CN113921239A - Coil system - Google Patents
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- CN113921239A CN113921239A CN202111289877.3A CN202111289877A CN113921239A CN 113921239 A CN113921239 A CN 113921239A CN 202111289877 A CN202111289877 A CN 202111289877A CN 113921239 A CN113921239 A CN 113921239A
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- H—ELECTRICITY
- H01—ELECTRIC ELEMENTS
- H01F—MAGNETS; INDUCTANCES; TRANSFORMERS; SELECTION OF MATERIALS FOR THEIR MAGNETIC PROPERTIES
- H01F27/00—Details of transformers or inductances, in general
- H01F27/28—Coils; Windings; Conductive connections
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/05—Detecting, measuring or recording for diagnosis by means of electric currents or magnetic fields; Measuring using microwaves or radio waves
- A61B5/055—Detecting, measuring or recording for diagnosis by means of electric currents or magnetic fields; Measuring using microwaves or radio waves involving electronic [EMR] or nuclear [NMR] magnetic resonance, e.g. magnetic resonance imaging
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- H—ELECTRICITY
- H01—ELECTRIC ELEMENTS
- H01F—MAGNETS; INDUCTANCES; TRANSFORMERS; SELECTION OF MATERIALS FOR THEIR MAGNETIC PROPERTIES
- H01F27/00—Details of transformers or inductances, in general
- H01F27/34—Special means for preventing or reducing unwanted electric or magnetic effects, e.g. no-load losses, reactive currents, harmonics, oscillations, leakage fields
- H01F27/36—Electric or magnetic shields or screens
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- H—ELECTRICITY
- H01—ELECTRIC ELEMENTS
- H01F—MAGNETS; INDUCTANCES; TRANSFORMERS; SELECTION OF MATERIALS FOR THEIR MAGNETIC PROPERTIES
- H01F27/00—Details of transformers or inductances, in general
- H01F27/40—Structural association with built-in electric component, e.g. fuse
Abstract
The invention discloses a coil system, which comprises a frequency selection module and at least one coil structure, wherein each coil structure comprises at least two coil modules capable of outputting magnetic resonance signals with different frequencies and an output module, each coil module is electrically connected with the output module, and the frequency selection module is electrically connected with each coil module and is used for conducting any one coil module in each coil structure so as to enable the output module to output the magnetic resonance signals output by the conducted coil module. The invention solves the technical problem that the dual-frequency coil in the prior art can not achieve the optimal matching effect under two frequencies.
Description
Technical Field
The invention relates to the technical field of nuclear magnetic resonance imaging, in particular to a coil system.
Background
The magnetic resonance imaging technology is a process of sending radio frequency pulses to a human body through a radio frequency transmitting coil, exciting atomic nuclei (such as hydrogen atomic nuclei) with specific frequency in the human body to generate magnetic resonance signals in a resonant mode, and carrying out medical imaging on the human body by processing the received signals through a computer through a radio frequency receiving coil.
A dual frequency coil, i.e. sensitive to magnetic resonance signals generated by nuclei of two specific frequencies. At present, dual-frequency coils are generally used for research on spectrum, and research on quantitative analysis of another element besides H (hydrogen), for example: c, Na, P, etc. Usually, the H-nuclear image is used for localization of the region of interest, which involves excitation of the H-nuclei and reception of H-magnetic resonance signals; the signal of the other element is received for analysis, which requires that the coil must be sensitive to the nmr signal of the other element. Because a coil with frequency point resonance can not receive signals sent by two atomic nuclei at the same time, the coils with two frequencies can not work at the same time, most of double-frequency coils control the frequency change of the coil by using different frequencies to enable lumped elements to present different electrical properties, and the coil is generally designed by finding out a compromise matching, so that the matching effect on loads under two frequencies can not reach the best.
Disclosure of Invention
The invention aims to overcome the technical defects and provide a coil system, which solves the technical problem that the dual-frequency coil in the prior art cannot achieve the optimal matching effect under two frequencies.
In order to achieve the technical purpose, the invention adopts the following technical scheme:
a coil system comprises a frequency selection module and at least one coil structure, wherein each coil structure comprises at least two coil modules capable of outputting magnetic resonance signals with different frequencies and an output module, each coil module is electrically connected with the output module, the frequency selection module is electrically connected with each coil module and used for conducting each coil module to enable the output module to output the magnetic resonance signals output by the conducted coil modules.
Preferably, in the coil system, the frequency selection module includes a first signal source, the first signal source is electrically connected to each of the coil modules, and the first signal source can simultaneously output a turn-on signal and at least a turn-off signal, where the turn-on signal is used to turn on the coil module, and the turn-off signal is used to turn off the coil module.
Preferably, in the coil system, the coil module includes a receiving unit and a transmitting unit, the receiving unit is electrically connected to the transmitting unit, the transmitting unit is further connected to the frequency selection module and the output module, the receiving unit is configured to receive the magnetic resonance signal, and the transmitting unit is configured to be turned on or off according to the signal output by the frequency selection module, so as to output or not output the magnetic resonance signal to the output module.
Preferably, in the coil system, the transmitting unit includes a first diode, an anode of the first diode is connected to the frequency selection module and the receiving unit, and a cathode of the first diode is connected to the output module.
Preferably, in the coil system, the receiving unit includes a receiving coil, the receiving coil is electrically connected to the transmitting unit, and the receiving coil is configured to receive a magnetic resonance signal and send the magnetic resonance signal to the transmitting unit.
Preferably, in the coil system, the receiving coils of each coil structure are arranged in an overlapping manner and do not intersect with each other.
Preferably, in the coil system, the receiving unit further includes an amplifying circuit, the amplifying circuit is connected between the receiving coil and the transmitting unit, and the amplifying circuit is configured to amplify the magnetic resonance signal.
Preferably, in the coil system, the coil structure further includes a detuning control unit, the coil module further includes a detuning unit corresponding to the receiving coil, the detuning unit is electrically connected to the detuning control unit of the corresponding coil structure, the detuning unit is electrically connected to the receiving coil and is configured to control a detuning state of the receiving coil, and the detuning control unit is configured to control on and off of each detuning unit.
Preferably, in the coil system, the detuning control unit includes a second signal source and a filter inductor, one end of the filter inductor is connected to the second signal source, and the other end of the filter inductor is connected to each detuning unit.
Preferably, in the coil system, the detuning unit includes a detuning capacitor bank, a resonant inductor, and a second diode, the detuning capacitor bank is connected in series with the receiving coil, one end of the resonant inductor is connected to one end of the detuning capacitor bank, an anode of the second diode is connected to the other end of the filter inductor and the other end of the resonant inductor, and a cathode of the second diode is connected to the other end of the detuning capacitor bank, where the detuning capacitor bank is formed by connecting a plurality of detuning capacitors in series.
Compared with the prior art, the coil system provided by the invention is provided with the plurality of coil modules, the plurality of coil modules are equivalent to a plurality of independent coils for different frequencies, so that debugging of various frequencies can be realized independently, and in order to avoid signal interference of the coils with different frequencies when the coils simultaneously work to influence the accuracy of magnetic resonance, the coil system provided by the invention is provided with the frequency selection module, the conduction state of each coil module is controlled by the frequency selection module, so that the coils needing to work are conducted, the output of the output module can be controlled, the whole coil system can be suitable for atomic nuclei with various different frequencies to work, and the coil system can achieve the best matching effect under various different frequencies.
Drawings
FIG. 1 is a block diagram of a preferred embodiment of a coil system provided by the present invention;
FIG. 2 is a schematic diagram of one embodiment of a coil module in a coil system provided by the present invention;
FIG. 3 is a schematic diagram of one embodiment of a coil structure provided by the present invention;
fig. 4 is a schematic diagram of yet another embodiment of a coil structure provided by the present invention.
Detailed Description
In order to make the objects, technical solutions and advantages of the present invention more apparent, the present invention is described in further detail below with reference to the accompanying drawings and embodiments. It should be understood that the specific embodiments described herein are merely illustrative of the invention and are not intended to limit the invention.
Referring to fig. 1, a coil system according to an embodiment of the present invention includes a frequency selection module 100 and at least one coil structure 200, each coil structure 200 includes at least two coil modules 210 capable of outputting magnetic resonance signals with different frequencies and an output module 220, each coil module 210 is electrically connected to the output module 220, and the frequency selection module 100 is electrically connected to each coil module 210 and is configured to conduct any one coil module 210 in each coil structure 200, so that the output module 220 outputs the magnetic resonance signal output by the conducted coil module 210.
In this embodiment, in order to realize resonance at two different frequency points, a plurality of coil modules 210 are provided, the plurality of coil modules 210 are equivalent to a plurality of independent coils for different frequencies, so debugging of multiple frequencies can be realized independently, in order to avoid signal interference of coils with different frequencies when the coils work simultaneously and influence the accuracy of magnetic resonance, in this embodiment, a frequency selection module 100 is provided, the conduction state of each coil module 210 is controlled by the frequency selection module 100, so that the coils needing to work are conducted, thereby controlling the output of an output module 220, so that the whole coil system can adapt to nuclear resonance of multiple different frequencies to generate magnetic resonance signals, and the coil system can achieve the best matching effect under multiple different frequencies.
Specifically, when the frequency selection module 100 works, the frequency selection module 100 sends a control signal to each coil module 210 of each coil structure 200, so that only one coil module 210 in each coil structure 200 is turned on, and the rest coil modules 210 are all turned off, so that each coil structure 200 can output a magnetic resonance signal required by a user, and when the output magnetic resonance signal needs to be changed, the output magnetic resonance signal can be changed only by changing the turned-on coil module 210.
In addition, it should be noted that the coil system according to the embodiment of the present invention may have a plurality of coil structures 200, and may be used for a flexible coil of a planar structure, an abdominal coil, a spine coil, and the like. In practical implementation, a plurality of coil structures 200 may be controlled by one frequency selection module 100, for example, the structure shown in fig. 3, and of course, one coil structure 200 may also be controlled by a plurality of frequency selection modules 100, respectively, so as to implement frequency signal output control of a plurality of coil structures 200.
For the frequency selection module 100, it only needs to make one coil module 210 of the coil structure 200 be turned on and the other coil modules 210 be turned off, and therefore, the frequency selection module 100 only needs to output several different signals to control different operating states of the different coil modules 210, in a preferred embodiment, as shown in fig. 4, the frequency selection module 100 includes a first signal source (not shown in the figure), the first signal source is electrically connected to each coil module 210, the first signal source can simultaneously output one path of on signal and at least one path of off signal, where the on signal is used to turn on the coil module 210, and the off signal is used to turn off the other coil module 210.
In this embodiment, the first signal source may be one or more signal generators installed in the magnetic resonance system, and the signal generators may emit at least two different types of direct current signals, so as to implement switching between two different states (on state and off state) of the coil module 210, as shown in fig. 4, for the dual-frequency coil, the first signal source inputs signals to the two coil modules 210 through DC1 and DC2, respectively, in order to enable only one of the two coil modules 210 to be turned on, when a DC1 inputs an on signal, a DC2 inputs an off signal, and when a DC2 inputs an on signal, a DC1 inputs an off signal, so as to implement adjustment of the magnetic resonance signal output by the output module 220. Preferably, the on signal is a forward signal, such as a 150mA current signal, and the off signal is a reverse signal, such as a-30V reverse voltage signal.
Referring to fig. 4, in a preferred embodiment, in order to ensure stable transmission of a signal output by a first signal source and to ensure stable control of the coil modules 210, the frequency selection module 100 further includes a plurality of first filter circuits 110 corresponding to the coil modules 210 one to one, the first filter circuits 110 are connected between the first signal source and the corresponding coil modules 210 and are configured to filter the signal output by the first signal source and output the filtered signal to the corresponding coil modules 210, and through a filtering effect of the first filter circuits 110, stability of signal transmission can be ensured, so that the control accuracy of the frequency selection module 100 on the coil modules 210 is higher.
Referring to fig. 4, in order to stably filter the signal output by the first signal source, in a preferred embodiment, the first filter circuit 110 includes a first inductor L1, one end of the first inductor L1 is connected to the first signal source, and the other end of the first inductor L1 is connected to the coil module 210, so as to filter the ripple in the on signal or the off signal through the dc filtering function of the first inductor L1, so as to make the signal input to the coil module 210 more stable.
Of course, in other embodiments, the first filter circuit 110 may also use other filtering methods to perform filtering, for example, a method of connecting capacitors in parallel or a complex filter circuit composed of capacitors and inductors, and the specific circuit structure is not limited in the present invention.
For the coil structure 200 to be sensitive to magnetic resonance signals generated by nuclei of at least two different frequencies, each coil module 210 needs to be able to receive magnetic resonance signals of nuclei of the corresponding frequency. Referring to fig. 4, in a preferred embodiment, the coil module 210 includes a receiving unit 211 and a transmitting unit 212, the receiving unit 211 is electrically connected to the transmitting unit 212, the transmitting unit 212 is further connected to the frequency selection module 100 and the output module 220, the receiving unit 211 is configured to receive the magnetic resonance signal, and the transmitting unit 212 is configured to be turned on or off according to the signal output by the frequency selection module 100 to output or not output the magnetic resonance signal to the output module 220.
In this embodiment, the receiving unit 211 can be sensitive to a magnetic resonance signal generated by a nucleus (e.g., an H nucleus) with a specific frequency, the transmitting unit 212 is connected to a corresponding first inductor L1 in the frequency selection module 100, and the first inductor L1 enables the transmitting unit 212 to be turned on or off by inputting a turn-on signal or a turn-off signal to the transmitting unit 212.
It should be noted that after the coil module 210 receives the magnetic resonance signal generated by the atomic nucleus, the coil module 210 performs a series of processing on the magnetic resonance signal, such as amplification, filtering, and the like, but during the transmission process, the frequency of the magnetic resonance signal remains unchanged, and therefore, for convenience of understanding, in the embodiment of the present invention, both the signal received by the coil module 210 and the signal output by the coil module are described as the magnetic resonance signal.
With continued reference to fig. 4, in order to achieve the reception of the magnetic resonance signal, in a preferred embodiment, the receiving unit 211 includes a receiving coil f, the receiving coil f is electrically connected to the transmitting unit 212, and the receiving coil f is used for receiving the magnetic resonance signal and sending the magnetic resonance signal to the transmitting unit 212.
In this embodiment, the receiving coil f is configured to receive a magnetic resonance signal, and in order to ensure that the receiving coil f is sensitive to an atomic nucleus of a specific frequency, the receiving coil f includes an antenna, a matching capacitor Cm and a frequency modulation capacitor Cf, the matching capacitor Cm and the frequency modulation capacitor Cf are connected in the antenna, the antenna is configured to receive the magnetic resonance signal, the matching capacitor Cm is configured to match the antenna with a human body load, a capacitance value is generally determined according to a human body as the load, the capacitance value is kept unchanged after the determination, and the frequency modulation capacitor Cf is an adjustable capacitor.
In a preferred embodiment, the respective receiver coils f of each coil structure 200 are arranged in an overlapping manner and do not cross each other when specifically installed. Specifically, a plurality of receiving coils f shown in fig. 2 are completely overlapped, and the upper and lower parts do not intersect, so that the two coils are completely overlapped, and under the same resonance frequency, the condition that the coupling between the coils is the maximum is the case, and the condition is basically useless for a single frequency. However, when the plurality of receiving coils f correspond to a plurality of different tuning frequencies according to different loads, which is equivalent to that each receiving coil f corresponds to a single frequency channel, the combination of the plurality of receiving coils f corresponds to a plurality of frequency channels, so that each coil structure 200 corresponds to at least two receiving frequencies, and the plurality of receiving coils f form a dual-frequency or multi-frequency coil array, so that a dual-frequency or multi-frequency tuned coil structure can be realized by using the receiving coil array, and the coils are completely overlapped and do not occupy more space, thereby being convenient for installation.
With continued reference to fig. 4, in order to obtain the maximum signal-to-noise ratio of the magnetic resonance signal output by the receiving coil f, in a preferred embodiment, the receiving unit 211 further includes an amplifying circuit 2111, the amplifying circuit 2111 is connected between the receiving coil f and the transmitting unit 212, and the amplifying circuit 2111 is used for amplifying the magnetic resonance signal.
With continued reference to fig. 4, in order to amplify the magnetic resonance signal, in a preferred embodiment, the amplifying circuit 2111 includes a second inductor L2 and a preamplifier a1, one end of the second inductor L2 is connected to one end of the receiving coil f, the other end of the second inductor L2 is connected to the first input end of the preamplifier a1, the second input end of the preamplifier a1 is connected to the other end of the receiving coil f, and the output end of the preamplifier a1 is connected to the transmitting unit 212.
In this embodiment, the second inductor L2 is used to assist in matching adjustment, so that the preamplifier a1 matches to its optimal noise matching point, and the preamplifier a1 can amplify the magnetic resonance signal input by the matching capacitor Cm, thereby ensuring the strength of the magnetic resonance signal.
Of course, in other embodiments, the amplifying circuit 2111 may also be implemented by other structures, for example, the second inductor L2 is replaced by two capacitors connected in series, and the common end of the capacitors connected in series is connected to the first input terminal of the preamplifier a1, so that the preamplifier a1 is matched to the optimal noise matching point, and the specific implementation manner of the present invention is not limited thereto.
With continued reference to fig. 4, in order for the transmitting unit 212 to output or not output the magnetic resonance signal to the output module 220, in a preferred embodiment, the transmitting unit 212 includes a first diode D1, a frequency selection module 100 connected to the anode of the first diode D1 and a receiving unit 211, and the output module 220 is connected to the cathode of the first diode D1.
In this embodiment, the positive electrode of the first diode D1 is connected to the other end of the first inductor L1, when the first inductor L1 inputs an on signal (e.g., 150mA current), the first diode D1 is turned on, and the magnetic resonance signal input by the positive electrode of the first diode D1 can be output to the output module 220 through the first diode D1, so as to output a desired magnetic resonance signal, when the first inductor L1 inputs an off signal (e.g., -30V voltage), the first diode D1 is turned off in the reverse direction, and the magnetic resonance signal input by the positive electrode of the first diode D1 cannot be output to the output module 220 through the first diode D1, so as to terminate transmission of the undesired magnetic resonance signal.
With continued reference to fig. 4, in a preferred embodiment, in order to ensure the stability of the transmission of the magnetic resonance signal, the transmitting unit 212 further includes a second filter circuit 2121, the second filter circuit 2121 is connected between the first diode D1 and the receiving unit 211, and the second filter circuit 2121 is used for filtering the magnetic resonance signal input by the receiving unit 211, so that the stability of the transmission of the magnetic resonance signal can be ensured by the filtering function of the second filter circuit 2121.
With continued reference to fig. 4, in order to achieve stable filtering of the magnetic resonance signal, in a preferred embodiment, the second filter circuit 2121 includes a first capacitor C1, one end of the first capacitor C1 is connected to the receiving unit 211, and the other end of the first capacitor C1 is connected to the anode of the first diode D1, so as to achieve filtering of the magnetic resonance signal through the filtering effect of the first capacitor C1.
Of course, in other embodiments, the second filter circuit 2121 may also use other filtering methods to perform filtering, for example, a complex filter circuit composed of a capacitor and an inductor is used, and the specific circuit structure is not limited in the embodiments of the present invention.
In a magnetic resonance system, if the receiving coil operates during the signal transmission of the coil structure 200, the receiving coil may affect the patient and may cause harm to the patient, and therefore, with reference to fig. 4, in a preferred embodiment, the coil module 210 further includes a detuning unit 213 corresponding to the receiving coil f, the coil structure 200 further includes a detuning control unit 230, the detuning units 213 of the coil module 210 are electrically connected to the detuning control unit 230 of the corresponding coil structure 200, the detuning unit 213 is electrically connected to the receiving coil f and is configured to control the detuning state of the receiving coil f, and the detuning control unit 230 is configured to control the on and off of each detuning unit 213.
In this embodiment, since the receiving coil is tightly attached to the human body to work, the transmitting part is a volume coil, and the two parts have the same frequency, if the transmitting part works, the receiving coil f is not in a detuned state, energy of the transmitting part is induced, and induced current is generated in the receiving coil f, so that the human body is burned. Therefore, when the receiving coil f needs to be detuned, the detuning control unit 230 sends a control signal to the detuning unit 213 to enable the detuning unit 213 to work, and when the receiving coil f needs to be tuned, the detuning control unit 230 sends a control signal to the detuning unit 213 to enable the detuning unit 213 to stop working, so that the receiving coil f is prevented from being influenced in the coil transmitting process, and the safety of a patient is ensured.
To achieve control of the detuning units 213, please continue to refer to fig. 4, in a preferred embodiment, the detuning control unit 230 includes a second signal source and a filter inductor L3, one end of the filter inductor L3 is connected to the second signal source, and the other end of the filter inductor L3 is connected to each detuning unit 213. In some embodiments, the signal (for example, 150mA or-30V signal) may be directly output from the second signal source provided externally, and then filtered by the filter inductor L3 and output to the detuning unit 213, so as to stop the operation of the receiving coil f during transmission and stop the operation of the transmission during reception.
In a preferred embodiment, in order to reduce the cost and facilitate the control of the coil state, please continue to refer to fig. 4, in a preferred embodiment, the externally disposed second signal source is removed, the signal output by the output module 220 is directly used as the second signal source, one end of the filter inductor L3 is connected to the output module 220, and further the voltage signal output by the detuning unit output module 220 is turned on and off, thereby avoiding separately setting the second signal source to control the detuning unit 213, and ensuring that the receiving coil f is always in the detuning state during the transmission process, so that the control accuracy is higher, the connection is also facilitated, and in addition, the time point of the control module for controlling the coil detuning is also avoided.
In this embodiment, when the transmitting unit 212 transmits a signal to the output module 220, and the output module 220 transmits a signal, one path is directly transmitted, and the other path is filtered by the filter inductor L3 and then output to each detuning unit 213, so that each detuning unit 213 operates to detune the receiving coil f, and further, in the signal transmitting process, the receiving coil is in a detuned state, which is equivalent to that the receiving unit 211 is turned off, and the transmitting unit 212 operates.
It should be noted that, the embodiment of the present invention is not limited to use the filter inductor L3 to filter the signal output by the output module 220, and in other embodiments, other filtering manners may also be used to filter the signal, for example, a manner of using a parallel capacitor or a complex filter circuit composed of a capacitor and an inductor, and the present invention is not limited to the specific circuit structure thereof.
Referring to fig. 4, in a preferred embodiment, the detuning unit 213 only needs to detune the receiving coil f, and includes a detuning capacitor group 2131, a resonant inductor L4, and a second diode D2, where the detuning capacitor group 2131 is connected in series with the receiving coil f, one end of the resonant inductor L4 is connected to one end of the detuning capacitor group 2131, an anode of the second diode D2 is connected to the other end of the filter inductor L3 and the other end of the resonant inductor L4, and a cathode of the second diode D2 is connected to the other end of the detuning capacitor group C1 and the second input end of the preamplifier a1, and the detuning capacitor group 2131 is formed by connecting a plurality of detuning capacitors in series.
In this embodiment, when a control signal is input to the filter inductor L3, the second diode D2 is turned on, and at this time, the detuning capacitor set 2131 is communicated with the resonant inductor L4 to form an LC parallel resonant circuit connected in series with the receiving coil f, where the LC parallel resonant circuit causes a very large impedance during resonance, so that the receiving coil f is in an approximately open circuit state, and the receiving coil f is detuned. In this embodiment, the detuned capacitor group 2131 is formed by two detuned capacitors connected in series (C2 and C3 in fig. 4).
As for the output module, it only needs to ensure stable output of the signal, please continue to refer to fig. 4, in a preferred embodiment, the output module 220 includes a second capacitor C4, one end of the second capacitor C4 is connected to each coil module 210, and the other end of the second capacitor C4 is used for outputting the magnetic resonance signal output by the turned-on coil module 210.
In this embodiment, the second capacitor C4 is used for outputting the magnetic resonance signal output by the coil module 210 after filtering, so as to filter ripples in the magnetic resonance signal, thereby ensuring the stability of the signal, in the specific implementation, one end of the second capacitor C4 is connected to the negative electrode of the first diode D1, the other end of the second capacitor C4 is connected to the signal output end and one end of the filter inductor L3, after filtering through the second capacitor C4, the signal is output in two paths, one path of the magnetic resonance signal is output, and the other path of the magnetic resonance signal is output to the detuning unit 213 after being filtered through the filter inductor L3.
For better understanding of the present invention, the following detailed description of the technical solution of the present invention is provided with reference to fig. 1 to 4:
fig. 4 shows a dual-band coil, which includes a frequency selection module 100, two coil modules 210 and an output module 220, when it is required for the upper coil module 210 to output a signal, DC1 inputs a-30V reverse voltage signal to the first diode D1 in the lower coil module 210, and turns the first diode D1 of the lower coil module 210 to be turned off in the reverse direction, so that the lower coil module 210 cannot output a signal, DC2 inputs a 150mA current signal to the first diode D1 of the upper coil module 210, and turns the first diode D1 of the upper coil module 210 on, so that RFin1 directly transmits a signal to RFout1 and a filter inductor L3, the filter inductor L3 filters the signal and outputs the signal to the second diode D2 of each detuning unit 213, so that each second diode D2 is turned on, and thus the LC parallel resonant loop composed of detuning capacitors C2, 829c 3 and resonant inductor L4 is turned on, and then produce great impedance, make the receiving coil f detune, thus can guarantee the receiving coil f is in the detuning state when carrying on signal transmission.
In summary, the coil system provided in the embodiments of the present invention is provided with a plurality of coil modules, and the plurality of coil modules are equivalent to a plurality of independent coils for different frequencies, so that debugging of multiple frequencies can be separately achieved, and in order to avoid signal interference occurring when the coils with different frequencies simultaneously operate to affect the accuracy of magnetic resonance, the coil system provided in the embodiments of the present invention is provided with a frequency selection module, and the frequency selection module controls the conduction state of each coil module to conduct the coil that needs to operate, so that the output of the output module can be controlled, and the entire coil system can adapt to nuclei with multiple different frequencies to operate, so that the coil system can achieve the best matching effect at multiple different frequencies.
The above-described embodiments of the present invention should not be construed as limiting the scope of the present invention. Any other corresponding changes and modifications made according to the technical idea of the present invention should be included in the protection scope of the claims of the present invention.
Claims (10)
1. A coil system is characterized by comprising a frequency selection module and at least one coil structure, wherein each coil structure comprises at least two coil modules capable of outputting magnetic resonance signals with different frequencies and an output module, each coil module is electrically connected with the output module, and the frequency selection module is electrically connected with each coil module and used for conducting any one of the coil modules in the coil structure so that the output module outputs the magnetic resonance signals output by the conducted coil modules.
2. The coil system according to claim 1, wherein the frequency selection module includes a first signal source electrically connected to each of the coil modules, and the first signal source is capable of outputting a turn-on signal and at least a turn-off signal simultaneously, wherein the turn-on signal is used for turning on the coil module, and the turn-off signal is used for turning off the coil module.
3. The coil system according to claim 1, wherein the coil module comprises a receiving unit and a transmitting unit, the receiving unit is electrically connected to the transmitting unit, the transmitting unit is further connected to the frequency selection module and the output module, the receiving unit is configured to receive a magnetic resonance signal, and the transmitting unit is configured to be turned on or off according to a signal output by the frequency selection module to output or not output the magnetic resonance signal to the output module.
4. The coil system of claim 3, wherein the transmitting unit comprises a first diode, an anode of the first diode is connected to the frequency selection module and the receiving unit, and a cathode of the first diode is connected to the output module.
5. The coil system of claim 3, wherein the receiving unit comprises a receiving coil electrically connected to the transmitting unit, the receiving coil configured to receive the magnetic resonance signal and transmit the magnetic resonance signal to the transmitting unit.
6. The coil system of claim 5 wherein the respective receive coils of each of the coil structures are arranged in an overlapping configuration and do not cross each other.
7. The coil system of claim 5, wherein the receiving unit further comprises an amplifying circuit connected between the receiving coil and the transmitting unit, the amplifying circuit being configured to amplify the magnetic resonance signal.
8. The coil system according to claim 7, wherein the coil structure further comprises a detuning control unit, the coil module further comprises a detuning unit corresponding to the receiving coil, the detuning unit being electrically connected to the detuning control unit of the corresponding coil structure, the detuning unit being electrically connected to the receiving coil and configured to control a detuning state of the receiving coil, the detuning control unit being configured to control turning on and off of each detuning unit.
9. The coil system according to claim 8, wherein the detuning control unit comprises a second signal source and a filter inductor, one end of the filter inductor is connected to the second signal source, and the other end of the filter inductor is connected to each detuning unit.
10. The coil system according to claim 9, wherein the detuning unit comprises a detuning capacitor bank, a resonant inductor and a second diode, the detuning capacitor bank is connected in series with the receiving coil, one end of the resonant inductor is connected with one end of the detuning capacitor bank, an anode of the second diode is connected with the other end of the filter inductor and the other end of the resonant inductor, and a cathode of the second diode is connected with the other end of the detuning capacitor bank, wherein the detuning capacitor bank is formed by connecting a plurality of detuning capacitors in series.
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| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202111289877.3A CN113921239A (en) | 2021-11-02 | 2021-11-02 | Coil system |
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| Application Number | Priority Date | Filing Date | Title |
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| CN202111289877.3A CN113921239A (en) | 2021-11-02 | 2021-11-02 | Coil system |
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| CN113921239A true CN113921239A (en) | 2022-01-11 |
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