CN101403788B - Nuclear magnetic resonance receiving coil - Google Patents
Nuclear magnetic resonance receiving coil Download PDFInfo
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- CN101403788B CN101403788B CN2008102172115A CN200810217211A CN101403788B CN 101403788 B CN101403788 B CN 101403788B CN 2008102172115 A CN2008102172115 A CN 2008102172115A CN 200810217211 A CN200810217211 A CN 200810217211A CN 101403788 B CN101403788 B CN 101403788B
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Abstract
The invention discloses a nuclear magnetic resonance receiving coil which comprises a separable coil base and coil upper parts which can realize the structural connection and the electrical connection by a socket connector, wherein, the coil base comprises a matching tuned circuit; the coil upper parts are more than two, can replace each other and are different in sizes; a tuning capacitor C7 is connected in a circuit of each coil upper part, and the value of the tuning capacitor C7 causes that each coil upper part has the same output impedance in the working frequency section of the receiving coil, thereby the matching status of the receiving coil can be guaranteed to be constant. One coil of the invention can play the functions of a plurality of coils which are different in size, thereby saving the manufacturing cost and the using cost of the coil.
Description
Technical field the present invention relates to a kind of nuclear magnetic resonance receiving coil, relates in particular to a kind of nuclear magnetic resonance receiving coil of adjustable size joint of sample space.
Background technology uses receiving coil to collect the radiofrequency signal that sample is excited to send in nmr imaging technique, is used for sample image after the radiofrequency signal of collecting is exaggerated and rebuilds.The important indicator of receiving coil is that the receiving sensitivity of coil also is the coil signal to noise ratio (snr).If only consider the coil factor, coil SNR can be expressed as follows:
Can see coil signal to noise ratio (S/N ratio) and V from top formula
EffSquare root be inversely proportional to V
EffBe the dutycycle (it is more accurate in fact to be called the sky accounting) of coil, make V
EffAs far as possible little, will allow sample fill up the inner space of coil as far as possible, so in the design of receiving coil, allow coil smaller as far as possible, lean on more closely with the imaging position.
In the medical magnetic resonance imaging technique, the different scanning position scanned use different special-purpose coils respectively, body coil, neck coil or the like are for example arranged.Because the difference of different patient anatomies, in order to make the scanning effect best, even same scanning position, reaching coil is complementary with the size that scans the position, coil dutycycle by the best obtains best signal noise ratio (snr) of image, also need to use the coil of different size, the cost of production and use is than higher.
Summary of the invention the objective of the invention is to overcome the deficiencies in the prior art, proposes a kind of nuclear magnetic resonance receiving coil, under the prerequisite that does not change match circuit, the coiler part structure is carried out suitable variation, makes it to be applicable to the sample size of different sizes.
A kind of nuclear magnetic resonance receiving coil disclosed by the invention comprises the separable coil base and the coil top that connect and be electrically connected by the connector implementation structure, comprises the coupling tuned circuit in the described coil base; Described coil top has more than two and can the phase trans-substitution, and each described coil top is of different sizes; In the circuit on each described coil top, be connected with tuning capacity C7, the value of described tuning capacity C7 makes each described coil top have same output impedance in the frequency of operation section of described receiving coil, thereby the matching status that guarantees described receiving coil is constant.
Described plural coil top further comprises a coil top and left coil middle part and right coil middle part more than two pairs, each is to being connected with tuning capacity C8 and C9 respectively in the circuit in the middle part of described left coil middle part and the right coil, and is connected with the coil base implementation structure with described coil top by connector respectively and is electrically connected; The value of described tuning capacity C8 and C9 makes each described coil top to described left coil middle part and right coil middle part and described coil top be combined into have same output impedance, thereby the matching status that guarantees described receiving coil is constant.
Series resonance in the middle part of the value of described tuning capacity C8 of the frequency of operation section of described receiving coil and C9 makes each described left coil middle part and right coil.
Nuclear magnetic resonance receiving coil disclosed by the invention, select different coil top for use at the size of sample, perhaps select different coil middle parts for use, thereby make the adjustable size of coil space save, can both obtain best coil dutycycle to different sample sizes, guarantee imaging effect preferably.A coil of the present invention can play the effect of a plurality of coils that vary in size, and has saved the manufacturing cost and the use cost of coil.
Description of drawings
Fig. 1 is the circuit theory diagrams of the receiving coil of routine.
Fig. 2 is the circuit theory diagrams after the conventional receiving coil structural change.
Fig. 3 and Fig. 4 are the circuit theory diagrams of receiving coil of the present invention.
Fig. 5 is a receiving coil structural representation of the present invention.
Fig. 6 is the present invention's receiving coil structural representation bigger than coil inside space shown in Figure 5.
Fig. 7 is the receiving coil structural representation with coil middle part of the present invention.
Embodiment is described in further details the present invention below in conjunction with the drawings and specific embodiments.
In the use of magnetic resonance imaging system, need to use receiving coil that magnetic resonance signal is gathered, most important index is that the receiving sensitivity of coil also is the coil signal to noise ratio (snr) in the receiving coil.The coil signal to noise ratio (S/N ratio) is relevant with the coil dutycycle, so need to use the coil at a plurality of special-purpose positions that the different scanning position is scanned.Because the difference of different patient anatomies in order to make the scanning effect best, even same scanning position will reach coil and be complementary with the size that scans the position, obtains best coil dutycycle, also needs to use the coil of different size.
After coil collected signal, the system that need be transferred to handles just can obtain image, so coil also must be adjusted to best matching state, signal does not have loss during with the assurance transmission, if coil does not match, transmission signals will have loss, and nature can not obtain best image.The variation of coil dimension can cause the variation of electromagnetic parameter, just need readjust matching status at this size, and production and the cost that uses are very high.
Purpose of the present invention is exactly to carry out suitable variation to the coiler part structure using on the basis of same coil match circuit, makes it to be applicable to that patient scans the needs of position different size.Can make a coil be equivalent to a plurality of coils in the past like this, and all obtain best coil dutycycle at the sample of different sizes, imaging effect is also just best.Thereby the high production and the use cost of a plurality of coils have been avoided making.
Receiving coil can manufacture the two parts that are separated from each other, and promptly by the coil base and the coil top of connection of connector implementation structure and electrical connection, realizes that purpose of the present invention has two kinds of methods:
1. emat coil top more
We are made into coil can pass through the interconnected structure of connector.Wherein a part remains unchanged, and promptly coil base is a fixed part, and the match circuit and the coil base of coil are fixed together; Another part is coil top, makes different sizes, and size is per sample selected to use.This be because any one replaceable part of coil we can regard it as a kind of inductance (L0+L
v) and the combinational circuit (L0+C0+L of capacitor C 0
v), if in removable parts, increase a capacitor C
v, suitably adjust C
v, make C
vWith L
vSeries resonance, coil can equivalence be L0+C0 just like this, sees away from base that at this time the unit for electrical property parameters of any loam cake all is identical, all is L0+C0, so any replaceable part all keeps optimum matching with fixed part.
2. increase the coil central structure
The place of patching at a coil that can separate up and down increases a docking apparatus---the coil middle part, and winding volume is increased, inner accommodation space increases.Owing to increased a coil middle part part, winding inductance quantity has increased, electric capacity on we connect on increasing partly, and make this electric capacity and the inductance series resonance that increases part, so just can make the equivalence of increase part see short circuit as, the inductance value of coil was with the original state inductance value was identical just now, and like this, it still is best matching state that coil uses the circuit of identical coupling.
Be illustrated in figure 1 as conventional coil circuit schematic diagram, coil is divided into two parts, and the electrical quantity on coil top is equivalent to inductance L 1, corresponding inductance L 2 of the electrical quantity of coil base and L3, and tuning capacity C1, C2 and C3.When the top and the base of coil combines, inductance L 1, L2 and L3 in the circuit of formation and capacitor C 1, C2 and C3 acting in conjunction are adjusted to best transmission matching status (being generally 50 ohm) with coil.
After coil top changes, the circuit structure of coil is as shown in Figure 2: the size on coil top has changed, its electrical quantity just is changed to L4, at this time coil will reach best matching state, according to the method for prior art, must change tuning capacity C1, C2 and C3 is that C4, C5 and C6 reach the transmission coupling, and such coil match circuit also just needs to make again, just need again new coil of complete making, improved production and use cost.
The circuit theory diagrams of coil of the present invention as shown in Figure 3 make L5+L6=L4 for the coil top of each different size, and L5+C7+L6=L1, only need inductance value part (L5+L6-L1) that increases and the C7 series resonance of connecting to get final product.At this time, because the complete equivalence of the impedance of the part that changes is L1, the impedance on the coil top of each coil top part and Fig. 1 is equivalence fully, uses the tuning capacity C1 identical with Fig. 1, and C2, C3 promptly can reach best transmission matching status.
Same, if take second kind of implementation method, circuit theory diagrams as shown in Figure 4, between the coil base of coil both sides and coil top, respectively increased a coil middle part, make the electrical quantity L1 on coil top, the electrical quantity sum that adds the coil middle part increases to L1+L7+L8, we suitably adjust C8 and C9, the electrical quantity that can make coil top and middle part is L1+L7+L8+C8+C9=L1, coil impedance can equivalence be the structure of Fig. 1 like this, so still can adopt the tuned circuit of Fig. 1 to reach best transmission coupling.
More than two kinds of methods all be a part that has changed coil, make coil be applicable to the patient of different size, by some electric capacity of series connection in changing part, make it to use whole base of primary winding and match circuit can also reach best transmission coupling, final same coil can adopt different loop constructions at different patient anatomies, make that the applicable surface of coil is bigger, imaging effect is also better.
Be to be the structure that example illustrates two kinds of schemes of receiving coil of the present invention below with single knee coil, as shown in Figure 5, Fig. 5 is the structural representation of small size single knee receiving coil, Fig. 6 is the structural representation of large size list knee receiving coil, and Fig. 7 is the structural representation with single knee receiving coil at coil middle part.Three coils all adopt identical base and coil transmission match circuit.If according to the method in past, because the variation of coil dimension can bring the variation of transmission match circuit, so three complete coils inequality of essential production.But if adopt this method, three kinds of coils all can adopt same coil base and transmission match circuit thereof, and the user only needs more emat coil top or increase the coil middle part to get final product.
The structure of single knee coil shown in Figure 6 is bigger than the coil upper dimension in the structure of single knee coil shown in Figure 5, so tap into tuning capacity in this coil top.We can design the loam cake of a plurality of sizes at different patients' needs, because the tuning match circuit of coil all is to be assemblied on the base, like this, more the cost on emat coil top can be well below the price of buying a coil, but on the function of using, each loam cake just can an equivalent fully complete coil in the past.
The structure of single knee coil of Fig. 7 has adopted the loam cake and the base of the structure among Fig. 5, but increased by two heightening devices is the coil middle part, make loop construction increase, thereby adapt to different patient's needs, can also be according to different patients' size design different rising devices, like this, coil main body (loam cake and base) can remain unchanged, just increase several rising devices, coil just can adapt to different patients, makes the service efficiency of coil be able to very big lifting.
The base of three kinds of structures is measure-alike, if adopt traditional method for making, and three coil loam cakes, the three kinds of different base match circuits that all need form a complete production network, still, if make according to this method, three kinds of loam cakes only need a base to get final product.
Claims (3)
1. a nuclear magnetic resonance receiving coil comprises the separable coil base and the coil top that connect and be electrically connected by the connector implementation structure, comprises the coupling tuned circuit in the described coil base; It is characterized in that described coil top has more than two and can the phase trans-substitution, each described coil top is of different sizes; In the circuit on each described coil top, be connected with tuning capacity C7, the value of described tuning capacity C7 makes each described coil top have same output impedance in the frequency of operation section of described receiving coil, thereby the matching status that guarantees described receiving coil is constant.
2. nuclear magnetic resonance receiving coil according to claim 1, it is characterized in that, described plural coil top further comprises a coil top and left coil middle part and right coil middle part more than two pairs, each is to being connected with tuning capacity C8 and C9 respectively in the circuit in the middle part of described left coil middle part and the right coil, and is connected with the coil base implementation structure with described coil top by connector respectively and is electrically connected; The value of described tuning capacity C8 and C9 makes each described coil top to described left coil middle part and right coil middle part and described coil top be combined into have same output impedance, thereby the matching status that guarantees described receiving coil is constant.
3. nuclear magnetic resonance receiving coil according to claim 2 is characterized in that, series resonance in the middle part of the value of described tuning capacity C8 of the frequency of operation section of described receiving coil and C9 makes each described left coil middle part and right coil.
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| CN2008102172115A CN101403788B (en) | 2008-10-31 | 2008-10-31 | Nuclear magnetic resonance receiving coil |
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| CN2008102172115A CN101403788B (en) | 2008-10-31 | 2008-10-31 | Nuclear magnetic resonance receiving coil |
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| CN101403788A CN101403788A (en) | 2009-04-08 |
| CN101403788B true CN101403788B (en) | 2011-03-23 |
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| Publication number | Priority date | Publication date | Assignee | Title |
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| CN101923147B (en) * | 2010-07-17 | 2013-01-02 | 深圳市特深电气有限公司 | Probe for magnetic resonance equipment and magnetic resonance equipment |
| CN111537929B (en) * | 2020-04-20 | 2023-01-24 | 联影(常州)医疗科技有限公司 | Radio frequency coil assembly and magnetic resonance system |
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 |
| CN1129799C (en) * | 1997-11-28 | 2003-12-03 | 株式会社日立医药 | Coil harness assembly for interventional MRI application |
| CN2768019Y (en) * | 2004-12-24 | 2006-03-29 | 上海辰光医疗科技有限公司 | Foot/knee associated RF winding device for magnetic resonance image system |
| CN100397092C (en) * | 2004-06-17 | 2008-06-25 | 西门子（中国）有限公司 | Receiving coil circuit of magnetic resonance imaging system |
| CN101256222A (en) * | 2007-02-28 | 2008-09-03 | 西门子（中国）有限公司 | Receiving coil loop of magnetic resonance imaging system as well as detuning method thereof |
-
2008
- 2008-10-31 CN CN2008102172115A patent/CN101403788B/en active Active
Patent 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 |
| CN1129799C (en) * | 1997-11-28 | 2003-12-03 | 株式会社日立医药 | Coil harness assembly for interventional MRI application |
| CN100397092C (en) * | 2004-06-17 | 2008-06-25 | 西门子（中国）有限公司 | Receiving coil circuit of magnetic resonance imaging system |
| CN2768019Y (en) * | 2004-12-24 | 2006-03-29 | 上海辰光医疗科技有限公司 | Foot/knee associated RF winding device for magnetic resonance image system |
| CN101256222A (en) * | 2007-02-28 | 2008-09-03 | 西门子（中国）有限公司 | Receiving coil loop of magnetic resonance imaging system as well as detuning method thereof |
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Address after: 518107 area 301c, building 201, 301, 501, 5, building 4, Jihui mould Industrial Park, Tianliao Avenue, Tianliao community, Yutang street, Guangming District, Shenzhen City, Guangdong Province Patentee after: Shenzhen RF Tech Co., Ltd. Address before: Nanshan District East Road Shenzhen city Guangdong province 518054 No. 29 green cloud building three layer Patentee before: Shenzhen RF Tech Co., Ltd. |