CN107526051B - Magnetic resonance radio frequency coil receiving circuit, radio frequency coil and magnetic resonance system - Google Patents
Magnetic resonance radio frequency coil receiving circuit, radio frequency coil and magnetic resonance system Download PDFInfo
- Publication number
- CN107526051B CN107526051B CN201710582372.3A CN201710582372A CN107526051B CN 107526051 B CN107526051 B CN 107526051B CN 201710582372 A CN201710582372 A CN 201710582372A CN 107526051 B CN107526051 B CN 107526051B
- Authority
- CN
- China
- Prior art keywords
- amplifier
- radio frequency
- magnetic resonance
- coil
- signal
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Active
Links
Images
Classifications
-
- 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
-
- 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
-
- 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
Landscapes
- Physics & Mathematics (AREA)
- Condensed Matter Physics & Semiconductors (AREA)
- General Physics & Mathematics (AREA)
- Magnetic Resonance Imaging Apparatus (AREA)
Abstract
The invention provides a magnetic resonance frequency coil receiving circuit, a radio frequency coil and a magnetic resonance system, wherein the magnetic resonance frequency coil receiving circuit comprises: an amplifier for amplifying the received magnetic resonance signal of the imaging subject; the adjustable element is matched with the amplifier and used for adjusting the input impedance of the amplifier, and the input impedance of the amplifier can be adjusted to a pure real part through the adjustable element; the adjustable element is a capacitive element and/or an inductive element. According to the technical scheme, the input impedance of the amplifier can be adjusted to be a pure real part by adjusting the adjustable element, so that the transmission loss of signals in a circuit is reduced, and the signal-to-noise ratio of the signals is improved.
Description
Technical Field
The invention relates to the field of medical imaging, in particular to a magnetic resonance radio frequency coil receiving circuit, a 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.
The receiving circuit of the radio frequency coil generally has large signal loss due to mismatching between circuits, so that the signal-to-noise ratio of the received magnetic resonance radio frequency signal is low, and the image quality is greatly influenced.
Disclosure of Invention
The invention aims to solve the problem of providing a magnetic resonance radio frequency coil receiving circuit, a radio frequency coil and a magnetic resonance system, and solves the problem of large transmission loss in the existing magnetic resonance radio frequency receiving circuit.
To solve the above problem, a signal receiving circuit of a magnetic resonance radio frequency coil includes: an amplifier for amplifying the received magnetic resonance signal of the imaging subject; the adjustable element is matched with the amplifier and used for adjusting the input impedance of the amplifier, and the input impedance of the amplifier can be adjusted to a pure real part through the adjustable element; the adjustable element is a capacitive element and/or an inductive element.
Preferably, the amplifier includes a signal input port, a signal output port, a bias circuit port and a power distribution port.
Preferably, the adjustable element is provided at an input of the amplifier.
Preferably, the adjustable element is a capacitor element, and the capacitor element is connected to the input end of the amplifier after being connected in parallel with a resistor.
Preferably, the adjustable element is two parallel capacitive elements, and the two parallel capacitive elements are connected to the input end of the amplifier.
Preferably, the method further comprises the following steps: the matching module is arranged between the coil unit and the amplifier and used for realizing impedance matching; and the analog-to-digital conversion module is connected to the rear end of the amplifier and is used for converting the analog signal into a digital signal.
In order to solve the above problem, the present invention further provides a radio frequency coil, including: one or several coil units for receiving magnetic resonance signals of an imaging subject; further comprising: the signal receiving circuit is configured to perform signal processing on the received magnetic resonance signal.
Preferably, the radio frequency coil is a radio frequency body coil or a local coil.
Preferably, the local coil includes a coil array formed by the plurality of coil units.
To solve the above problem, the present invention further provides a magnetic resonance system, including: the aforementioned radio frequency coil.
Compared with the prior art, the technical scheme of the invention provides the magnetic resonance radio frequency coil receiving circuit, the radio frequency coil and the magnetic resonance system, the input impedance of the amplifier can be adjusted to be a pure real part by adjusting the adjustable element, the transmission loss of signals in the circuit is reduced, and the signal-to-noise ratio of the signals is improved.
Drawings
Figure 1 is a schematic structural diagram of a magnetic resonance system in accordance with some embodiments of the invention;
figure 2 is a schematic structural view of a magnetic resonance radio frequency coil according to some embodiments of the present invention;
figure 3 is a schematic diagram of the structure of the magnetic resonance radio frequency coil amplification circuit of some embodiments of the present invention;
fig. 4 is a schematic diagram of a two-terminal architecture.
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 diagram of a magnetic resonance radio frequency coil according to the present invention, and as shown in fig. 2, the radio frequency coil includes a coil unit 201 and a signal receiving circuit 202. In some embodiments, the radio frequency coil may be a radio frequency body coil having a birdcage configuration disposed outside of an imaging subject (e.g., a human body) inside a gantry of a magnetic resonance system. In some embodiments, the radio frequency coil may be a local coil, which is a radio frequency coil covering a part of the human body, such as a head coil, a wrist coil, a shoulder coil, a spine coil, a flexible coil, a foot coil. The coil unit 201 is used to receive magnetic resonance signals emitted by the imaging subject, and the coil unit 201 may be a single channel coil, for example, a coil having only one loop. In other embodiments, the coil unit 201 may be a coil array of multi-channel radio frequency coils, for example, the number of channels may be 8, 16, 32, 64.
A signal receiving circuit 202 is connected to a rear end of the coil unit 201, and the signal receiving circuit 202 is configured to perform signal processing on the magnetic resonance signal received by the coil unit 201. The signal processing herein may include amplifying, filtering, notching, frequency converting, analog-to-digital converting, etc. the signal.
The signal receiving circuit 202 may include a matching module 2021, an amplifier circuit 2022, and an analog-to-digital conversion module 2023. The matching module 2021 is disposed between the coil unit 201 and the amplifier circuit 2022, and is used for implementing impedance matching therebetween. The analog-to-digital conversion module 2023 is connected to the rear end of the amplifier circuit 2022, and is configured to convert an analog signal into a digital signal. The digital signal can be used as magnetic resonance original data to further carry out operations such as image reconstruction and the like, and a magnetic resonance image which can be finally used for diagnosis by a doctor is obtained.
Fig. 3 is a schematic diagram of an amplifier circuit 2022 of an mr rf coil according to the present invention. For this amplifier circuit, a radio frequency signal is input from the port IN and output from the port OUT.
The signal receiving circuit of the traditional magnetic resonance radio frequency coil adopts a design mode of a matching network and a low input impedance (generally 1-5 ohms) amplifier, and the design mode is to reduce the current in the coil and reduce the electromagnetic interference on the signal receiving circuit caused by the coupling current between the coil units under the condition of a multi-channel coil unit. The amplifier circuit of the present invention differs from conventional designs in that it can be an amplifier circuit that employs a high input impedance, which herein refers to an input impedance of greater than 500 ohms, greater than 1000 ohms, or greater than 2000 ohms.
When a High input impedance amplifier is used, it can be specifically realized by a Field Effect Transistor (FET) and/or a High Electron Mobility Transistor (HEMT).
As shown in FIG. 3, amplifier 301 may include four ports, port ①, port ②, port ③, and port ④, where port ② and port ④ are bypass ports for the amplifier 301 for power distribution or biasing, port ① of amplifier 301 is a signal input port, and port ③ is a signal output port.
An input end matching circuit 302 and a matching circuit 303 are arranged on the input end side of the amplifier 301, the matching circuit 302 comprises a resistor R1, a capacitor C1 and a capacitor C2, the matching circuit 303 comprises a resistor R2 and a capacitor C3. on the output end side of the amplifier 301, the matching circuit 305 comprises a resistor R4, a resistor R5 and a capacitor C6., the amplifier 301 is connected with a capacitor C4 at a port ② for power distribution, a bias circuit 304 is connected at the port ④ and comprises a resistor R3 and a capacitor C5., and the amplifier is used for amplifying a magnetic resonance signal received by the coil unit 201.
According to the two-port principle, referring to fig. 4, for a two-port network (input port is port 1, output port is port 2), the impedance analysis of its ports satisfies the following formula:
wherein V1 represents the input terminal voltage, V2 represents the output terminal voltage, I1Represents the input current, I2Representing the output terminal current. z is a radical of11、z12、z21、z22The impedance between the ports is respectively represented, and the impedance value of each port is represented as follows:
therefore, the input impedance of the amplifier 301 in fig. 3 can be expressed mathematically by the resistors R1 and R2, and the capacitors C1, C2, and C3 of the matching circuit 302 and the matching circuit 303 at the input terminal. If the input impedance of the amplifier 301 is finally expressed in a complex form, the imaginary part of the input impedance can be adjusted to 0 by adjusting the capacitance value of the capacitor C1, C2, or C3, so that only the real part of the input impedance of the amplifier 301 is retained.
The output impedance of the amplifier 301 can be expressed mathematically by the resistors R4, R5he, and the capacitor C6 of the matching circuit 305 at the input. If the output impedance of the amplifier 301 is finally expressed in a complex form, the imaginary part of the output impedance can be adjusted to 0 by adjusting the capacitance value of the capacitor C6, so that the output impedance of the amplifier 301 only retains the real part.
In some embodiments of the present invention, the capacitors C1, C2, C3 and C6 are configured as adjustable capacitors, and the specific capacitance thereof is adjustable, so that the adjustment of the capacitance value changes the input impedance or the output impedance of the amplifier 301, thereby achieving the purpose that the input impedance or the output impedance 302 of the amplifier 301 is a pure real part.
In some embodiments, in addition to the capacitance element as the adjustable element, an inductance element may also be used as the adjustable element, and in a similar manner to the adjustable capacitance, the input impedance or the output impedance of the amplifier 301 may also be adjusted through the adjustable inductance, so as to achieve the purpose that the input impedance or the output impedance 302 of the amplifier 301 is a pure real part. In some embodiments, the tunable element may include a tunable capacitor and a tunable inductor, and the tunable capacitor and the tunable inductor are adjusted simultaneously to adjust the input impedance or the output impedance of the amplifier 301, so as to achieve the purpose that the input impedance or the output impedance 302 of the amplifier 301 is a pure real component.
The advantage of adjusting the input impedance or the output impedance of the amplifier 301 to a purely real part is that the losses of the signal transmitted in the circuit can be reduced. And the form of the adjustable element can meet the requirement of adjusting various radio frequency coils, and for different radio frequency coils, due to the difference of circuit structures, the purpose that the input impedance of the amplifier is a pure real part can be realized by adjusting the adjustable element before leaving a factory.
The technical scheme of the invention provides a magnetic resonance radio frequency coil receiving circuit, a radio frequency coil and a magnetic resonance system, and the signal receiving circuit, the radio frequency coil and the magnetic resonance system can adjust the input impedance of an amplifier to a pure real part by adjusting an adjustable element, reduce the transmission loss of signals in the circuit and improve the signal-to-noise ratio of the signals.
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 (9)
1. A signal receiving circuit for a magnetic resonance radio frequency coil, comprising:
an amplifier for amplifying the received magnetic resonance signal of the imaging subject;
an adjustable element forming a matching circuit of the input port of the amplifier for adjusting the input impedance of the amplifier and by which the imaginary part of the input impedance of the amplifier can be adjusted to zero, thereby adjusting the input impedance of the amplifier to a pure real part;
the adjustable element is a capacitive element and/or an inductive element;
and the matching module is arranged between the coil unit and the amplifier and used for realizing impedance matching.
2. The signal receiving circuit of claim 1, wherein the amplifier includes a signal input port, a signal output port, a bias circuit port, and a power distribution port.
3. The signal receiving circuit of claim 1, wherein the tunable element is a capacitive element connected in parallel with a resistor to the input of the amplifier.
4. The signal receiving circuit of claim 1, wherein the tunable element is two parallel capacitive elements, and wherein the two parallel capacitive elements are connected to the input of the amplifier.
5. The signal receiving circuit of claim 1, further comprising:
and the analog-to-digital conversion module is connected to the rear end of the amplifier and is used for converting the analog signal into a digital signal.
6. A radio frequency coil comprising one or several coil units for receiving magnetic resonance signals of an imaging subject; characterized in that it further comprises a signal receiving circuit according to any of claims 1-5 for signal processing of the received magnetic resonance signals.
7. The radio frequency coil as set forth in claim 6, wherein the radio frequency coil is a radio frequency body coil or a local coil.
8. The radio frequency coil as set forth in claim 7, wherein the local coil includes a coil array of the plurality of coil units.
9. A magnetic resonance system, comprising: the radio frequency coil of any of claims 6 to 8.
Priority Applications (7)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201710582372.3A CN107526051B (en) | 2017-07-17 | 2017-07-17 | Magnetic resonance radio frequency coil receiving circuit, radio frequency coil and magnetic resonance system |
| PCT/CN2017/119389 WO2019015258A1 (en) | 2017-07-17 | 2017-12-28 | 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 |
| US15/856,058 US10545204B2 (en) | 2017-07-17 | 2017-12-28 | Non-resonant 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 |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201710582372.3A CN107526051B (en) | 2017-07-17 | 2017-07-17 | Magnetic resonance radio frequency coil receiving circuit, radio frequency coil and magnetic resonance system |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CN107526051A CN107526051A (en) | 2017-12-29 |
| CN107526051B true CN107526051B (en) | 2020-06-26 |
Family
ID=60749030
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN201710582372.3A Active CN107526051B (en) | 2017-07-17 | 2017-07-17 | Magnetic resonance radio frequency coil receiving circuit, radio frequency coil and magnetic resonance system |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN107526051B (en) |
Citations (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN102096079A (en) * | 2009-12-12 | 2011-06-15 | 杭州中科微电子有限公司 | Method for constructing radio frequency front end of multi-mode multi-band satellite navigation receiver and module thereof |
| CN102498410A (en) * | 2009-09-17 | 2012-06-13 | 皇家飞利浦电子股份有限公司 | Multi-element transmit rf chain with local automatic tune and match device |
| CN102565733A (en) * | 2011-12-12 | 2012-07-11 | 中国科学院深圳先进技术研究院 | Magnetic resonance multi-core array radio frequency device and magnetic resonance signal receiving method |
| CN103364745A (en) * | 2012-04-02 | 2013-10-23 | 西门子公司 | Magnetic resonance tomography apparatus |
| CN205193255U (en) * | 2015-12-01 | 2016-04-27 | 上海联影医疗科技有限公司 | Magnetic resonance radio frequency receiver coil pack |
Family Cites Families (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| WO2007030832A2 (en) * | 2005-09-09 | 2007-03-15 | State Or Oregon Acting By And Through The State Board Of Higher Education Of Behalf Of The University Of Oregon | High impedance differential input preamplifier and antenna for magnetic resonance systems |
| US8269498B2 (en) * | 2009-05-04 | 2012-09-18 | The Regents Of The University Of California | Method and apparatus for MRI signal excitation and reception using non-resonance RF method (NORM) |
| US9632203B2 (en) * | 2010-06-22 | 2017-04-25 | Schlumberger Technology Corporation | Non-resonant logging tools with H-bridge switching |
| US10024938B2 (en) * | 2012-03-08 | 2018-07-17 | Schlumberger Technology Corporation | System and method for processing magnetic resonance signals |
| EP3164728B1 (en) * | 2014-07-01 | 2023-08-09 | Koninklijke Philips N.V. | Mr receive coil with detune circuit and energy harvesting circuit |
-
2017
- 2017-07-17 CN CN201710582372.3A patent/CN107526051B/en active Active
Patent Citations (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN102498410A (en) * | 2009-09-17 | 2012-06-13 | 皇家飞利浦电子股份有限公司 | Multi-element transmit rf chain with local automatic tune and match device |
| CN102096079A (en) * | 2009-12-12 | 2011-06-15 | 杭州中科微电子有限公司 | Method for constructing radio frequency front end of multi-mode multi-band satellite navigation receiver and module thereof |
| CN102565733A (en) * | 2011-12-12 | 2012-07-11 | 中国科学院深圳先进技术研究院 | Magnetic resonance multi-core array radio frequency device and magnetic resonance signal receiving method |
| CN103364745A (en) * | 2012-04-02 | 2013-10-23 | 西门子公司 | Magnetic resonance tomography apparatus |
| CN205193255U (en) * | 2015-12-01 | 2016-04-27 | 上海联影医疗科技有限公司 | Magnetic resonance radio frequency receiver coil pack |
Non-Patent Citations (1)
| Title |
|---|
| 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 * |
Also Published As
| Publication number | Publication date |
|---|---|
| CN107526051A (en) | 2017-12-29 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| US10884080B2 (en) | Dual-nuclear RF coil device and dual-nuclear RF coil array device | |
| RU2544867C2 (en) | Multi-element transmitting radio-frequency circuit with local automatic tuning and matching device | |
| US10895615B2 (en) | Balun for use in magnetic resonance imaging (MRI) systems and an MRI system that employs the balun | |
| CN107290697B (en) | Magnetic resonance radio frequency coil and magnetic resonance system | |
| US20100033185A1 (en) | Rf coil and apparatus to reduce acoustic noise in an mri system | |
| DE102012105201A1 (en) | System and method for receiving magnetoresonant signals | |
| US7479784B2 (en) | Arrangements, systems and methods for facilitating and collecting information associated with fluxes of magnetic fields provided at various angles from one another | |
| CN107561464B (en) | Magnetic resonance radio frequency coil and magnetic resonance system | |
| US10838025B2 (en) | Radio-frequency system for a magnetic resonance apparatus | |
| US5502387A (en) | Variable geometry MRI coil | |
| Kathiravan et al. | A review on potential issues and challenges in MR imaging | |
| DE102009044766A1 (en) | Radio frequency (RF) coil and device | |
| JP6410452B2 (en) | Method for obtaining separation matrix of separation device for coil array of parallel transmission magnetic resonance imaging system (MRI system), configuration method of parallel transmission magnetic resonance imaging system (MRI system) having separation device for coil array, magnetic resonance imaging Computer program for determining separation matrix of separation device for coil array of system (MRI) and parallel transmission magnetic resonance imaging system (MRI) | |
| CN110168393A (en) | The magnetic resonance tomography equipment run under low magnetic field intensity and local coil matrix | |
| CN105572612B (en) | A method of improving Multi-channel radio-frequency coil performance | |
| CN106990372B (en) | A kind of magnetic nuclear resonance radio frequency antenna circuit and its impedance matching methods | |
| CN107526051B (en) | Magnetic resonance radio frequency coil receiving circuit, radio frequency coil and magnetic resonance system | |
| DE102011006569A1 (en) | Local coil, method for generating magnetic resonance recordings of an examination subject and use of the local coil | |
| US20200326395A1 (en) | Single-stage amplifier with active feedback compensation | |
| CN115280172A (en) | Radio frequency receive coil network for single-sided magnetic resonance imaging | |
| US10613165B2 (en) | End ring port structure of an atypical radio-frequency coil of a magnetic resonance imaging system | |
| Hui | An effective compensation method for the mutual coupling effect in phased arrays for magnetic resonance imaging | |
| Zhu et al. | Detunable wireless Litzcage coil for human head MRI at 1.5 T | |
| DE102008044467A1 (en) | A system and apparatus for receiving magnetic resonance (MR) signals from an object to be imaged | |
| Qian et al. | Sensitivity Enhancement of an Inductively Coupled Local Detector Using a HEMT‐Based Current Amplifier |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| PB01 | Publication | ||
| PB01 | Publication | ||
| SE01 | Entry into force of request for substantive examination | ||
| SE01 | Entry into force of request for substantive examination | ||
| GR01 | Patent grant | ||
| GR01 | Patent grant | ||
| CP01 | Change in the name or title of a patent holder |
Address after: 201807 Shanghai city Jiading District Industrial Zone Jiading Road No. 2258 Patentee after: Shanghai Lianying Medical Technology Co., Ltd Address before: 201807 Shanghai city Jiading District Industrial Zone Jiading Road No. 2258 Patentee before: SHANGHAI UNITED IMAGING HEALTHCARE Co.,Ltd. |
|
| CP01 | Change in the name or title of a patent holder |