Transmitting and receiving integrated array coil and magnetic resonance equipment
By designing an integrated transceiver array coil, and utilizing M·N coil units and corresponding amplifiers and switches, efficient excitation and stable reception of large FOV imaging in an ultra-high field magnetic resonance system were achieved, solving the problems of low excitation efficiency and poor uniformity in traditional coil designs.
Patent Information
- Authority / Receiving Office
- CN · China
- Patent Type
- Utility models(China)
- Current Assignee / Owner
- SUZHOU MEDCOIL HEALTHCARE
- Filing Date
- 2025-05-22
- Publication Date
- 2026-05-15
AI Technical Summary
In ultra-high field magnetic resonance systems, traditional 1*N type loop array and dipole array excitation coil designs suffer from low excitation efficiency, poor uniformity, and sensitivity to load, making it difficult to achieve stable operation, especially in large FOV imaging.
It adopts an integrated transceiver array coil design, including M·N coil units, M·N preamplifiers, N power dividers and transceiver switching switches. By adjusting different RF transmit power and phase, it can achieve flexible switching and decoupling of coil units, thereby improving excitation uniformity and receiver signal-to-noise ratio.
It improves the uniformity and efficiency of the excitation region, enhances the stability of the coil to the load, and improves the signal-to-noise ratio in the receiving mode.
Smart Images
Figure CN224247910U_ABST
Abstract
Description
Technical Field
[0001] This application relates to the field of nuclear magnetic resonance technology, and in particular to a transceiver array coil and a magnetic resonance device. Background Technology
[0002] In ultra-high field magnetic resonance systems, such as the 7.0T system, the high radio frequency and shortened electromagnetic wavelength result in significant excitation inhomogeneity during large FOV imaging of the body. The excitation efficiency (the size of the B1 field generated under a certain load with the same power) also decreases significantly due to the increase in frequency, making it difficult to use sequences with large flip angles under safe radio frequency power pulses.
[0003] In systems with low to medium field strength, the most classic excitation coil unit design is the birdcage coil, which offers optimal uniformity and excitation efficiency at large fields of view (FOV). However, at ultra-high fields, due to the limitation of electrical length, tuning large-size birdcage coils becomes impossible. The industry has had to adopt new design approaches, such as... Figure 1 and Figure 2 As shown, loop arrays and dipole arrays are the most commonly used and effective excitation coil designs.
[0004] However, traditional 1*N loop arrays have significant drawbacks: the coil units are not square enough (the length-to-length ratio is relatively large), resulting in a significant reduction in excitation and reception efficiency; the large area of N loops makes them highly susceptible to load effects at ultra-high field frequencies, leading to unstable operation. 1*N dipole arrays (for excitation) also have obvious drawbacks: excessively low excitation efficiency, with the excitation field concentrated in the center, resulting in insufficient excitation at the head and feet. Summary of the Invention
[0005] In view of this, this application provides a transceiver integrated array coil and a magnetic resonance device.
[0006] In a first aspect, this application proposes a transceiver integrated array coil, comprising:
[0007] N coil unit groups are arranged along a first direction, and each coil unit group includes M coil units arranged along a second direction, wherein the first direction is perpendicular to the second direction, and M and N are both integers not less than 2;
[0008] M·N preamplifiers are connected one-to-one with M·N coil units;
[0009] N power dividers are connected to M coil units in different coil unit groups in a one-to-one correspondence with the N coil unit groups;
[0010] The M and N preamplifiers are used to connect to the receiver of the magnetic resonance device, and the N power dividers are used to connect to the N radio frequency power amplifiers in a one-to-one correspondence.
[0011] In some possible implementations, a transmit / receive switching switch is also included, which is configured to selectively place the coil unit in one of the following states:
[0012] Coupled to the preamplifier and decoupled from the power divider;
[0013] It is coupled to the power divider and decoupled from the preamplifier.
[0014] In some possible implementations, the number of transceiver switches is M·N, and the M·N transceiver switches are connected in a one-to-one correspondence with the M·N coil units, respectively between the corresponding coil unit and the preamplifier, and also between the corresponding coil unit and the power divider.
[0015] In some possible implementations, it also includes:
[0016] M·N phase shifters are connected to the respective transceiver switches and the power divider in a one-to-one correspondence with the M·N transceiver switches. The phase shifters are configured to adjust the phase difference between different coil units.
[0017] In some possible implementations, it also includes:
[0018] A phase shifter is configured to adjust the phase difference between different coil units.
[0019] In some possible implementations, for the M coil units in the same coil unit group, any two adjacent coil units are partially overlapped.
[0020] In some possible implementations, for adjacent first and second coil unit groups among the N coil unit groups:
[0021] The M coil units in the first coil unit group and the M coil units in the second coil unit group are partially overlapped in a one-to-one correspondence, or the M coil units in the first coil unit group and the M coil units in the second coil unit group are spaced apart along the first direction.
[0022] In some possible implementations, the first direction is the direction surrounding the inspected area.
[0023] In some possible implementations, the transceiver array coil is used to perform magnetic resonance imaging on the examined part of the subject, wherein the first direction is the direction surrounding the examined part, and the second direction is the length direction of the subject.
[0024] Secondly, a magnetic resonance imaging (MRI) device is proposed, comprising:
[0025] As described in the first aspect, the transceiver integrated array coil
[0026] The N radio frequency power amplifiers, and
[0027] The receiver.
[0028] According to the transceiver array coil provided in this application, when operating in transmit mode, coil units in different coil unit groups can be assigned different RF transmit powers, and each coil unit in the same coil unit group can be assigned the same RF transmit power. Furthermore, the coverage area of the array coil in the second direction can be increased by increasing the number of coil units in each coil unit group, without having to design the coil units into a long and narrow shape with a large aspect ratio. Therefore, this application can effectively increase the excitation area and uniformity, improve efficiency, alleviate the problem of excessive coil sensitivity to load, and help increase the received signal-to-noise ratio in receive mode. Attached Figure Description
[0029] To more clearly illustrate the technical solutions of the embodiments of this application, the accompanying drawings of the embodiments will be briefly described below. Obviously, the drawings described below only relate to some embodiments of this application, and are not intended to limit this application.
[0030] Figure 1 This is a structural block diagram of a traditional multi-source transceiver integrated array coil.
[0031] Figure 2 This is a structural block diagram of a traditional single-source transceiver integrated array coil.
[0032] Figure 3 This is a structural block diagram of the magnetic resonance device provided in the embodiments of this application.
[0033] Figure 4 This is a schematic diagram of the transceiver array coil provided in the embodiments of this application.
[0034] Figure 5 This is a schematic diagram of the transceiver array coil provided in the embodiments of this application.
[0035] Figure 6 This is a schematic diagram of the transceiver array coil provided in the embodiments of this application.
[0036] Explanation of reference numerals in the attached figures:
[0037] DR1 - First direction, DR2 - Second direction;
[0038] 1000-Magnetic Resonance Imaging Equipment;
[0039] 100-Transmitter / receiver integrated array coil;
[0040] 10-Coil unit group;
[0041] 1-Coil unit;
[0042] 2-Preamplifier;
[0043] 3-Power divider;
[0044] 4- Transceiver switch;
[0045] 5-RF power amplifier;
[0046] 6-Receiver. Detailed Implementation
[0047] To make the objectives, technical solutions, and advantages of this application clearer, the technical solutions of the embodiments of this application will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some, not all, of the embodiments of this application. Based on the described embodiments of this application, all other embodiments obtained by those skilled in the art without creative effort are within the scope of protection of this application. It is understood that, without conflict, some technical means of the various embodiments described herein can be substituted for or combined with each other.
[0048] In the description of this application, the terms "first," "second," etc., are used only to distinguish the described objects and have no sequential or technical meaning. Therefore, objects specified with "first," "second," etc., may explicitly or implicitly include one or more of those objects, and, for example, the term "first element" itself does not imply the existence of a "second element," nor does the term "second element" itself imply the existence of a "first element." Furthermore, words such as "a" or "one" do not indicate a quantity limitation, but rather indicate the presence of at least one, while "multiple" indicates not less than two.
[0049] Figure 3 The present invention illustrates a magnetic resonance device 1000 provided according to an embodiment of the present application. The magnetic resonance device 1000 includes a transceiver array coil 100, a receiver 6, and N radio frequency power amplifiers 5.
[0050] The transceiver array coil 100 can both transmit radio frequency signals to a subject's examination area (e.g., the body or limbs) to excite hydrogen nuclei within that area to generate magnetic resonance signals, and receive magnetic resonance signals from the subject's examination area, thereby performing magnetic resonance imaging on the subject's examination area. The transceiver array coil 100 includes M·N coil units 1, M·N preamplifiers 2, M·N transceiver switching switches 4, and N power dividers 3. See also... Figures 4 to 6 ,exist Figures 4 to 6 In the embodiment shown, M = 3 and N = 8. In other embodiments, M and N may be other integer values, but both should be no less than 2.
[0051] The M·N (i.e., 24) coil units 1 comprise N groups of N coil units 10 arranged along a first direction DR1, with each group containing M coil units 1 arranged along a second direction DR2. As described later, the first direction DR1 can be the direction surrounding the inspected area.
[0052] M·N preamplifiers 2 are connected one-to-one with M·N coil units 1, that is, each coil unit 1 is connected to a different preamplifier 2. Furthermore, all M·N preamplifiers 2 are connected to the receiver 6 of the magnetic resonance device 1000.
[0053] N power dividers 3 are connected to M coil units 1 in different coil unit groups 10 in a one-to-one correspondence with N coil unit groups 10. That is, each coil unit 1 in the same coil unit group 10 is connected to the same power divider 3, but different coil unit groups 10 correspond to different power dividers 3.
[0054] M·N transceiver switches 4 are connected one-to-one with M·N coil units 1, both between the corresponding coil unit 1 and the preamplifier 2, and between the corresponding coil unit 1 and the power divider 3. In other words, each coil unit 1 is connected to the corresponding preamplifier 2 via a different transceiver switch 4, and each coil unit 1 is connected to the corresponding power divider 3 via a different transceiver switch 4. Thus, by switching each transceiver switch 4 to different operating states, each coil unit 1 can be selectively coupled to the preamplifier 2 and decoupled from the power divider 3, or coupled to the power divider 3 and decoupled from the preamplifier 2, thereby allowing the array coil to selectively operate in transmit (excite) mode or receive mode.
[0055] The N radio frequency power amplifiers 5 of the magnetic resonance device 1000 are connected one-to-one with the N power dividers 3, so that each power divider 3 can independently provide different radio frequency power.
[0056] With this design, when the array coil operates in transmit mode, coil units 1 in different coil unit groups 10 can be assigned different RF transmit powers, and each coil unit 1 in the same coil unit group 10 can be assigned the same RF transmit power. Furthermore, the coverage area of the array coil in the second direction DR2 can be increased by increasing the number of coil units 1 in each coil unit group 10, without having to design the coil units 1 into a long, narrow shape with a large aspect ratio (the dimension of the second direction DR2 is longer, and the dimension of the first direction DR1 is shorter). Therefore, this design can effectively increase the excitation area and uniformity, improve efficiency, alleviate the problem of excessive coil sensitivity to load, and help increase the received signal-to-noise ratio in receive mode.
[0057] In some embodiments, M·N phase shifters can be configured, each connected to a corresponding transceiver switch 4 and the power divider 3 in a one-to-one correspondence with one of the M·N transceiver switches 4. The phase shifters can be used to adjust the phase difference between different coil units 1.
[0058] exist Figure 4 In the embodiment shown, for the M coil units 1 in the same coil unit group 10, any two adjacent coil units 1 are partially overlapped to achieve decoupling between the coil units 1 in the same coil unit group 10; and for each two adjacent coil unit groups 10, the M coil units 1 in one of the first coil unit groups 10 are partially overlapped with the M coil units 1 in the other coil unit group 10 in a one-to-one correspondence to achieve decoupling between the coil units 1 in different coil unit groups 10.
[0059] exist Figure 5 In another embodiment shown, for each pair of adjacent coil unit groups 10, M coil units 1 in one coil unit group 10 are separated from M coil units 1 in the other coil unit group 10 along the first direction DR1. By separating adjacent coil unit groups 10 by a certain distance, the coupling (decoupling) between different coil unit groups 10 can also be reduced.
[0060] exist Figure 6 In another embodiment shown, the transceiver array coil 100 includes two substantially symmetrical parts, which, in use, can cover the front and rear sides of the subject's body, respectively, to transmit radio frequency signals to the subject's body from the front and rear sides, or to receive magnetic resonance signals from the subject's body from the front and rear sides, respectively.
[0061] And in Figures 4 to 6In the various embodiments shown, the array coils can be configured to completely or partially surround the subject's examined portion. In this case, the first direction DR1 can be understood as the direction surrounding the examined part (e.g., the subject's body), and the second direction DR2 is the subject's length direction. Figures 4 to 6 This is the state after the array coils are flattened.
Claims
1. A transceiver integrated array coil, characterized in that, include: N coil unit groups are arranged along a first direction, and each coil unit group includes M coil units arranged along a second direction, wherein the first direction is perpendicular to the second direction, and M and N are both integers not less than 2; M·N preamplifiers are connected one-to-one with M·N coil units; N power dividers are connected to M coil units in different coil unit groups in a one-to-one correspondence with the N coil unit groups; The M and N preamplifiers are used to connect to the receiver of the magnetic resonance device, and the N power dividers are used to connect to the N radio frequency power amplifiers in a one-to-one correspondence.
2. The transceiver integrated array coil according to claim 1, characterized in that, It also includes a transmit / receive switching switch, which is configured to selectively place the coil unit in one of the following states: Coupled to the preamplifier and decoupled from the power divider; It is coupled to the power divider and decoupled from the preamplifier.
3. The transceiver integrated array coil according to claim 2, characterized in that, The number of transceiver switches is M·N. The M·N transceiver switches are connected to the corresponding coil units and the preamplifier, respectively, in a one-to-one correspondence with the M·N coil units. They are also connected to the corresponding coil units and the power divider.
4. The transceiver integrated array coil according to claim 3, characterized in that, Also includes: M·N phase shifters are connected to the respective transceiver switches and the power divider in a one-to-one correspondence with the M·N transceiver switches. The phase shifters are configured to adjust the phase difference between different coil units.
5. The transceiver integrated array coil according to claim 1, characterized in that, Also includes: A phase shifter is configured to adjust the phase difference between different coil units.
6. The transceiver integrated array coil according to claim 1, characterized in that, For the M coil units in the same coil unit group, any two adjacent coil units are partially overlapped.
7. The transceiver integrated array coil according to claim 1, characterized in that, For adjacent first and second coil unit groups in the N coil unit groups: The M coil units in the first coil unit group and the M coil units in the second coil unit group are partially overlapped in a one-to-one correspondence, or the M coil units in the first coil unit group and the M coil units in the second coil unit group are spaced apart along the first direction.
8. The transceiver integrated array coil according to claim 1, characterized in that, The first direction is the direction surrounding the inspected area.
9. The transceiver integrated array coil according to claim 1, characterized in that, The transceiver array coil is used to perform magnetic resonance imaging on the examined part of the subject. The first direction is the direction surrounding the examined part, and the second direction is the length direction of the subject.
10. A magnetic resonance imaging device, characterized in that, include: The transceiver integrated array coil as described in any one of claims 1 to 9, The N radio frequency power amplifiers, and The receiver.