038] "Computer memory" or "memory" is an example of a computer-readable storage medium. Computer memory is any memory that can be directly accessed by a processor. "Computer storage device" or "storage device" is another example of a computer-readable storage medium. A computer storage device is any non-volatile computer-readable storage medium. In some embodiments, a computer storage device may also be a computer memory, or vice versa.

[0039] As used herein, "processor" encompasses electronic components capable of executing a program or machine-executable instructions or computer-executable code. References to a computing device that includes a "processor" should be construed to be capable of including more than one processor or processing core. The processor may be, for example, a multi-core processor. A processor may also refer to a collection of processors within a single computer system or distributed among multiple computer systems. The term computing device should also be construed to be capable of referring to a collection or network of computing devices each including one or more processors. Computer-executable code may be executed by multiple processors that may be within the same computing device or even distributed among multiple computing devices.

[0040] Computer-executable code may include machine-executable instructions or programs that cause the processor to perform aspects of the present invention. The computer-executable code for performing operations in accordance with aspects of the present invention may be written in any combination of one or more programming languages and compiled into machine-executable instructions, the one or more programming languages including object-oriented programming languages such as Java, Smalltalk, C++, etc. and conventional procedural programming languages such as the "C" programming language or similar programming languages. In some instances, the computer-executable code may take the form of a high-level language or take a pre-compiled form and be used in conjunction with an interpreter that generates machine-executable instructions at runtime.

[0041] The computer-executable code can be executed entirely on the user's computer, partially on the user's computer (as a stand-alone software package), partially on the user's computer and partially on a remote computer, or entirely on a remote computer or server. In the latter case, the remote computer can be connected to the user's computer via any type of network including a local area network (LAN) or a wide area network (WAN), or can be connected to an external computer (e.g., via the Internet using an Internet service provider).

[0042] Aspects of the present invention are described with reference to the flowcharts, illustrations, and / or block diagrams of methods, apparatus (systems), and computer program products according to embodiments of the invention. It should be understood that, when applicable, each block or portion of a block in the flowcharts, illustrations, and / or block diagrams can be implemented by computer program instructions in the form of computer-executable code. It should also be understood that, when not mutually exclusive, combinations of blocks from different flowcharts, illustrations, and / or block diagrams can be combined. These computer program instructions can be provided to a processor of a general purpose computer, a special purpose computer, or other programmable data processing apparatus that produces a machine, such that the instructions executed via the processor of the computer or other programmable data processing apparatus create means for implementing the functions / actions specified in the flowchart and / or one or more block diagram blocks.

[0043] These computer program instructions can also be stored in a computer-readable medium that can direct a computer, other programmable data processing apparatus, or other device to operate in a particular manner, such that the instructions stored in the computer-readable medium produce an article of manufacture including instructions for implementing the functions / actions specified in the flowchart and / or one or more block diagram blocks.

[0044] The computer program instructions can also be loaded onto a computer, other programmable data processing apparatus, or other device to cause a series of operational steps to be performed on the computer, other programmable apparatus, or other device, thereby producing a computer-implemented process such that the instructions executed on the computer or other programmable apparatus provide a process for implementing the functions / actions specified in the flowchart and / or one or more block diagram blocks.

[0045] As used herein, "user interface" is an interface that allows a user or operator to interact with a computer or computer system. A "user interface" may also be referred to as a "human-machine interface device". The user interface can provide information or data to the operator and / or receive information or data from the operator. The user interface can enable input from the operator to be received by the computer and can provide output from the computer to the user. In other words, the user interface can allow the operator to control or manipulate the computer, and the interface can allow the computer to indicate the effects of the operator's control or manipulation. The display of data or information on a display or graphical user interface is an example of providing information to the operator. The receipt of data via a keyboard, mouse, trackball, touchpad, pointing stick, graphics tablet, joystick, gamepad, webcam, headset, pedal, wired glove, remote control, and accelerometer are all examples of user interface components that implement the receipt of information or data from the operator.

[0046] As used herein, "hardware interface" encompasses interfaces that enable a processor of a computer system to interact with and / or control external computing devices and / or apparatuses. The hardware interface can allow the processor to send control signals or instructions to the external computing devices and / or apparatuses. The hardware interface can also enable the processor to exchange data with the external computing devices and / or apparatuses. Examples of hardware interfaces include, but are not limited to: Universal Serial Bus, IEEE 1394 port, parallel port, IEEE 1284 port, serial port, RS-232 port, IEEE-488 port, Bluetooth connection, wireless local area network connection, TCP / IP connection, Ethernet connection, control voltage interface, MIDI interface, analog input interface, and digital input interface.

[0047] As used herein, "display" or "display device" encompasses output devices or user interfaces suitable for displaying images or data. The display can output visual, audio, and / or tactile data. Examples of displays include, but are not limited to: computer monitors, television screens, touchscreens, tactile electronic displays, braille screens, cathode ray tubes (CRT), storage tubes, bistable displays, electronic paper, vector displays, flat panel displays, vacuum fluorescent displays (VF), light emitting diode (LED) displays, electroluminescent displays (ELD), plasma display panels (PDP), liquid crystal displays (LCD), organic light emitting diode displays (OLED), projectors, and head-mounted displays.

[0048] Magnetic resonance (MR) data is defined herein as the measurement of radio frequency signals emitted by atomic spins, recorded using the antenna of a magnetic resonance device during a magnetic resonance imaging scan. MRF magnetic resonance data is magnetic resonance data. Magnetic resonance data is an example of medical image data. A magnetic resonance imaging (MRI) image or MR image is defined herein as a reconstructed two-dimensional or three-dimensional visualization of anatomical data contained within magnetic resonance imaging data. This visualization can be performed using a computer. BRIEF DESCRIPTION OF THE DRAWINGS

[0049] In the following, preferred embodiments of the present invention will be described only by way of example and with reference to the drawings, in which:

[0050] Figure 1 illustrates an example of a magnetic resonance imaging system;

[0051] Figure 2 illustrates an example of a magnetic resonance imaging antenna;

[0052] Figure 3 shows a flowchart of a method of operating a magnetic resonance imaging system Figure 1 illustrated;

[0053] Figure 4 illustrates an example of a generator;

[0054] Figure 5 illustrates a further example of a generator;

[0055] Figure 6 illustrates a further example of a generator;

[0056] Figure 7 illustrates a further example of a generator;

[0057] Figure 8 illustrates a further example of a generator;

[0058] Figure 9 illustrates a further example of a generator;

[0059] Figure 10 illustrates a further example of a generator; and

[0060] Figure 11 illustrates a further example of a generator.

[0061] LIST OF REFERENCE NUMERALS

[0062] 100 Magnetic resonance imaging system

[0063] 104 Magnet

[0064] 106 Bore of the magnet

[0065] 108 Imaging region

[0066] 109 Region of interest

[0067] 110 Magnetic field gradient coil

[0068] 112 Magnetic field gradient coil power supply

[0069] 114 Magnetic resonance imaging antenna

[0070] 115 Coil element

[0071] 116 Radio frequency system

[0072] 117 Generator

[0073] 118 Object

[0074] 120 Object support

[0075] 122 Pressurized gas system

[0076] 124 Gas pipeline

[0077] 125 Optical fiber communication system

[0078] 126 Computer system

[0079] 128 Hardware interface

[0080] 130 Processor

[0081] 132 User interface

[0082] 134 Computer memory

[0083] 140 Machine-executable instructions

[0084] 142 Pulse sequence command

[0085] 144 Magnetic resonance imaging data

[0086] 146 Magnetic resonance image

[0087] 200 Gas inlet

[0088] 202 Gas outlet

[0089] 204 Optional muffler

[0090] 206 Communication system

[0091] 300 Acquiring magnetic resonance imaging data by controlling a magnetic resonance imaging system using pulse sequence commands

[0092] 302 Powers a magnetic resonance imaging coil by controlling a pressurized gas system to supply pressurized gas during acquisition of magnetic resonance imaging data

[0093] 400 Turbine

[0094] 401 Rotor

[0095] 402 Blade

[0096] 404 Rotating shaft

[0097] 406 Conductive loop

[0098] 500 Switching circuit

[0099] 502 Fixed pickup coil

[0100] 600 Conductive plate

[0101] 700 Resonant cavity

[0102] 702 Mechanical component

[0103] 702’ Mechanical component

[0104] 900 Conductive path

[0105] 902 Rectifier circuit

[0106] 1000 Conductive part

[0107] 1002 Elastic element

[0108] 1100 Single attachment point Detailed implementation

[0109] In these figures, elements with similar numbers are equivalent elements or perform the same function. If functionally equivalent, elements previously discussed will not necessarily be discussed in subsequent figures.

[0110] Figure 1An example of a magnetic resonance imaging system 100 with a magnet 104 is shown. The magnet 104 is a superconducting cylindrical magnet having a bore 106 therethrough. It is also possible to use different types of magnets; for example, it is also possible to use both split cylindrical magnets and so-called open magnets. A split cylindrical magnet is similar to a standard cylindrical magnet, except that the cryostat has been split into two parts to allow access to the isoplanes of the magnet, and such a magnet can be used, for example, in combination with charged particle beam therapy. An open magnet has two magnet parts, one above the other, with a space in the middle large enough to accommodate an object: the arrangement of the two part regions is similar to the arrangement of Helmholtz coils. Open magnets are popular because the object is less restricted. Inside the cryostat of the cylindrical magnet there is a set of superconducting coils. Inside the bore 106 of the cylindrical magnet 104, there is an imaging region 108 in which the magnetic field is strong and uniform enough to perform magnetic resonance imaging. An area of interest 109 within the imaging region 108 is shown. Magnetic resonance data is typically acquired for the area of interest. An object 118 is shown being supported by an object support 120 such that at least a portion of the object 118 is within the imaging region 108 and the area of interest 109.

[0111] There is also a set of magnetic field gradient coils 110 within the bore 106 of the magnet, which are used to acquire preliminary magnetic resonance data to spatially encode magnetic spins within the imaging region 108 of the magnet 104. The magnetic field gradient coils 110 are connected to a magnetic field gradient coil power supply 112. The magnetic field gradient coils 110 are intended to be representative. Typically, the magnetic field gradient coils 110 include three independent coil sets for spatially encoding in three orthogonal spatial directions. The magnetic field gradient power supply supplies current to the magnetic field gradient coils. The current supplied to the magnetic field gradient coils 110 is controlled according to time and can be ramped or pulsed.

[0112] Within the imaging region 108, a magnetic resonance imaging antenna 114 is visible. The magnetic resonance imaging antenna 114 includes one or more coil elements 115, a radio frequency system 116, and a generator 117. The radio frequency system 116 is coupled to the coil elements 115 and can act as a receiver and / or transmitter in different examples. The magnetic resonance imaging antenna 114 is connected to a computer 126 via an optical fiber connection 125 or a communication system connection. The optical fiber connection 125 can be used to exchange digital information between the computer 126 and the magnetic resonance imaging antenna 114. The optical fiber connection 125 can be replaced, for example, by a wireless connection such as a Wi-Fi network or a Bluetooth connection.

[0113] The magnetic resonance imaging antenna can be a transmit coil and / or a receive coil.

[0114] There is a pressurized gas system 122 external to the magnet 104. There is a gas line 124 between the pressurized gas system 122 and the generator 117. The pressurized gas supplies gas pressure to the generator 117, which converts the gas pressure into electrical energy for powering the radio frequency system 116. The magnetic resonance imaging antenna 114 may also have a plurality of receive / transmit elements capable of transmitting and / or receiving on separate channels. The sub-antennas for each of these channels are referred to herein as coil elements.

[0115] The magnetic resonance imaging antenna 114, the magnetic field gradient coil power supply, and the pressurized gas system 122 are shown connected to a hardware interface 128 of a computer system 126. The computer system also includes a processor 130 that communicates with the hardware system 128, a memory 134, and a user interface 132. The memory 134 can be any combination of memories accessible to the processor 130. This can include things such as main memory, cache memory, and also includes non-volatile memory such as flash RAM, hard disk drives, or other storage devices. In some examples, the memory 134 can be considered a non-transitory computer-readable medium.

[0116] The memory 134 is shown as containing machine-executable instructions 140. The machine-executable instructions 140 enable the processor 130 to perform various control tasks of the magnetic resonance imaging system 100 and perform various numerical and image processing tasks. The memory 134 is also shown as containing pulse sequence commands 142. The pulse sequence commands can be commands or data that are converted into such commands that enable the processor 130 to control the magnetic resonance imaging system 100 to acquire magnetic resonance imaging data. The memory 134 is also shown as containing magnetic resonance imaging data 144 acquired by controlling the magnetic resonance imaging system 100 with the pulse sequence commands 142. The memory 134 is also shown as containing magnetic resonance images 146 reconstructed from the magnetic resonance imaging data 144.

[0117] Figure 2 There is shown Figure 1 a more detailed view of the magnetic resonance imaging antenna 114 that exists in. The magnetic resonance imaging antenna 114 is shown as including a plurality of coil elements 115. These coil elements 115 are coupled to the radio frequency system 116. Depending on the particular example, the radio frequency system 116 can be a transmitter and / or a receiver. The radio frequency system 116 is shown as having an optional communication system 206. The communication system 206 can be, for example, a connection for fiber optic or for a wireless communication system such as Wi-Fi. This can enable the magnetic resonance imaging antenna 114 to be controlled without using a wired connection.

[0118] The generator 117 is on top of the radio frequency system 116. The generator 117 has a gas inlet 200 and a gas outlet 202. Pressurized gas enters through the gas inlet 200 and exits through the gas outlet 202. The mechanical work performed thereby is converted into electrical energy by the generator 117. In this example, there is an optional muffler 204 that is attached to the gas outlet 202. This may be useful, for example, in reducing the amount of audible acoustic noise from the generator 117.

[0119] Figure 3 The illustrated operation Figure 1 is shown in the flowchart of the method of the magnetic resonance imaging system 100. First, in step 300, magnetic resonance imaging data 144 is acquired by controlling the magnetic resonance imaging system 100 with a pulse sequence command 142. Next, in step 302, the magnetic resonance imaging coil 114 is powered by controlling the pressurized gas system 122 to supply pressurized gas during the acquisition of the magnetic resonance imaging data 144.

[0120] Figure 4 An example of the generator 117 is illustrated. In this example, the generator 117 includes a turbine 400 with a rotor 401. Pressurized gas entering at the inlet and exiting at the gas outlet 202 causes the turbine 400 to rotate. It rotates about a rotation axis 404. The turbine 400 includes a plurality of vanes 402. There are conductive loops 406 within two opposing vanes 402. As the vanes 402 rotate, a current is generated into the conductive loops 406. In Figure 4 the example shown, for example, brushes can be used to make the electrical connection to the conductive loops 406 and supply electrical energy to the radio frequency system.

[0121] Figure 5 An alternative generator 117 is shown. Figure 5 The example in Figure 4 is similar to the example in Figure 4 except that the version in

[0122] does not require brushes. In this example, the conductive loops 406 are connected to a switch circuit 500 that is configured to electrically connect and disconnect the loops 406. This results in an oscillating electromagnetic field that can be picked up by a stationary pickup coil 502. The stationary pickup coil 502 is shown as being embedded in the housing of the generator 117.

[0123] Figure 6Shows an additional alternative of the generator 117. Figure 6 The view in [reference] does not show the turbine, however the structure shown is connected to the turbine. In this example, the turbine causes the conductive plate 600 to rotate about the axis of rotation 404. In the presence of a magnetic field, this causes eddy currents, which then generate an electromagnetic field, which can then be picked up by the stationary pick-up coil 502. Figure 6 The example shown has the disadvantage that the frequency of the electromagnetic radiation is set by the rotational speed of the turbine. However, Figure 6 The example shown has the great advantage of its mechanical simplicity. The design is very robust and does not require any additional electrical components in the rotor.

[0124] Optional or supplementary MRI coils (such as surface coils, head coils or other dedicated coils) are almost always used in magnetic resonance imaging. Although the handling of the coils is simple, the connecting cables are bulky. The reason for this is that high-frequency potential wells are required to make the cables safe for the patient.

[0125] To avoid bulky cables, purely wireless technologies have been proposed. Powering with a battery is feasible, but makes the coil heavy and / or dangerous. Wireless power transfer at the Larmor frequency or higher frequencies does not seem feasible, while at lower frequencies it makes the coil heavy and stiff. There are also concepts of powering the coil through a thin cable using high-frequency signals. These concepts suffer from low efficiency and thus unwanted coil heating.

[0126] An embodiment can provide means for transferring power to a magnetic resonance imaging coil (i.e., an MRI receiving coil) using compressed air or other pressurized gas. Some kind of turbine can be used to expand the air at the coil. A generator using the main magnetic field as the stator field can be attached (or integrated) to the turbine. Thus, ferromagnetic materials may not be required, and for a 16-element coil, the turbine / generator unit is expected to have a mass of less than 2 grams and a volume of 1 cm 3 . At atmospheric pressure, the air flow is expected to be about 0.5 l / s. This means that the compressed air flow at 10 atmospheres is only 50 ml / s. This mass flow can be very close to the breathing action of a human, so it is feasible to suppress the noise emission to a very low level. This gas flow can provide an effective cooling means to keep the coil always accurately at the ambient temperature.

[0127] The energy generated by the adiabatic expansion of a diatomic gas is:

[0128]

[0129] (n: amount of substance in moles of the molecule; R: universal gas constant; T: absolute temperature; P: pressure).

[0130] At a pressure ratio of 10, to generate 50 W of power at room temperature, a flux of approximately 0.02 mol / s is required, i.e., an exhaust flow of approximately 0.5 l / s (similar to the human breathing motion). Even considering efficiency, 50 W can be sufficient to power a 16-element coil. During expansion, the gas flow cools significantly. The temperature starts at approximately 300 K and ends at roughly 150 K. However, when considering all losses, there should be sufficient available power to return the gas to 300 K. There may be no risk to the patient, and the problem of coil heating is also solved. However, it may be beneficial to use only fully dry air to avoid turbine blockage.

[0131] Typical material strengths of common engineering materials allow a turbine blade tip speed of 100 m / s while still having sufficient safety margins. In the case of a 1 cm turbine diameter, this translates to a frequency of 3.1 kHz. A single loop coil with an area of 1 cm 2 mounted on the turbine can generate a peak voltage of 2.9 V in an external field of 1.5 T. Assuming a 1 mm 2 copper area, the coil resistance can be approximately 5 mΩ, and thus the short-circuit power is approximately 800 W. This can be more than the available power from the turbine. Therefore, it may be possible to extract energy with very high efficiency and using very low copper mass (<400 mg) by reducing the current. The copper can be distributed over more windings and / or coils to regulate the voltage and smooth the waveform.

[0132] An efficient fast-rotating turbine design can be used. An inexpensive example is a simple Tesla turbine, which has a relatively low efficiency compared to multi-stage axial turbines. An axial design with blades can provide a good compromise between efficiency and simplicity. In such a design, one or more coils (conductive loops) can be easily wound around the rotor or the blades of the rotor.

[0133] It is expected that this type of power supply will not negatively affect MR imaging. The rotor and the turbine housing can be made of non-magnetic materials such as high-strength plastics and ceramics. The current in the coil can be no higher than the usual feed current in classical power supplies. Therefore, the image may not be distorted more than in the current design.

[0134] The generator can be constructed such that the acoustic noise generated in this design has a very high frequency. High-frequency acoustic noise can be absorbed quite well using fiber / cloth or using a muffler. The turbine can be packaged in a fiber material, and all the exhaust air can pass through a dense fiber material. It is feasible to have some pressure drop through the material and still generate sufficient power.

[0135] There may be many available quick-lock pressurized air connectors (e.g., from Festo). The outer diameter of the hose can be somewhere between 3 mm and 6 mm. The signal can be transmitted through a fiber optic, and the fiber penetrates the hose at the end of the hose and enters a separate standard connector. If an attempt is made to unplug the plug to avoid generating a sound, a sensor system can be used to depressurize the hose.

[0136] Exhaust can be handled by allowing it to escape from multiple pieces of cloth covering holes distributed on the surface of the magnetic resonance imaging coil.

[0137] There is a trend towards more flexible and higher-channel MRI coils. However, as mentioned above, connection cables with RF traps are still bulky and stiff and require careful routing for RF safety. Turbines can operate in the audio frequency band, thus directly generating unwanted noise at the patient. Here, whistles and similar oscillators (acoustic resonators) operating with pressurized air at ultrasonic frequencies are proposed as alternative generators. Voltage can be induced in a conductive membrane oscillating in an acoustic cavity by a B0 field, and the oscillation is excited by an air flow, for example similar to blowing a whistle on a blade of grass. In addition to being inaudible, such devices can avoid any macroscopically moving parts, bearings, and the strict tolerances of the turbine concept. This makes them cheaper and more robust. A favorable cooling concept that provides exactly as much local cooling power as the electrical energy dissipated locally by all loads is maintained, thus solving the cooling problem in the MR coil.

[0138] The problems of power supply and cooling of magnetic resonance imaging antennas increase with the number of channels (the number of coil elements) because each preamplification / digitization / detuning unit increases the dissipated energy. The above air turbine proposal solves this problem well because the law of conservation of energy requires that all the energy generated by the thermodynamic engine during adiabatic expansion reduces the internal energy of the air. Thus, neglecting the small Joule-Thomson effect, the cooling "energy" provided by the air is exactly the same as the heat dissipated by all the connected electrical loads (turbine bearings, generators) during energy conversion.

[0139] The main problem with the turbine solution is that unless it is very small (rotor diameter less than 2 mm), it is restricted to the audio frequency band, thus generating an unwanted high-pitched monotonic noise. Typical material strengths in common engineering materials allow a turbine blade tip speed of 100 m / s. At a turbine diameter of 1 cm, this translates to a frequency of 3.1 kHz. The turbine diameter can still be reduced by two-thirds, resulting in close to 10 kHz, but it is difficult to reach 25 kHz and still achieve efficient energy conversion. However, such a frequency is beneficial because it can be inaudible and also safe for the human auditory system.

[0140] In magnetic resonance imaging antennas, MR signals from each coil element (or channel) are pre-amplified, digitized, and converted to optical signals in many current MR coils, but this and coil detuning can consume a significant amount of power provided electrically. The corresponding electrical coil connections pose RF safety issues and can therefore be carefully routed (not too close to the patient or body coil wires, preferably parallel to the B0 field) and equipped with thick insulation layers and RF traps, making them bulky and inflexible.

[0141] Typically, an example generator includes an acoustic resonator excited by an air flow and a conductive element oscillating within the resonator, having the effect of inducing a voltage by means of an external magnetic field.

[0142] In particular, whistles operated with pressurized air at ultrasonic frequencies are proposed for such generators. Ultrasonic operation makes them inaudible, and this concept avoids any rotating or macroscopically moving parts, corresponding bearings, and the strict tolerances of the turbine concept. This makes them cheaper and more robust. A favorable cooling concept that provides as much local cooling power as the electrical energy dissipated locally by all loads is maintained.

[0143] As described above, the energy generated by the adiabatic expansion of a diatomic gas (such as air with 79% N2 and 20% O2) is given. At a pressure ratio of 10, to generate 50 W of thermodynamic power at room temperature, a flux of approximately 0.02 mol / s is required, i.e., an exhaust flow of approximately 0.5 l / s (similar to a human breathing action). The total power consumption of a 16-channel coil array with RXE can be approximately 16 W, such that 50 W can be sufficient to power such coils, also considering typical conversion losses.

[0144] Several different types of generators using resonant cavities can be constructed. They can also have different types of mechanical components that move mechanically in response to resonances in the resonant cavity.

[0145] 1. The first type of generator is the "blade of grass" or reed-type resonator.

[0146] In a first example, a generator similar to a whistle represented by a blade of grass is proposed, as shown in the following Figure 7As shown. Here, the blade (mechanical component 702) is made of a material with high tensile strength, high yield strength, conductive, and non-ferromagnetic properties (e.g., copper-beryllium or copper-cobalt-beryllium as used for conductive springs). Its long axis is oriented perpendicular to the static magnetic field provided by the MR system. The air flow is oriented parallel to the magnetic field and excites the transverse vibration of the blade. This induces a voltage along the long axis of the blade, which is used to drive an AC current. The blade is designed to have its fundamental resonance at approximately f0 = 25 kHz. To limit acoustic losses, it can be located in a cavity with a matching acoustic resonance. The width l of the cavity can be:

[0147]

[0148] where c = speed of sound, which gives a width of approximately 7 mm, which is quite small for use in an MR coil.

[0149] The resonance frequency of the blade itself can be controlled by appropriately selecting its length, thickness, and material properties similar to a guitar string. The fundamental resonance frequency is given by:

[0150]

[0151] For a blade length and cross-section d = 1 cm and A = 1 cm * 50 μm, the tensile force F in the blade, the density and elastic modulus of copper-beryllium ρ = 8250 kg / m 3 and E = 130 GPa, the resonance at 25 kHz will use the following strain

[0152]

[0153] of only 1.6%, while the elastic range in CuBe and CuCoBe is up to 20% in range depending on the alloy used. It seems most advantageous to select CuCo0.5Be because of its combination of high yield stress and high conductivity.

[0154] The cross-section of the blade can be shaped similar to an aircraft wing profile to minimize turbulence. The blade can also be designed such that one end (the windward or leeward end) is thicker than the other end, or reinforced with a steel having an even higher elastic modulus, making the corresponding side so stiff that it does not oscillate significantly. This can result in additional torsion of the blade and a higher resonance frequency.

[0155] Figure 7Another example of the generator 117 is shown. In this example, there is again an inlet 200 and an outlet 202 for the pressurized gas. In this example, there is a resonance cavity 700. The passage of the pressurized gas causes a resonance that causes the mechanical member 702 to oscillate. This mechanical vibration of the mechanical member 702 is used to generate electrical energy. The mechanical member 702 is similar to a blade of grass or a reed. The oscillating blade 702 is fixed at the top and bottom of the cavity and is designed to have a resonance that matches the resonance of the cavity. The air flow excites this resonance and causes a voltage U by means of the main field B0 ind .

[0156] Alternatively, the generator can be designed as a tube or a whistle or a variant thereof as shown below Figure 8 . Figure 8 An alternative structure for the resonance cavity 700 is shown. In this structure, the generator 117 is constructed similar to an organ pipe. In this design, pressurization causes a resonant oscillation of the air column in the tube, which can be transferred to the movement of a membrane located at the position of the maximum amplitude of the air movement. The external field causes a voltage U ind . The generator can also be designed such that the membrane is located at other positions within it, for example, more towards its upper end or at its upper end

[0157] Power generation:

[0158] For the grass blade type, the amplitude of the blade when oscillating in its fundamental mode is:[[]]

[0159]

[0160] This gives the induced voltage:[[]]

[0161]

[0162] Thus, the maximum voltage is For a blade length of d = 1 cm, a frequency f0 = 25 kHz, a field B0 = 1.5 T, and an expected lateral oscillation amplitude of a0 = 1 mm, this amounts to a peak voltage of 1.5 V

[0163] The resistance of the blade can be estimated by the following formula:[[]]

[0164]

[0165] And for d = 1 cm, A = 1 cm * 50 μm, and ρ = 8.5E - 8 Ωm for CuBe2, R = 1.7 mΩ, resulting in a theoretical short - circuit power of over 660 W. This is far greater than the available thermodynamic power of a reasonable air flow and far less than the power required electrically. To obtain 16 W of electrical power, an AC current of approximately I = 16 W / 1.5 V * sqrt2 = 16 A through the blades is needed, resulting in a heat dissipation of 0.45 W, which can be easily cooled by a cold air flow.

[0166] During adiabatic expansion, the air cools significantly. If a pressure ratio of 10 is provided at approximately 300 K, it cools to approximately 150 K. But when all losses are considered, there is fully sufficient available power to bring the air back to 300 K. Thus, in the case of an MR coil, since the air is released at ambient temperature, there is no risk to the patient.

[0167] Generally, it is recommended to locate the generator at those components that require the most cooling (CPU, GPU, or RXE in the case of an MR coil), and provide an air duct that protrudes together with the electrical wires to power and cool the locally adjacent components.

[0168] This type of power can be MR - imaging - compatible. Assuming a square loop of 1 cm size, the required AC current of approximately I = 16 A through the blade loop can generate an alternating bipolar magnetic field with the following intensity at its center:

[0169]

[0170] It can be shielded to 0.7% of its original value with a copper shell of approximately 2 mm ( = 5 times the skin depth) thickness. Additionally, the residual accumulated phase of adjacent spins during MR imaging can be re - phased within 1 / f0 = 40 μs, i.e., usually within a few sampling points. This residual sinusoidal phase modulation across individual k - space lines is not phase - locked, resulting in a locally increased virtual noise level.

[0171] Trace water and CO2 in the feed air can be removed to avoid any icing of components in the generator by water ice or dry ice. Methods known in the art, for example, the techniques used in industrial liquid air production, can be used for this purpose.

[0172] Alternatively or additionally, the generator can be flushed periodically with low - pressure air for a short period to remove any ice.

[0173] Figure 9 is shown Figure 7Another example of the generator 117 in the depicted style. In this example, there is a portion on the side of the resonance cavity 700 and also along the conductive path 900 of the mechanical member 702. As the acoustic resonance builds up in the resonance cavity 700, the mechanical member 702 can oscillate back and forth, and the area enclosed by the conductive path 900 can change. This can result in a current in the conductive path 900. In this example, there is a rectifying circuit 902 for supplying electrical power to the RF system. The rectifying circuit 902 is not shown in all examples, but it should be understood that if an alternating current is supplied by the generator 117 within the generator or within the RF circuit, there may be a rectifying circuit 902.

[0174] Figure 10 Another example of the generator 117 is shown. Figure 10 The example in Figure 9 is similar to the example depicted in

[0175] except that the conductive path 900 is connected to the switching circuit 500. The mechanical member in this example includes a conductive portion 1000 having the conductive path 900, which is entirely located on the mechanical member 702. The conductive portion 1000 is attached to the resonance cavity 700 by an elastic element 1002. Such a design can be achieved, for example, by forming the mechanical member 702 as a metallic or mostly metallic blade (conductive portion 1000) that can be suspended by an elastic material (elastic element 1002) with high durability. The acoustic resonance in the resonance cavity 700 can cause the mechanical member 702 to vibrate. For some designs, the elastic element 1002 can enable the conductive portion 1000 to vibrate using rotational and / or torsional components. This can facilitate the generation of electrical energy. Figure 11 Another example of the generator 117 is shown. In this example, the mechanical member 702' is at least partially made of a conductive material. The mechanical member 702' can be made of a conductive material or a partially conductive material, for example. As the acoustic resonance builds up in the resonance cavity 700, the back-and-forth vibration of the mechanical member 702' causes eddy currents within the conductive portion of the mechanical member 702'. This results in an electromagnetic field that can be picked up by the stationary pickup coil 502. In this case, the stationary pickup coil is the conductive path 900. Figure 11The example of [[ID=]] functions when the mechanical member 702' has rotational or torsional movement. To obtain such torsional movement, the mechanical member 702' is connected at the top and is connected at only one point at the bottom 1100. This enables parts of the mechanical member 702' to swing back and forth in a rotational or quasi-rotational or torsional movement manner.

[0176] Although the invention has been illustrated and described in detail in the drawings and foregoing description, such illustration and description are to be considered illustrative or exemplary and not restrictive; the invention is not limited to the disclosed embodiments.

[0177] Those skilled in the art will, by studying the drawings, the description and the claims, be able to understand and realize other variations of the disclosed embodiments when practicing the claimed invention. In the claims, the word "comprising" does not exclude other elements or steps, and the words "a" or "an" do not exclude a plurality. A single processor or other unit may fulfill the functions of several items recited in the claims. Although specific elements are recited in mutually different dependent claims, this does not indicate that a combination of these elements cannot be used to advantage. A computer program may be stored and / or distributed on a suitable medium, such as an optical storage medium or a solid-state medium provided together with or as part of other hardware, but the computer program may also be distributed in other forms, such as via the Internet or other wired or wireless telecommunication systems. Any reference signs in the claims should not be construed as limiting the scope.

Claims

1. A magnetic resonance imaging antenna (114), comprising: One or more coil elements (115); A radio frequency system (116) coupled to the one or more coil elements; A gas inlet (200) configured to receive pressurized gas; A gas outlet (202) configured to discharge the pressurized gas; A generator (117) configured to convert mechanical energy generated by the pressurized gas flowing from the gas inlet to the gas outlet into electrical energy in the presence of an external magnetic field, wherein the generator is configured to power the magnetic resonance imaging antenna with the electrical energy, wherein the generator includes a turbine (400) configured to be rotated by the pressurized gas flowing from the gas inlet to the gas outlet, wherein the turbine is configured to rotate a conductive element (600) formed as a conductive loop, wherein the conductive element is configured to generate electrical energy when rotated in the external magnetic field, and wherein the generator includes a switching circuit (500) in series with the conductive loop, wherein the switching circuit is configured to be powered by the conductive loop, wherein the switching circuit is configured to electrically disconnect and electrically close the conductive loop at a predetermined frequency, and wherein the generator further includes one or more stationary pickup coils configured to receive electrical energy switched at the predetermined frequency, and wherein the at least one stationary pickup coil is configured to supply the electrical energy to the radio frequency system.

2. The magnetic resonance imaging antenna according to claim 1, wherein, The turbine includes vanes (402), and wherein the conductive loop is attached to at least two of the vanes.

3. The magnetic resonance imaging antenna according to claim 1, wherein The turbine has a rotating shaft (404), wherein the conductive element (600) is asymmetric with respect to the rotating shaft, and wherein the generator further includes one or more stationary pickup coils configured to receive electrical energy caused by the rotation of the conductive element, and wherein the at least one stationary pickup coil is configured to supply the electrical energy to the radio frequency system.

4. The magnetic resonance imaging antenna according to any one of claims 1 to 3, wherein, Any one of the following exists: The turbine includes a rotor (401) having a diameter less than 2 mm or less than 1 mm; The turbine is configured to have a rotation rate of at least 1.2 million revolutions per minute; and A combination of the above.

5. A magnetic resonance imaging antenna (114), comprising: One or more coil elements (115); A radio frequency system (116) coupled to the one or more coil elements; A gas inlet (200) configured to receive pressurized gas; A gas outlet (202) configured to discharge the pressurized gas; A generator (117) configured to convert mechanical energy generated by the pressurized gas flowing from the gas inlet to the gas outlet into electrical energy in the presence of an external magnetic field, wherein the generator is configured to power the magnetic resonance imaging antenna with the electrical energy, wherein the generator includes: A resonator (700) configured to generate an acoustic resonance in response to the conveyance of pressurized gas from the gas inlet to the gas outlet; Mechanical members (702, 702'), configured to vibrate in response to the acoustic resonance, wherein the mechanical members are suspended within the resonator; At least one conductive path (900) configured such that movement of the mechanical members causes the generation of the electrical energy in the external magnetic field.

6. The magnetic resonance imaging antenna according to claim 5, wherein, The resonator is a whistle tuned to an ultrasonic frequency.

7. The magnetic resonance imaging antenna according to claim 5 or 6, wherein The mechanical member (702') includes a conductive element configured to vibrate torsionally, wherein the at least one conductive path is one or more stationary pickup coils configured to receive electrical energy generated by the vibration of the conductive element, and wherein the at least one stationary pickup coil is configured to supply the electrical energy to the RF system.

8. The magnetic resonance imaging antenna according to claim 5 or 6, wherein Each conductive path in the at least one conductive path (900) is at least partially on the mechanical member.

9. The magnetic resonance imaging antenna according to claim 1 or 5, wherein The generator is arranged such that the pressurized gas conveyed from the gas inlet to the gas outlet cools the RF system.

10. The magnetic resonance imaging antenna according to claim 1 or 5, wherein There is any one of the following: The RF system includes a receiver coupled to at least a portion of the one or more coil elements; And The RF system includes a transmitter coupled to at least a portion of the one or more coil elements; A magnetic resonance imaging system includes an optical fiber communication system (125) configured to control the RF system; The magnetic resonance imaging system includes a wireless communication system configured to control the RF system; and A combination of the above.

11. A magnetic resonance imaging system (100), comprising a magnetic resonance imaging antenna (114) according to any one of the preceding claims, wherein, The magnetic resonance imaging system includes a main magnet (104), wherein the main magnet is configured to generate the external magnetic field, and wherein the magnetic resonance imaging system further includes a pressurized gas system (122) for supplying pressurized gas to the gas inlet (200) of the magnetic resonance imaging antenna.

12. The magnetic resonance imaging system according to claim 11, wherein, The magnetic resonance imaging system further includes: A memory (134) storing machine-executable instructions (140) and pulse sequence commands (142), the pulse sequence commands being configured to control the magnetic resonance imaging system to acquire magnetic resonance imaging data using the magnetic resonance imaging antenna; and A processor (130) for controlling the magnetic resonance imaging system, wherein execution of the machine-executable instructions causes the processor to: Acquire (300) the magnetic resonance imaging data by controlling the magnetic resonance imaging system using the pulse sequence commands; and Power the magnetic resonance imaging antenna (302) by controlling the pressurized gas system to supply the pressurized gas during the acquisition of the magnetic resonance imaging data.

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