CN112394308B - Transmitting radio frequency coil unit and magnetic resonance system - Google Patents
Transmitting radio frequency coil unit and magnetic resonance system Download PDFInfo
- Publication number
- CN112394308B CN112394308B CN201910752732.9A CN201910752732A CN112394308B CN 112394308 B CN112394308 B CN 112394308B CN 201910752732 A CN201910752732 A CN 201910752732A CN 112394308 B CN112394308 B CN 112394308B
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- radio frequency
- frequency coil
- coil unit
- transmitting
- transmitting radio
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- 239000004020 conductor Substances 0.000 claims abstract description 10
- 238000004804 winding Methods 0.000 claims abstract description 3
- 239000003990 capacitor Substances 0.000 claims description 9
- 230000008878 coupling Effects 0.000 abstract description 15
- 238000010168 coupling process Methods 0.000 abstract description 15
- 238000005859 coupling reaction Methods 0.000 abstract description 15
- 230000005540 biological transmission Effects 0.000 description 13
- 230000000241 respiratory effect Effects 0.000 description 11
- 238000010586 diagram Methods 0.000 description 10
- 230000000694 effects Effects 0.000 description 8
- 238000001514 detection method Methods 0.000 description 5
- 230000029058 respiratory gaseous exchange Effects 0.000 description 5
- 230000002401 inhibitory effect Effects 0.000 description 2
- 238000002595 magnetic resonance imaging Methods 0.000 description 2
- 238000012550 audit Methods 0.000 description 1
- 230000009286 beneficial effect Effects 0.000 description 1
- 238000005516 engineering process Methods 0.000 description 1
- 230000004907 flux Effects 0.000 description 1
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
- G01R33/3628—Tuning/matching of the transmit/receive coil
-
- 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
Abstract
The invention provides a transmitting radio frequency coil unit and a magnetic resonance system. The transmitting radio frequency coil unit is formed by winding a conductor, and a central symmetrical structure is formed by taking a unique intersection point as a central symmetrical point; the two end points of the conductor are not connected, one end point is used for connecting the positive electrode of the coaxial cable through a feeder line, and the other end point is used for connecting the negative electrode of the coaxial cable through the feeder line; and the transmitting radio frequency coil unit is positioned at the geometric center of the receiving radio frequency coil array and positioned on the same plane as the receiving radio frequency coil array. The embodiment of the invention reduces the coupling between the radio frequency coil units in the MRI system.
Description
Technical Field
The present invention relates to the field of MRI (Magnetic Resonance Imaging ) technology, in particular to a transmit radio frequency coil unit and an MR (Magnetic Resonance ) system.
Background
In MR systems, the transmission radio frequency signals and their reflection signals can be used to detect respiratory signals. The transmitting radio frequency coil unit transmits radio frequency signals with different frequency from MR, the radio frequency signals act on a human body to generate reflected signals, the reflected signals are received by the receiving radio frequency coil array, and the receiving radio frequency coil array is used for respiratory motion tracking based on respiratory signal modulation of the MR receiver.
When the radio frequency coil units work, the radio frequency coil units are electrified to generate alternating magnetic fields, and each alternating magnetic field generated by each radio frequency coil unit corresponds to one channel. In an ideal case, the alternating magnetic field generated by each radio frequency coil unit is independent, i.e. the alternating magnetic fields generated by any two radio frequency coil units have no influence on each other. However, in practical applications, coupling phenomena may occur between two rf coil units, especially for adjacent rf coil units, which reduces the signal-to-noise ratio of the multi-channel rf coil.
In order to reduce interference with the MR signals during respiratory motion signal detection, the transmitting radio frequency coil unit is composed of a small loop which is arranged to be decoupled from the main receiving loop of the receiving radio frequency coil array. To achieve decoupling, the most common approach is to provide radio frequency coil unit overlap to reduce coupling between adjacent radio frequency coil units. Fig. 1 shows a schematic diagram of a common decoupling of the transmit loop and the MR receive loop, wherein two measures are taken to achieve decoupling:
the first measure is that each two adjacent receiving radio frequency coil units are partially overlapped to form an overlapped area, and the overlapped area has a certain area, so that compared with the condition that each two adjacent coils do not have the overlapped area, the magnetic flux of each radio frequency coil unit is changed, and the influence of coupling is neutralized. The area of the overlapping area can be adjusted and determined according to the following mode: taking radio frequency coil units 1 and 2 as an example, setting the area of a superposition area of the radio frequency coil units 1 and 2 as S1 at initial time, detecting whether a transmission value between the radio frequency coil units 1 and 2 reaches a preset standard, if the transmission value does not reach the preset standard, indicating that the radio frequency coil units 1 and 2 do not realize decoupling, adjusting the size of the radio frequency coil units S1, detecting the transmission value between the radio frequency coil units 1 and 2, and adjusting and detecting the transmission value until the transmission value reaches the preset standard. The transmission value is an energy transmission value between two radio frequency coil units, and in an ideal case, when the transmission value is zero, the transmission value indicates that the two radio frequency coil units are not coupled at all, and in practical application, as long as the transmission value is smaller than a preset standard value, the transmission value is regarded as that the two radio frequency coil units are not coupled.
And secondly, arranging a transmitting radio frequency coil unit at the geometric center of the receiving radio frequency coil array, wherein the transmitting loop is overlapped with the main receiving loop of the receiving radio frequency coil array.
The disadvantage of the above-described decoupling approach is that the overlapping of the transmit loop and the main receive loop is effective only for decoupling adjacent radio frequency coil units and not for non-adjacent radio frequency coil units. For example, the transmit loop has a good decoupling effect between the MR main receive loops 6 and 7, but for other MR receive loops such as: 1. 2, 3, 4, 5, 8, 9, 10, 11, 12, the decoupling effect is poor. In addition, in order to reduce the coupling to the MR receive circuit, the transmit circuit is always designed to be sufficiently small, which also reduces the strength of the transmit signal.
Disclosure of Invention
To solve the above problems, the present invention provides a transmitting radio frequency coil unit to reduce coupling between radio frequency coil units in an MR system.
The present invention provides an MR system to reduce coupling between radio frequency coil units in the MR system.
The technical scheme of the invention is realized as follows:
the transmitting radio frequency coil unit is positioned in the MR system, is formed by winding a conductor and takes a unique intersection as a central symmetry point to form a central symmetry structure;
the two end points of the conductor are not connected, one end point is used for connecting the positive electrode of the coaxial feed through a feeder line, and the other end point is used for connecting the negative electrode of the coaxial feed through the feeder line;
and the transmitting radio frequency coil unit is positioned at the geometric center of the receiving radio frequency coil array and positioned on the same plane as the receiving radio frequency coil array.
The outline of the transmitting radio frequency coil unit does not exceed the overlapping area of the two receiving radio frequency coil units at the geometric center of the receiving radio frequency coil array.
The transmitting radio frequency coil unit is of a butterfly structure, and two wings of the butterfly structure take a unique intersection point as a central symmetry point.
Any symmetry axis of the transmitting radio frequency coil unit is parallel to the transverse side or the longitudinal side of the receiving radio frequency coil array.
Two capacitors are connected in series in the radio frequency coil unit, the two capacitors are distributed on a symmetrical axis (202) of the radio frequency coil unit passing through the coil unit, and the capacitance values of the two capacitors are equal.
An MR system comprising a transmit radio frequency coil unit as claimed in any one of the preceding claims.
According to the invention, the coupling between the radio frequency coil units in the MR system is reduced by constructing the transmitting radio frequency coil units which are symmetrical in center and have opposite magnetic force lines in the two parts of the central symmetry, and arranging the transmitting radio frequency coil units at the geometric center of the receiving radio frequency coil array.
Drawings
FIG. 1 is a schematic diagram of a common decoupling of a prior art transmit loop and MR receive loop;
fig. 2 is a schematic structural diagram of a transmitting rf coil unit according to an embodiment of the present invention;
fig. 3 is a schematic diagram of a positional relationship between a transmitting rf coil unit and a receiving rf coil array according to an embodiment of the present invention;
fig. 4 is a schematic diagram of a positional relationship between a transmitting rf coil unit and a receiving rf coil array according to another embodiment of the present invention;
fig. 5 is a schematic structural diagram of a transmitting rf coil unit according to another embodiment of the present invention.
Wherein, the reference numerals are as follows:
Detailed Description
In order to make the objects, technical solutions and advantages of the present invention more apparent, the technical solutions of the present invention will be described in detail below by way of examples with reference to the accompanying drawings.
As used in the specification of the present invention and the appended claims, the singular forms "a," "an," and "the" are intended to include the plural forms as well, unless the context clearly indicates otherwise.
The present invention is described in detail below:
fig. 2 is a schematic structural diagram of a transmitting rf coil unit according to an embodiment of the present invention, where the transmitting rf coil unit is located in an MR system, and the transmitting rf coil unit is wound by a conductor, and forms a central symmetry structure with a unique intersection point as a central symmetry point;
the two end points of the conductor are not connected, one end point is used for connecting the positive electrode of the coaxial feed through a feeder line, and the other end point is used for connecting the negative electrode of the coaxial feed through the feeder line;
and the transmitting radio frequency coil unit is positioned at the geometric center of the receiving radio frequency coil array and positioned on the same plane as the receiving radio frequency coil array.
As shown in fig. 2, the upper half 21 and the lower half 22 of the transmitting radio frequency coil unit are center-symmetrical with the intersection O as a center symmetry point.
One terminal a of a conductor constituting the transmitting radio frequency coil unit is connected to the positive electrode of the coaxial feed 23, and the other terminal B is connected to the negative electrode of the coaxial feed 23, so that the directions of magnetic lines of force of the upper half portion 21 and the lower half portion 22 are opposite when a current from the coaxial feed 23 passes through the conductor.
As shown in fig. 2, the transmitting radio frequency coil unit has two axes of symmetry 201 and 202.
Fig. 3 is a schematic diagram of a positional relationship between a transmitting rf coil unit and a receiving rf coil array according to an embodiment of the present invention, wherein the center of the transmitting rf coil unit coincides with the center of the receiving rf coil array, the transmitting rf coil unit and the receiving rf coil array are located on the same plane, and the outline of the transmitting rf coil unit does not exceed the overlapping area of the two receiving rf coil units at the geometric center of the receiving rf coil array.
As shown in fig. 3, the center of the overlapping area of the receiving radio frequency coil units 6 and 7 is the geometric center of the receiving radio frequency coil array, the center of the transmitting radio frequency coil unit overlaps with the center of the overlapping area, the transmitting radio frequency coil unit and the receiving radio frequency coil array are on the same plane, and the outline of the transmitting radio frequency coil unit does not exceed the overlapping area.
The structure of the transmitting radio frequency coil unit and the position relation between the transmitting radio frequency coil unit and the receiving radio frequency coil array can be seen: the structure of the transmitting radio frequency coil unit is centrosymmetric, the directions of magnetic lines of force of the two centrosymmetric parts are opposite, and the transmitting radio frequency coil unit is positioned at the geometric center of the receiving radio frequency coil array and is positioned on the same plane with the receiving radio frequency coil array, so that the receiving radio frequency coil unit is symmetrical with the transmitting radio frequency coil unit in pairs, and the coupling between the radio frequency coil units is effectively removed.
Alternatively, the transmitting rf coil unit is a butterfly structure, where two wings of the butterfly structure are centered at a unique intersection point (e.g., point O in fig. 2). The transmitting rf coil unit shown in fig. 2 is a butterfly structure.
In practical applications, to maximize the decoupling between the radio frequency coil units, for either of the two symmetry axes of the transmit radio frequency coil unit: such as symmetry axis 201 or 202 in fig. 2, which is parallel to the lateral or longitudinal edges of the receive radio frequency coil array. As shown in fig. 3, the axis of symmetry 201 of the transmit rf coil unit is parallel to the lateral edges of the receive rf coil array.
Fig. 4 is a schematic diagram of a positional relationship between a transmitting rf coil unit and a receiving rf coil array according to another embodiment of the present invention, wherein a symmetry axis 201 of the transmitting rf coil unit is parallel to a longitudinal edge of the receiving rf coil array.
For the transmitting rf coil units shown in fig. 3 and fig. 4, the self structure of the transmitting rf coil unit is central symmetry, and the directions of magnetic lines of force of two symmetrical parts are opposite, meanwhile, when the receiving rf coil array is also central symmetry, the receiving rf coil units in the receiving rf coil array are also central symmetry with respect to the transmitting rf coil unit, at this time, the decoupling effect is optimal, and the coupling between the rf coil units can be completely removed theoretically.
In addition, even for the receiving radio frequency coil array which is not symmetrically arranged relative to the transmitting radio frequency coil unit, the effect of effectively inhibiting coupling can be finally achieved due to the symmetry of the self structure of the transmitting radio frequency coil unit.
Fig. 5 is a schematic structural diagram of a transmitting rf coil unit according to another embodiment of the present invention, in which: the transmitting rf coil itself generates an additional inductance, and in order to eliminate the additional inductance, two tuning capacitors C1, C2, C1, C2 may be connected in series to the transmitting rf coil unit, where the capacitance values of the two tuning capacitors C1, C2 are equal, and the tuning capacitors C1, C2 are distributed on a symmetry axis of the transmitting rf coil unit passing through the coil unit, i.e. the symmetry axis 202 in fig. 2.
It should be noted that, experiments prove that after the transmitting radio frequency coil unit provided by the embodiment of the invention is adopted, the intensity of the respiratory signal acquired by the MR receiver is still very strong.
Table 1 shows the comparison results of the modulation depth of the respiration signal, wherein the modulation depth of the respiration signal is expressed by the ratio of the peak intensity to the trough intensity of the respiration signal, when the transmission RF coil unit provided by the embodiment of the invention is used for respiratory motion detection of the same volunteer and the RF coil unit shown in FIG. 1 is adopted.
TABLE 1
As can be seen from table 1: the transmitting radio frequency coil unit provided by the embodiment of the invention is used for respiratory motion detection, and compared with the radio frequency coil unit shown in fig. 1, the receiving channels with large modulation depth of respiratory signals are more, namely the strength of the respiratory signals is increased after the transmitting radio frequency coil unit provided by the embodiment of the invention is used.
The embodiment of the invention also provides an MR system comprising a transmitting radio frequency coil unit as described above.
The beneficial technical effects of the embodiment of the invention are as follows:
1. the structure of the transmitting radio frequency coil unit is centrosymmetric, the directions of magnetic lines of force of the two centrosymmetric parts are opposite, and the transmitting radio frequency coil unit is positioned at the geometric center of the receiving radio frequency coil array and is positioned on the same plane with the receiving radio frequency coil array, so that the receiving radio frequency coil unit is symmetrical with the transmitting radio frequency coil unit in pairs, and the coupling between the radio frequency coil units is effectively removed.
Further, when the transmitting radio frequency coil units are placed, any one of two symmetrical axes of the transmitting radio frequency coil units is parallel to the transverse edge or the longitudinal edge of the receiving radio frequency coil array, so that the number of the receiving radio frequency coil units which are symmetrical to each other in pairs relative to the transmitting radio frequency coil units in the receiving radio frequency coil array is further increased, and the decoupling effect is further improved; in particular, the decoupling effect is optimal in the case of a centrally symmetrical structure of the receiving radio frequency coil array itself.
In addition, even for the receiving radio frequency coil array which is not symmetrically arranged relative to the transmitting radio frequency coil unit, the effect of effectively inhibiting coupling can be finally achieved due to the symmetry of the transmitting radio frequency coil unit.
2. The coupling between the transmitting radio frequency coil unit and the receiving radio frequency coil array is reduced, so that the strength of a transmitting signal can be increased, the strength of a detected respiratory signal is increased, and the signal-to-noise ratio of the respiratory signal is improved.
3. The coupling between the transmitting RF coil unit and the receiving RF coil array is reduced, so that the requirement on the stability of the signal of the receiving channel is reduced, and the interference and drift problems commonly encountered by a motion (such as respiration) detection receiver are avoided.
The transmitting radio frequency coil unit and the MR system comprising the transmitting radio frequency coil unit provided by the embodiment of the invention can be applied to motion detection of respiration, heartbeat and the like.
While the invention has been illustrated and described in detail in the drawings and in the preferred embodiments, the invention is not limited to the disclosed embodiments, and it will be appreciated by those skilled in the art that the code audits of the various embodiments described above may be combined to produce further embodiments of the invention, which are also within the scope of the invention.
Claims (6)
1. A transmitting radio frequency coil unit located in a magnetic resonance MR system, characterized in that,
the transmitting radio frequency coil unit is formed by winding a conductor, and a central symmetrical structure is formed by taking a unique intersection point as a central symmetrical point;
the two end points of the conductor are not connected, one end point is used for connecting the positive electrode of the coaxial feed (23) through a feeder line, and the other end point is used for connecting the negative electrode of the coaxial feed (23) through the feeder line;
and the transmitting radio frequency coil unit is positioned at the geometric center of the receiving radio frequency coil array and positioned on the same plane as the receiving radio frequency coil array.
2. The transmitting radio frequency coil unit according to claim 1, wherein the transmitting radio frequency coil unit has a contour that does not exceed a region of coincidence of two receiving radio frequency coil units at a geometric center of the receiving radio frequency coil array.
3. The transmitting radio frequency coil unit according to claim 1, wherein the transmitting radio frequency coil unit has a butterfly structure, and two wings of the butterfly structure are centered on a single intersection point.
4. The transmitting radio frequency coil unit according to claim 1, characterized in that either symmetry axis (201, 202) of the transmitting radio frequency coil unit is parallel to a transversal or longitudinal side of the receiving radio frequency coil array.
5. The transmitting radio frequency coil unit according to claim 1, wherein two capacitors are connected in series in the radio frequency coil unit, the two capacitors are distributed on a symmetry axis (202) of the radio frequency coil unit passing through the coil unit, and capacitance values of the two capacitors are equal.
6. An MR system, characterized in that the system comprises a transmitting radio frequency coil unit as claimed in any one of claims 1 to 5.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201910752732.9A CN112394308B (en) | 2019-08-15 | 2019-08-15 | Transmitting radio frequency coil unit and magnetic resonance system |
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| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201910752732.9A CN112394308B (en) | 2019-08-15 | 2019-08-15 | Transmitting radio frequency coil unit and magnetic resonance system |
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| CN112394308A CN112394308A (en) | 2021-02-23 |
| CN112394308B true CN112394308B (en) | 2024-01-30 |
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