CN101256222B - Receiving coil loop of magnetic resonance imaging system as well as detuning method thereof - Google Patents
Receiving coil loop of magnetic resonance imaging system as well as detuning method thereof Download PDFInfo
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- CN101256222B CN101256222B CN200710064092XA CN200710064092A CN101256222B CN 101256222 B CN101256222 B CN 101256222B CN 200710064092X A CN200710064092X A CN 200710064092XA CN 200710064092 A CN200710064092 A CN 200710064092A CN 101256222 B CN101256222 B CN 101256222B
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Abstract
The invention discloses a magnetic resonance imaging system receiver coil loop and detuning method thereof. The receiver coil loop comprises receiver coil and detuning loop, wherein the detuning loop comprises detuning capacitance, first inductance and diode in series in the receiver coil, the first inductance is connected with the detuning capacitance in parallel after connecting with the diode in series and the first inductance and diode are independent of receiver coil to be outside the receiver coil. The detuning method thereof comprises: connecting detuning capacitance in series in receiver coil, and connecting the first inductance and diode in series outside and independent of the receiver coil, and connecting the detuning capacitance and first inductance and diode in parallel; thedetuning capacitance, first inductance and diode forming detuning circuit, when the diode is on state, the detuning capacitance and the first inductance forming parallel resonance, therefore the receiver coil detunes. The invention has features: saving space without prejudice to handle, increased the distribution performance of the loop field of the receiver coil.
Description
Technical field
The present invention relates to receiving coil loop, especially receiving coil loop in the magnetic resonance imaging system and off resonance method thereof.
Background technology
Magnetic resonance imaging (Magnetic Resonance Imaging is hereinafter to be referred as MRI) is also referred to as Magnetic resonance imaging, is meant the imaging technique that utilizes nmr phenomena to obtain the physical internal structural information.But but remarkable advantages such as MRI is many because of its imaging parameters, the high random layer bedding fault of resolution and noninvasive imaging have obtained using widely in the imaging of medical field.
In the MRI system, for fear of influence between coil and protection patient, receiving coil must be in the off resonance state in body coil transmits process.In the prior art, the method that realizes being in body coil transmits process when receiving coil the off resonance state is to seal in a LC shunt-resonant circuit in receiving coil, very large impedance is caused in described LC loop when resonance, make coil be in approximate open-circuit condition.
But prior art also has certain deficiency, is described as follows in conjunction with Fig. 1, and wherein the effect of prime amplifier 102 is that the signal that receiving coil 101 receives is amplified, and outputs to then in the receiving system:
1) in the very little receiving coil 101 of volume (such as the arteria carotis coil), add the bigger detuned circuit 103 of volume ratio, shown in the dashed rectangle among Fig. 1, can in the operation of reality, bring a lot of inconvenience;
2) detuned circuit 103 needs very little electric capacity, can cause in the receiving coil 101 capacitance profile inhomogeneous, influences field distribution; For example in the wrist surface coils, the off resonance capacitor C 4 in the detuned circuit 103 is 33 pico farads, and the value of other four electric capacity in the receiving coil 101 is respectively that C1 is 220 pico farads, and C2 is 220 pico farads, and C3 is that 270 pico farads and C5 are 330 pico farads;
3) insert under the situation of isolation circuit at needs, receiving coil loop can not provide more convenient access point.
Summary of the invention
Technical matters to be solved by this invention is in order a kind of receiving coil loop of magnetic resonance imaging system and off resonance method thereof to be provided, comfortable working environment to be provided easily, improving the distribution performance of receiving coil loop of magnetic resonance imaging system field.
For solving the problems of the technologies described above, the present invention at first provides a kind of receiving coil loop of magnetic resonance imaging system, comprise receiving coil and off resonance loop, wherein said off resonance loop comprises that one is serially connected with the off resonance electric capacity in the described receiving coil, first inductance and a diode, it is in parallel after described first inductance and described diode are connected in series with described off resonance electric capacity, wherein, described first inductance and described diode are independent of described receiving coil and are arranged on the circuit external plate of described receiving coil.
Receiving coil loop of the present invention, may further include prime amplifier, first electric capacity and second electric capacity, described first electric capacity is connected the back with described second capacitances in series in parallel with described diode, and the other end of described second electric capacity is connected in described amp.in; Be used for making described prime amplifier obtain its optimum noise match point, and and then make described receiving coil obtain best signal to noise ratio (S/N ratio) by regulating described second electric capacity.
Receiving coil loop of the present invention can further comprise one second inductance, and the one end is connected between described first electric capacity and described second electric capacity, and the other end is connected in described amp.in mouth; Be used for cooperating, make described prime amplifier match its optimum noise match point with described first electric capacity and described second electric capacity.
Receiving coil loop of the present invention can further comprise one the 3rd inductance, and is in parallel with described first electric capacity; Be used for providing direct current to described diode.
The present invention and then a kind of magnetic resonance imaging system receiving coil off resonance method is provided comprises: off resonance electric capacity of serial connection in receiving coil; And be independent of described receiving coil and at its outside one first inductance of serial connection and a diode, and first inductance after will connecting and diode and described off resonance electric capacity are connected in parallel; Wherein, described off resonance electric capacity, first inductance and diode constitute the off resonance loop, and when diode current flow, the off resonance electric capacity and first inductance constitute parallel resonance, thereby make described receiving coil off resonance.
In the receiving coil off resonance method of the present invention, described first inductance and described diode can be arranged on the described receiving coil circuit external plate.
Receiving coil off resonance method of the present invention can further provide prime amplifier, first electric capacity, second electric capacity, and described first electric capacity is connected the back with second capacitances in series in parallel with described diode, and described second electric capacity is connected in described amp.in; Be used for making described prime amplifier obtain its optimum noise match point, and and then make described receiving coil obtain best signal to noise ratio (S/N ratio) by regulating described second electric capacity.
Receiving coil off resonance method of the present invention can further provide one the 3rd inductance, and is in parallel with described first electric capacity; Be used for providing direct current to described diode.
Receiving coil off resonance method of the present invention can further provide one second inductance, and the one end is connected between described first electric capacity and second electric capacity, and the other end is connected in described amp.in mouth; Be used for cooperating, make described prime amplifier match its optimum noise match point with described first electric capacity and described second electric capacity.
Compared with prior art, adopt receiving coil loop of magnetic resonance imaging system of the present invention and off resonance method thereof, have following characteristics:
1) detuned circuit is arranged on the receiving coil circuit external plate, not only can saves the space but also do not hinder operation;
2) can distribute equably electric capacity in the receiving coil, a distribution that makes is more even;
3) tie point of diode and inductance can be used to insert isolation circuit between the different receiving coils unit in the off resonance loop.
Description of drawings
Fig. 1 is a receiving coil loop synoptic diagram in the prior art;
Fig. 2 is a receiving coil loop embodiment synoptic diagram of the present invention.
Embodiment
The present invention is described in further detail below in conjunction with the drawings and specific embodiments.
As shown in Figure 2, whole off resonance loop 203 is positioned at the outside of receiving coil 201, comprises an off resonance capacitor C p1 who is serially connected in the receiving coil 201, and one first inductance L s1 and a diode D1, shown in the dotted ellipse among Fig. 2.The first inductance L s1 and diode D1 are independent of receiving coil 201, and are arranged on the receiving coil 201 circuit external plates.After the first inductance L s1 and diode D1 are connected in series, in parallel with off resonance capacitor C p1 again.When diode D1 conducting, the off resonance capacitor C P1 and the first inductance L s1 constitute parallel resonance, thereby make whole receiving coil 201 be in idle off resonance state.
In the receiving coil loop of the present invention, also comprise a prime amplifier 202, and between receiving coil 201 and prime amplifier 202, be connected with the first capacitor C s and the second capacitor C p2.After the first capacitor C s and the second capacitor C p2 were connected in series, D1 was in parallel with diode.In prime amplifier 202 these sides, the second capacitor C p2 is connected the input end of prime amplifier 202.Regulate matching status by the capacitance of regulating the second capacitor C p2, make the input impedance matching of prime amplifier 202 arrive its optimum noise match point, and and then make receiving coil 201 obtain best signal to noise ratio (S/N ratio).
The second capacitor C p2 can be a tunable capacitor, or fixed capacity.If the second capacitor C p2 is a fixed capacity, then under different applied environments, need on circuit board, change the electric capacity of different appearance values according to concrete needs.
In the receiving coil loop of the present invention, also add one second inductance L s2, the one end is connected on the tie point of the first capacitor C s and the second capacitor C p2, and the other end is connected on the input port of prime amplifier 202.This mainly is to consider when some only can't make prime amplifier 202 obtain needed phase place with the first capacitor C s and the second capacitor C p2, cooperate by the second inductance L s2 that adds and to regulate, just can make prime amplifier 202 match its optimum noise match point, and and then make receiving coil 201 obtain best signal to noise ratio (S/N ratio).Sometimes, might need to add the second inductance L s2 in that the bigger situation of the size of receiving coil 201 is next.
In order to make receiving coil 201 enter the off resonance state easily, the present invention also by one the 3rd inductance L s3, provides direct current to diode D1 when receiving coil 201 need enter the off resonance state, allows its conducting, makes receiving coil 201 enter the off resonance state.The 3rd inductance L s3 and the first capacitor C s are connected in parallel, and one terminates on the tie point of the first inductance L s1 and diode D1, and the other end is connected on the tie point of the first capacitor C s and the second capacitor C p2.
When receiving coil 201 was in the off resonance state, off resonance capacitor C p1 only need get the fixed capacity of a smaller value, if the equiva lent impedance of receiving coil 201 is Z
1, so from the impedance Z of the right side part of diode D1
InFor:
At this moment, need make impedance Z
InBig as much as possible, with this loss that reduces by the first inductance L s1 to influence on signal-to-noise ratio (SNR).For example in the system of 1.5T, when the equivalent resistance of receiving coil 201 is 5 ohm, equivalent inductive reactance is 88 ohm, during off resonance capacitor C p1=22 pico farad, the first inductance L s1=284.64 nanohenry among Fig. 2, the first capacitor C s=5.34 pico farad, the second capacitor C p2=30.93 pico farad, the second inductance L s2=139.2 nanohenry.At this moment, be 0.975 by calculating from receiving coil 201 to amp.in the signal to noise ratio (S/N ratio) that 202 transmission coefficient obtains.
Receiving coil loop of the present invention, because the off resonance loop 203 that will contain than low-capacitance electric capacity independently is arranged on the receiving coil 201 circuit external plates, so can be by holding the not little electric capacity of value difference in the receiving coil 201 that distributes equably, thereby a distribution that makes be more even.And the appearance value like off resonance capacitor C 4 in the prior art receiving coil loop is not bigger with the capacitance gap of other several electric capacity, the distribution of influence field.
In addition, diode D1 in the off resonance of the present invention loop and the tie point of the first inductance L s1 can be used to insert isolation circuit and eliminate influencing each other between receiving coil 201 different units.Said receiving coil 201 comprises two kinds among the present invention, and a kind of is the coil that has only a unit, and another comprises a more than cellular array coil exactly.At this situation of array coil, the receiving coil loop in the invention is applied to each coil unit.All array coils all are composed of multiple units, and can have coupling between the different units of same array coil when work, and then influence imaging results.In the prior art, isolation circuit and be inconvenient to add, but adopt receiving coil loop of the present invention can be easily inserts corresponding isolation circuit from the tie point of the diode D1 and the first inductance L s1.
The present invention and then a kind of off resonance method of magnetic resonance imaging system receiving coil is provided, off resonance capacitor C p1 of serial connection in receiving coil 201 as shown in Figure 2, be independent of be connected in series on the circuit board of receiving coil 201 one first inductance L s1 and a diode D1 in the outside of receiving coil 201, and the first inductance L s1 that will be connected in series and diode D1 and off resonance capacitor C p1 are connected in parallel.Off resonance capacitor C p1, the first inductance L s1 and diode D1 constitute off resonance loop 203.When diode D1 conducting, the off resonance capacitor C p1 and the first inductance L s1 constitute parallel resonance, thereby make whole receiving coil 201 be in idle off resonance state.
On this basis, the inventive method is by improving the performance that capacitance profile in the receiving coil 201 improves receiving coil loop.After the first capacitor C s and the second capacitor C p2 were connected in series, D1 was in parallel with diode.In prime amplifier 202 these sides, the second capacitor C p2 is connected amplifier 202 input ends.Regulate matching status by the capacitance of regulating the second capacitor C p2, make the input impedance matching of prime amplifier 202 arrive its optimum noise match point.
The inventive method also by inserting the second inductance L s2, cooperates the adjusting of the first capacitor C s and the second capacitor C p2, makes prime amplifier 202 obtain needed phase place, matches its optimum noise match point.The end of the second inductance L s2 is connected on the tie point of the first capacitor C s and the second capacitor C p2, and the other end is connected on the input port of prime amplifier 202.When some only uses the first capacitor C s and the second capacitor C p2 can't make prime amplifier 202 obtain needed phase place, cooperate accent by the second inductance L s2 that adds
Save the first capacitor C s and the second capacitor C p2, just can make prime amplifier 202 match its optimum noise match point, and and then make receiving coil 201 obtain best signal to noise ratio (S/N ratio).Sometimes, might need to add the second inductance L s2 in that the bigger situation of the size of receiving coil 201 is next.
In order to make receiving coil 201 enter the off resonance state easily, the inventive method also comes to provide the direct current that enters the off resonance state for diode D1 by inserting one the 3rd inductance L s3.When needs entered the off resonance state, prime amplifier 202 was by the second inductance L s2 and the 3rd inductance L s3, direct current outputed to allow its conducting on the diode D1, make receiving coil 201 its enter the off resonance state.The 3rd inductance L s3 and the first capacitor C s are connected in parallel, and one terminates on the tie point of the first inductance L s1 and diode D1, and the other end is connected on the tie point of the first capacitor C s and the second capacitor C p2.
Claims (8)
1. receiving coil loop of magnetic resonance imaging system, comprise receiving coil (201) and off resonance loop (203), wherein said off resonance loop (203) comprises an off resonance electric capacity (Cp1) that is serially connected with in the described receiving coil (201), one first inductance (Ls1) and a diode (D1), it is in parallel after described first inductance (Ls1) and described diode (D1) are connected in series with described off resonance electric capacity (Cp1), it is characterized in that described first inductance (Ls1) and described diode (D1) are independent of described receiving coil (201) and are arranged at the outside of described receiving coil (201); Described first inductance (Ls1) and described diode (D1) are arranged on described receiving coil (201) the circuit external plate.
2. receiving coil loop of magnetic resonance imaging system as claimed in claim 1, further comprise prime amplifier (202), first electric capacity (Cs) and second electric capacity (Cp2), described first electric capacity (Cs) and described second electric capacity (Cp2) back that is connected in series is in parallel with described diode (D1), and the other end of described second electric capacity (Cp2) is connected in described amplifier (202) input end; Be used for making described prime amplifier (202) obtain its optimum noise match point, and and then make described receiving coil (201) obtain best signal to noise ratio (S/N ratio) by regulating described second electric capacity (Cp2).
3. receiving coil loop of magnetic resonance imaging system as claimed in claim 2, further comprise one second inductance (Ls2), the one end is connected between described first electric capacity (Cs) and described second electric capacity (Cp2), and the other end is connected in described amplifier (202) input port; Be used for cooperating, make described prime amplifier (202) match its optimum noise match point with described first electric capacity (Cs) and described second electric capacity (Cp2).
4. receiving coil loop of magnetic resonance imaging system as claimed in claim 2 further comprises one the 3rd inductance (Ls3), and is in parallel with described first electric capacity (Cs); Be used for providing direct current to described diode (D1).
5. a magnetic resonance imaging system receiving coil off resonance method is characterized in that, comprising:
A serial connection off resonance electric capacity (Cp1) in receiving coil (201); And
Be independent of described receiving coil (201) and at its outside serial connection one first inductance (Ls1) and a diode (D1), and first inductance (Ls1) after will connecting and diode (D1) and described off resonance electric capacity (Cp1) are connected in parallel;
Wherein, described off resonance electric capacity (Cp1), first inductance (Ls1) and diode (D1) constitute off resonance loop (203), when diode (D1) conducting, off resonance electric capacity (Cp1) and first inductance (Ls1) constitute parallel resonance, thereby make described receiving coil (201) off resonance;
Wherein, described first inductance (Ls1) and diode (D1) are set on described receiving coil (201) the circuit external plate.
6. method as claimed in claim 5, prime amplifier (202), first electric capacity (Cs) and second electric capacity (Cp2) further are provided, described first electric capacity (Cs) and second electric capacity (Cp2) back that is connected in series is in parallel with described diode (D1), and described second electric capacity (Cp2) is connected in described amplifier (202) input end; Be used for making described prime amplifier (202) obtain its optimum noise match point, and and then make described receiving coil (201) obtain best signal to noise ratio (S/N ratio) by regulating described second electric capacity (Cp2).
7. method as claimed in claim 6 further provides one second inductance (Ls2), and the one end is connected between described first electric capacity (Cs) and second electric capacity (Cp2), and the other end is connected in described amplifier (202) input port; Be used for cooperating, make described prime amplifier (202) match its optimum noise match point with described first electric capacity (Cs) and described second electric capacity (Cp2).
8. method as claimed in claim 6 further provides one the 3rd inductance (Ls3), and is in parallel with described first electric capacity (Cs); Be used for providing direct current to described diode (D1).
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| Application Number | Priority Date | Filing Date | Title |
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| CN200710064092XA CN101256222B (en) | 2007-02-28 | 2007-02-28 | Receiving coil loop of magnetic resonance imaging system as well as detuning method thereof |
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| CN200710064092XA CN101256222B (en) | 2007-02-28 | 2007-02-28 | Receiving coil loop of magnetic resonance imaging system as well as detuning method thereof |
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| CN101256222A CN101256222A (en) | 2008-09-03 |
| CN101256222B true CN101256222B (en) | 2010-09-29 |
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Families Citing this family (7)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN101403788B (en) * | 2008-10-31 | 2011-03-23 | 深圳市特深电气有限公司 | Nuclear magnetic resonance receiving coil |
| CN103547937B (en) * | 2011-05-23 | 2016-09-21 | 皇家飞利浦有限公司 | FET as the detuned circuit for MRI RF coil switchs |
| CN103185874B (en) * | 2011-12-28 | 2015-09-16 | 上海辰光医疗科技股份有限公司 | Without external DC line commutation apparatus can off resonance magnetic resonance radio frequency coil |
| DE102012211147B4 (en) * | 2012-06-28 | 2017-08-31 | Siemens Healthcare Gmbh | Automatic detuning of unconnected transmit-receive coils for MRI |
| CN108802641B (en) * | 2013-04-11 | 2022-01-07 | 西门子(深圳)磁共振有限公司 | Local coil and magnetic resonance imaging system |
| CN103576111A (en) * | 2013-11-15 | 2014-02-12 | 厦门大学 | Double-frequency-modulation surface coil |
| CN107765201B (en) * | 2016-08-19 | 2020-08-25 | 华东师范大学 | Magnetic resonance imaging receiving coil with protection circuit |
Citations (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US5435302A (en) * | 1988-09-09 | 1995-07-25 | Medrad, Inc. | Flexible surface coils for use in nuclear magnetic resonance imaging |
| JP2588552B2 (en) * | 1986-12-22 | 1997-03-05 | フィリップス エレクトロニクス ネムローゼ フェンノートシャップ | Magnetic resonance imaging device |
| CN1710442A (en) * | 2004-06-17 | 2005-12-21 | 西门子（中国）有限公司 | Receiving coil circuit of magnetic resonance imaging system |
| CN1714747A (en) * | 2004-07-02 | 2006-01-04 | 西门子（中国）有限公司 | Array receiving coil of magnetic resonance imaging system |
| CN1284001C (en) * | 2001-10-01 | 2006-11-08 | 西门子公司 | Coil device relative receiving circuit of magnetic resonant device and relative magnetic resonant device |
-
2007
- 2007-02-28 CN CN200710064092XA patent/CN101256222B/en not_active Expired - Fee Related
Patent Citations (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JP2588552B2 (en) * | 1986-12-22 | 1997-03-05 | フィリップス エレクトロニクス ネムローゼ フェンノートシャップ | Magnetic resonance imaging device |
| US5435302A (en) * | 1988-09-09 | 1995-07-25 | Medrad, Inc. | Flexible surface coils for use in nuclear magnetic resonance imaging |
| CN1284001C (en) * | 2001-10-01 | 2006-11-08 | 西门子公司 | Coil device relative receiving circuit of magnetic resonant device and relative magnetic resonant device |
| CN1710442A (en) * | 2004-06-17 | 2005-12-21 | 西门子（中国）有限公司 | Receiving coil circuit of magnetic resonance imaging system |
| CN1714747A (en) * | 2004-07-02 | 2006-01-04 | 西门子（中国）有限公司 | Array receiving coil of magnetic resonance imaging system |
Non-Patent Citations (1)
| Title |
|---|
| CN 1714747 A,全文. |
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