CN107290697B - Magnetic resonance radio frequency coil and magnetic resonance system - Google Patents
Magnetic resonance radio frequency coil and magnetic resonance system Download PDFInfo
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- CN107290697B CN107290697B CN201710581577.XA CN201710581577A CN107290697B CN 107290697 B CN107290697 B CN 107290697B CN 201710581577 A CN201710581577 A CN 201710581577A CN 107290697 B CN107290697 B CN 107290697B
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
- G01R33/00—Arrangements or instruments for measuring magnetic variables
- G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
- G01R33/28—Details of apparatus provided for in groups G01R33/44 - G01R33/64
- G01R33/32—Excitation or detection systems, e.g. using radio frequency signals
- G01R33/34—Constructional details, e.g. resonators, specially adapted to MR
- G01R33/34084—Constructional details, e.g. resonators, specially adapted to MR implantable coils or coils being geometrically adaptable to the sample, e.g. flexible coils or coils comprising mutually movable parts
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
- G01R33/00—Arrangements or instruments for measuring magnetic variables
- G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
- G01R33/28—Details of apparatus provided for in groups G01R33/44 - G01R33/64
- G01R33/32—Excitation or detection systems, e.g. using radio frequency signals
- G01R33/36—Electrical details, e.g. matching or coupling of the coil to the receiver
- G01R33/3621—NMR receivers or demodulators, e.g. preamplifiers, means for frequency modulation of the MR signal using a digital down converter, means for analog to digital conversion [ADC] or for filtering or processing of the MR signal such as bandpass filtering, resampling, decimation or interpolation
Abstract
The invention provides a magnetic resonance radio frequency coil and a magnetic resonance system, the magnetic resonance radio frequency coil comprises: the radio frequency antenna is used for receiving radio frequency signals sent by an imaging object; the signal processing module is connected with the radio frequency antenna and used for processing the radio frequency signals received by the radio frequency antenna; the radio frequency antenna does not comprise a capacitance element, and is made of an elastic metal material or liquid metal which is made of a non-magnetic substance. The technical scheme of the invention can allow the radio frequency coil to deform to a certain extent under the condition of not influencing the sensitivity of the radio frequency coil, thereby keeping better image quality.
Description
Technical Field
The invention relates to the field of medical imaging, in particular to a magnetic resonance radio frequency coil and a magnetic resonance system.
Background
Nuclear Magnetic Resonance Imaging (NMRI), also known as spin Imaging (or MRI), uses the principle of Nuclear Magnetic Resonance to detect emitted electromagnetic waves by an external gradient Magnetic field according to different attenuations of the released energy in different structural environments inside a substance, and then draws a structural image inside the object.
The radio frequency coil is a very important coil in a magnetic resonance scanner, the radio frequency coil directly determines the imaging quality, and the performance of the radio frequency coil is set to a great extent when the radio frequency coil is delivered from a factory. In general, to obtain an image with a high signal-to-noise ratio by using an existing coil, it is necessary to increase the received tissue magnetic resonance signal and reduce the noise, and the amount of noise is related to the volume of the tissue contained in the coil, and the less the tissue is contained, the less the noise is. At the same time, the size of the tissue volume contained in the radio frequency coil also determines the H proton content involved in imaging. The rf coil should be as close to the scan area as possible to minimize the spacing between the scan areas, thereby increasing the strength of the received MR signal and reducing the received noise. Therefore, when the radio frequency coil is selected, the radio frequency coil which can be closely matched with a patient and has the smallest coverage on an anatomical part is selected according to the size of the anatomical part to be scanned.
However, due to the design limitation of the existing radio frequency coil, a certain deformation is required for attaching the imaging part, and the deformation affects the sensitivity of the radio frequency coil, thereby reducing the image quality.
Disclosure of Invention
The invention aims to provide a magnetic resonance radio frequency coil and a magnetic resonance system, and solves the problems that the sensitivity of the coil is influenced and the image quality is further influenced due to deformation of the radio frequency coil.
To solve the above problems, the present invention provides a magnetic resonance radio frequency coil, comprising: the radio frequency antenna is used for receiving radio frequency signals sent by an imaging object; the signal processing module is connected with the radio frequency antenna and used for processing the radio frequency signals received by the radio frequency antenna; the radio frequency antenna does not comprise a capacitance element, and is made of an elastic metal material or liquid metal which is made of a non-magnetic substance.
Preferably, the radio frequency antenna is a non-resonant radio frequency antenna.
Preferably, the radio frequency antenna further comprises a matching module, wherein the matching module is connected with the radio frequency antenna and is used for matching the radio frequency antenna with a back-end circuit of the matching module.
Preferably, the matching module is broadband matching.
Preferably, the magnetic resonance coil is adapted for use in a multi-nuclear magnetic resonance system, and is capable of imaging with at least one of the following atoms: phosphorus, sodium.
Preferably, the method further comprises the following steps: and the digitization module is used for digitizing the processed radio frequency signal and transmitting the signal to the back end. The transmission mode of the digital module is realized by at least one of the following modes: wired, optical, or wireless.
Preferably, the signal processing module is a direct sampling architecture, including: low noise amplifiers and filters.
Preferably, the signal processing module is in any one of the following forms: a superheterodyne receiver or a zero intermediate frequency receiver.
Preferably, the method further comprises the following steps: an energy transmission module for providing energy for the signal processing module and/or the digitization module, wherein the energy transmission module is realized by at least one of the following modes: portable power, direct current cable or wireless charging.
To solve the above problem, the present invention further provides a magnetic resonance system, including: such as the aforementioned radio frequency coil.
Compared with the prior art, the technical scheme of the invention provides the magnetic resonance radio-frequency coil and the magnetic resonance system, which can allow the radio-frequency coil to deform to a certain extent under the condition of not influencing the sensitivity of the radio-frequency coil, and keep better image quality.
Drawings
Figure 1 is a schematic structural diagram of a magnetic resonance system in accordance with some embodiments of the invention;
FIG. 2 is a schematic diagram of a circuit configuration of a magnetic resonance RF coil;
figure 3 is a schematic diagram of a magnetic resonance radio frequency coil configuration according to some embodiments of the present invention;
FIG. 4 is a block diagram of an analog signal processing module according to some embodiments of the invention;
FIG. 5 is a block diagram of an analog signal processing module according to some embodiments of the invention;
FIG. 6 is a block diagram of an analog signal processing module according to some embodiments of the invention;
figure 7 is a schematic diagram of a magnetic resonance radio frequency coil configuration according to some embodiments of the present invention.
Detailed Description
In order to make the aforementioned objects, features and advantages of the present invention comprehensible, embodiments accompanied with figures are described in detail below. In the following description, specific details are set forth in order to provide a thorough understanding of the present invention. The invention can be implemented in a number of ways different from those described herein and similar generalizations can be made by those skilled in the art without departing from the spirit of the invention. Therefore, the present invention is not limited to the specific embodiments disclosed below.
As used in this application and the appended claims, the terms "a," "an," "the," and/or "the" are not intended to be inclusive in the singular, but rather are intended to be inclusive in the plural unless the context clearly dictates otherwise. In general, the terms "comprises" and "comprising" merely indicate that steps and elements are included which are explicitly identified, that the steps and elements do not form an exclusive list, and that a method or apparatus may include other steps or elements.
Fig. 1 is a schematic diagram of an mr system according to some embodiments of the present invention, and as shown in fig. 1, an mr system 100 generally includes a magnetic resonance housing having a main magnet 101 therein, where the main magnet 101 may be formed of superconducting coils for generating a main magnetic field, and in some cases, may also be a permanent magnet. The main magnet 101 may be used to generate a main magnetic field strength of 0.2 tesla, 0.5 tesla, 1.0 tesla, 1.5 tesla, 3.0 tesla, or higher. In magnetic resonance imaging, an imaging subject 150 is carried by the patient couch 106, and as the couch plate moves, the imaging subject 150 is moved into the region 105 where the magnetic field distribution of the main magnetic field is relatively uniform. Generally for a magnetic resonance system, as shown in fig. 1, the z direction of the spatial coordinate system (i.e. the coordinate system of the apparatus) is set to be the same as the axial direction of the gantry of the magnetic resonance system, the length direction of the patient is usually kept consistent with the z direction for imaging, the horizontal plane of the magnetic resonance system is set to be xz plane, the x direction is perpendicular to the z direction, and the y direction is perpendicular to both the x and z directions.
In magnetic resonance imaging, the pulse control unit 111 controls the radio frequency pulse generation unit 116 to generate a radio frequency pulse, and the radio frequency pulse is amplified by the amplifier, passes through the switch control unit 117, and is finally emitted by the radio frequency body coil 103 or the local coil 104 to perform radio frequency excitation on the imaging object 150. The imaging subject 150 generates corresponding radio frequency signals from resonance upon radio frequency excitation. When receiving the radio frequency signals generated by the imaging subject 150 according to the excitation, the radio frequency signals may be received by the body coil 103 or the local coil 104, there may be a plurality of radio frequency receiving links, and after the radio frequency signals are sent to the radio frequency receiving unit 118, the radio frequency signals are further sent to the image reconstruction unit 121 for image reconstruction, so as to form a magnetic resonance image.
The magnetic resonance system 100 also includes gradient coils 102 that may be used to spatially encode radio frequency signals in magnetic resonance imaging. The pulse control unit 111 controls the gradient signal generating unit 112 to generate gradient signals, which are generally divided into three mutually orthogonal directions: gradient signals in the x, y and z directions, which are different from each other, are amplified by gradient amplifiers (113, 114, 115) and emitted from the gradient coil 102, thereby generating a gradient magnetic field in the region 105.
The pulse control unit 111, the image reconstruction unit 121, the processor 122, the display unit 123, the input/output device 124, the storage unit 125 and the communication port 126 can perform data transmission through the communication bus 125, so as to realize the control of the magnetic resonance imaging process. The processor 122 may be composed of one or more processors. The display unit 123 may be a display provided to a user for displaying an image. The input/output device 124 may be a keyboard, a mouse, a control box, or the like, and supports input/output of the corresponding data stream. The storage unit 125 may be a Read Only Memory (ROM), a Random Access Memory (RAM), a hard disk, etc., and the storage unit 125 may be used to store various data files that need to be processed and/or used for communication, as well as possible program instructions executed by the processor 122. The communication port 105 may be implemented with other components such as: and the external equipment, the image acquisition equipment, the database, the external storage, the image processing workstation and the like are in data communication.
Fig. 2 is a schematic circuit structure diagram of a radio frequency coil, and referring to fig. 2, a radio frequency coil 200 includes a radio frequency antenna 201, where the radio frequency antenna 201 is used to acquire a radio frequency signal emitted by an imaging object 150, and due to a magnetic resonance principle, the radio frequency antenna 201 receives a magnetic resonance radio frequency signal of a fixed frequency band, for example, for a device with a main magnetic field strength of 1.5T, the radio frequency antenna 201 needs to be modulated to a resonant frequency of about 64MHz for signal reception, and for a device with a main magnetic field strength of 3T, the radio frequency antenna 201 needs to be modulated to a frequency of about 128MHz for signal reception. Typically, the rf antenna 201 will include a capacitive element (also referred to as a resonant capacitor) that, in conjunction with the resistance or inductance of the rf antenna or other elements, achieves the resonant frequency of the rf antenna 201.
The rear end of the rf antenna 201 may be provided with a matching module 202, the matching module may be formed by a matching capacitor, the matching module 202 is configured to implement impedance matching between the rf antenna 201 and the rear end circuit, and the impedance from the rear end to the rf antenna 201 is usually 50 Ohms.
The rf coil 200 further includes a phase shifter 203 at the rear end of the matching module 202 for adjusting the phase of the rf signal, and an amplifier 203 for amplifying the rf signal. Amplifier 203 has an associated matching block that typically causes the impedance to be 50Ohms as viewed from the front end of amplifier 204 to phase shifter 203. The amplifier 204 is connected to the back end of the amplifier via a coaxial line for introducing the radio frequency signal into the signal processing system of the magnetic resonance.
The radio frequency coil in the mode has the advantages that the transmission distance of the analog signals in the radio frequency link is long, and large noise loss is introduced. And because the radio frequency antenna is composed of an inductor and a capacitor, welding of related elements is required, and the deformation performance of the coil is limited due to the existence of welding, so that the radio frequency antenna is not suitable for being used in a magnetic resonance radio frequency coil, particularly a flexible coil. In addition, since the conventional method is provided with a capacitor with a fixed capacitance value, and the resonant frequency f of the radio frequency coil is 1/sqrt (lc), where C is the resonant capacitor and L is the resonant inductor, the radio frequency coil can only resonate at a fixed frequency, that is, only a single frequency radio frequency signal can be received. Although the radio frequency coil has a high Q value, when the radio frequency antenna deforms, the resonance frequency of the coil changes, the sensitivity of the coil is influenced, the strength of a received magnetic resonance radio frequency signal is further influenced, and the final image quality is influenced.
Fig. 3 is a schematic diagram of a magnetic resonance rf coil according to the present invention, and referring to fig. 3, the rf coil 300 includes: a radio frequency antenna 301, the radio frequency antenna 301 is used for collecting the radio frequency signal emitted by the imaging object 150. The rf antenna 301 does not employ capacitive elements so that the rf antenna does not resonate at a fixed frequency and the rf filling employs a non-resonant rf antenna. The rf antenna 301 can thus receive a wider range of rf frequencies, and the broadband resonant frequency can be 57-74MHz, as opposed to a narrow band that fixes the resonant frequency around, for example, 64 MHz. This frequency range makes the magnetic resonance coil suitable for use in a multi-nuclear magnetic resonance system for imaging a variety of atoms, such as phosphorus, sodium, and the like.
The radio frequency antenna 301 can be formed by using an elastic material or liquid metal, and the elastic metal material or the liquid metal is made of a non-magnetic substance, so that the coil antenna 301 can keep better elasticity, better fit with a scanning part of an imaging object, improve the radio frequency signal intensity and improve the image quality. Meanwhile, as the resonant frequency is broadband, the reliability of the radio frequency signal can still be ensured under the maximum deformation. The insensitive structure of the radio frequency coil can minimize the influence on the sensitivity of the coil when the radio frequency antenna deforms.
The signal matching module 302 is arranged at the rear end of the radio frequency antenna 301, and the broadband matching is performed on the rear end circuits of the radio frequency antenna 301 and the signal matching module 302, so that better noise matching can be obtained in a wider range.
The back end of the signal matching module 302 may be connected to an analog signal processing module 303, and the analog signal processing module 303 serves as an interface between the front-end rf antenna 301 and the back-end digitizing module 304, and may be configured to perform signal processing on the rf analog signal received by the rf antenna 301, for example, amplification, filtering, phase shifting, notching, and the like of the analog signal.
In some embodiments, the analog signal processing module 303 may employ a radio frequency signal direct sampling architecture. Referring to fig. 4, which is a circuit diagram of an analog signal processing module according to the present invention, the analog signal processing module 400 includes a low noise amplifier 401 and a filter 402, and amplifies and filters a radio frequency signal. The low noise amplifier 401 is used as the first stage of receiving the radio frequency signal, the gain of the low noise amplifier directly determines the noise coefficient of the receiving chain, and a low noise amplifying circuit with high gain can be adopted. This direct sampling architecture reduces the use of analog devices, and the performance of the direct sampling architecture depends on the speed and number of bits of the ADC.
In some implementations, the circuitry of the analog signal processing module 303 may also use a mixer, with the receive chain architecture configured as a superheterodyne receiver. Referring to fig. 5, it is a circuit structure diagram of an analog signal processing module according to the present invention. The analog signal processing module 500 may include a low noise amplifier 501, a down converter 502, a local oscillator 503, and a channel selection filter 504. The radio frequency signal is linearly amplified by the low noise amplifier 501 and then mixed with the local oscillation signal, and the frequency is down-converted into a fixed intermediate frequency signal, and then the fixed intermediate frequency signal is filtered and input into the ADC for sampling. The main problem is that image frequency interference is generated.
In some embodiments, the receive chain architecture may also be set to a zero intermediate frequency receiver by the arrangement of the circuitry of the analog signal processing module 303. Referring to fig. 6, it is a circuit structure diagram of another analog signal processing module according to the present invention. The analog signal processing module 600 may include a low noise amplifier 601, a first downconverter 602, a first low pass filter 603, a second downconverter 604, a local oscillator 605, a 90-degree phase shift circuit 606, and a second low pass filter 607. The direct down-conversion receiver is also called as a zero intermediate frequency receiver, and is characterized in that the local oscillator frequency is equal to the carrier frequency, and the carrier frequency is zero, so that no image frequency exists, and image frequency interference can not exist naturally.
The back end of the analog signal processing module 303 may be connected to a digitizing module 304, and the digitizing module 304 may be configured to convert the analog signal into a digital signal (through an analog-to-digital converter (ADC)), and may perform preliminary processing on the digital signal, such as signal compression and signal adjustment. The digitizing module 304 may be connected to its back-end system by wire, fiber optics, or wirelessly.
The analog signal processing module 303 and the digitizing module 304 are controlled by a signal control module 305, and the signal control module 305 may include a clock signal circuit for providing a clock signal to control the ADC sampling or to turn off the rf coil to acquire the signal.
The analog signal processing module 303 and the digitizing module 304 are powered by a power transfer module 306, and the power transfer module 306 may include a battery assembly for supplying power (power) to the analog signal processing module 303 and the digitizing module 304, and in some cases to other modules of the rf coil 300. The energy transfer module 306 may use a dc cable or wireless charging to power/charge the battery.
In some embodiments, as shown in fig. 7, the rear end of the rf antenna 701 may be directly connected to the digital signal processing module 702, and the digital signal processing module 702 may include an analog-to-digital acquisition module, which converts an analog signal acquired by the rf antenna 701 into a digital signal and then directly processes the digital signal, for example, perform signal amplification, frequency conversion, filtering, notching, and the like. The process of analog signal processing is not needed, the arrangement of related circuit devices is omitted, the space of the radio frequency coil is saved, the design of the radio frequency coil is more diversified, and the radio frequency coil is not bound by some electronic devices.
The technical scheme of the invention provides the magnetic resonance radio frequency coil and the magnetic resonance system, which can allow the radio frequency coil to deform to a certain extent under the condition of not influencing the sensitivity of the radio frequency coil, and keep better image quality.
Although the present invention has been described with reference to the preferred embodiments, it is not intended to limit the present invention, and those skilled in the art can make variations and modifications of the present invention without departing from the spirit and scope of the present invention by using the methods and technical contents disclosed above.
Also, this application uses specific language to describe embodiments of the application. Reference throughout this specification to "one embodiment," "an embodiment," and/or "some embodiments" means that a particular feature, structure, or characteristic described in connection with at least one embodiment of the present application is included in at least one embodiment of the present application. Therefore, it is emphasized and should be appreciated that two or more references to "an embodiment" or "one embodiment" or "an alternative embodiment" in various places throughout this specification are not necessarily all referring to the same embodiment. Furthermore, some features, structures, or characteristics of one or more embodiments of the present application may be combined as appropriate.
Similarly, it should be noted that in the preceding description of embodiments of the application, various features are sometimes grouped together in a single embodiment, figure, or description thereof for the purpose of streamlining the disclosure aiding in the understanding of one or more of the embodiments. This method of disclosure, however, is not intended to require more features than are expressly recited in the claims. Indeed, the embodiments may be characterized as having less than all of the features of a single embodiment disclosed above.
Numerals describing the number of components, attributes, etc. are used in some embodiments, it being understood that such numerals used in the description of the embodiments are modified in some instances by the use of the modifier "about", "approximately" or "substantially". Unless otherwise indicated, "about", "approximately" or "substantially" indicates that the number allows a variation of ± 20%. Accordingly, in some embodiments, the numerical parameters used in the specification and claims are approximations that may vary depending upon the desired properties of the individual embodiments. In some embodiments, the numerical parameter should take into account the specified significant digits and employ a general digit preserving approach. Notwithstanding that the numerical ranges and parameters setting forth the broad scope of the range are approximations, in the specific examples, such numerical values are set forth as precisely as possible within the scope of the application.
The entire contents of each patent, patent application publication, and other material cited in this application, such as articles, books, specifications, publications, documents, and the like, are hereby incorporated by reference into this application. Except where the application is filed in a manner inconsistent or contrary to the present disclosure, and except where the claim is filed in its broadest scope (whether present or later appended to the application) as well. It is noted that the descriptions, definitions and/or use of terms in this application shall control if they are inconsistent or contrary to the statements and/or uses of the present application in the material attached to this application.
Finally, it should be understood that the embodiments described herein are merely illustrative of the principles of the embodiments of the present application. Other variations are also possible within the scope of the present application. Thus, by way of example, and not limitation, alternative configurations of the embodiments of the present application can be viewed as being consistent with the teachings of the present application. Accordingly, the embodiments of the present application are not limited to only those embodiments explicitly described and depicted herein.
Claims (7)
1. A magnetic resonance radio frequency coil, comprising:
the radio frequency antenna is used for receiving radio frequency signals sent by an imaging object;
the signal processing module is connected with the radio frequency antenna and used for processing the radio frequency signals received by the radio frequency antenna;
the radio frequency antenna does not comprise a capacitance element, and is made of an elastic metal material or liquid metal, and the elastic metal material or the liquid metal is made of a non-magnetic substance;
the signal processing module comprises a signal matching module, an analog signal processing module and a digitization module;
the signal matching module is connected with the rear end of the radio frequency antenna to perform noise matching;
the analog signal processing module is connected with the rear end of the signal matching module so as to process the radio frequency analog signal received by the radio frequency antenna;
the digital module is connected with the rear end of the analog signal processing module and is used for converting an analog signal into a digital signal;
analog signal processing module includes low noise amplifier, first down converter, first low pass filter, second down converter, local oscillator, 90 degrees phase shift circuit and second low pass filter, low noise amplifier connects first down converter and second down converter simultaneously, first down converter is connected first low pass filter, second low pass filter is connected to the second down converter, the local oscillator is connected simultaneously the second down converter with 90 degrees phase shift circuit, just 90 degrees phase shift circuit's output is connected to first down converter.
2. The magnetic resonance radio frequency coil of claim 1, wherein the radio frequency antenna is a non-resonant radio frequency antenna.
3. The magnetic resonance radio frequency coil of claim 1, wherein the signal matching module is broadband matching.
4. The magnetic resonance radio frequency coil of claim 2, wherein the magnetic resonance radio frequency coil is adapted for use in a multi-nuclear magnetic resonance system for imaging with at least one of the following atoms: phosphorus, sodium.
5. The magnetic resonance radio frequency coil according to claim 1, wherein the transmission mode of the digitizing module is realized by at least one of: wired, optical, or wireless.
6. The magnetic resonance radio frequency coil as set forth in claim 1, further including: an energy transmission module for providing energy for the analog signal processing module and/or the digitization module, wherein the energy transmission module is realized by at least one of the following modes: portable power, direct current cable or wireless charging.
7. A magnetic resonance system, comprising: the magnetic resonance radio frequency coil as set forth in any one of claims 1-6.
Priority Applications (7)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201710581577.XA CN107290697B (en) | 2017-07-17 | 2017-07-17 | Magnetic resonance radio frequency coil and magnetic resonance system |
| US15/856,058 US10545204B2 (en) | 2017-07-17 | 2017-12-28 | Non-resonant magnetic resonance coil and magnetic resonance imaging system using the same |
| EP17210845.8A EP3432017A1 (en) | 2017-07-17 | 2017-12-28 | Non-resonant magnetic resonance rf coil and magnetic resonance imaging system |
| PCT/CN2017/119389 WO2019015258A1 (en) | 2017-07-17 | 2017-12-28 | Magnetic resonance coil and magnetic resonance imaging system using the same |
| US16/750,013 US10838027B2 (en) | 2017-07-17 | 2020-01-23 | Non-resonant magnetic resonance coil and magnetic resonance imaging system using the same |
| US17/098,502 US11221383B2 (en) | 2017-07-17 | 2020-11-16 | Non-resonant magnetic resonance coil and magnetic resonance imaging system using the same |
| US17/647,595 US11821967B2 (en) | 2017-07-17 | 2022-01-10 | Non-resonant magnetic resonance coil and magnetic resonance imaging system using the same |
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| CN201710581577.XA CN107290697B (en) | 2017-07-17 | 2017-07-17 | Magnetic resonance radio frequency coil and magnetic resonance system |
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| CN107290697B true CN107290697B (en) | 2020-12-04 |
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| US10545204B2 (en) | 2017-07-17 | 2020-01-28 | Shanghai United Imaging Healthcare Co., Ltd. | Non-resonant magnetic resonance coil and magnetic resonance imaging system using the same |
| US11221383B2 (en) | 2017-07-17 | 2022-01-11 | Shanghai United Imaging Healthcare Co., Ltd. | Non-resonant magnetic resonance coil and magnetic resonance imaging system using the same |
| US10969447B2 (en) * | 2017-11-22 | 2021-04-06 | General Electric Company | Flexible radio frequency coil array with detachable straps for MR imaging |
| CN113933770B (en) * | 2021-11-25 | 2022-06-28 | 浙江大学 | Component layout method and system based on radio frequency emission surface coil and coil |
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| An easily constructed, tuning free, ultra-broadband probe for NMR;NURPHREE D. 等;《JOURNAL OF MAGNETIC RESONANCE 》;20070901;第188卷(第1期);第160-167页 * |
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