Magnetic resonance imaging inductance resonance coil and application coil device

Abstract

The utility model discloses a magnetic resonance imaging inductance resonance coil and an application coil device, and the coil comprises a coil base material, a coil group, a conductor material, and at least one group of series combination A formed by an inductor La and two PIN diodes Va which are reversely connected in parallel, the series combination A is connected in parallel with a decoupling capacitor Ca and then is connected in series with a bridging capacitor C through a conductor material I to form an annular passive coil or a rectangular passive coil or other coil forms in any shape; the active coil at least comprises an annular active coil or a rectangular active coil or other coil forms in any shape; the passive coil and the active coil are regularly and symmetrically arranged in a crossed manner, the coils are mutually overlapped, the crossed points are mutually insulated, and the active coil is connected to signal receiving equipment through a lead interface after a pre-amplifier is arranged in the active coil, so that the integration greatly reduces the requirements on additional pre-amplifiers and eliminates the requirements on complex mixers and multiplexers.

Description

Technical Field

[0001] The utility model relates to the technical field of magnetic resonance imaging, and more specifically, the present application relates to a magnetic resonance imaging inductive resonance coil and an applied coil device. Background Art

[0002] In existing magnetic resonance imaging (MRI) systems, wired coil devices are used to participate in imaging. By using multiple coils to receive signals from the subject to be examined and process the signals to reduce the imaging time, the g-factor is a value determined by the position of the coil and the SENSE (sensitivity encoding) algorithm. Moreover, in the SENSE technology, it is known that the SNR (signal-to-noise ratio) is inversely proportional to the g-factor (geometric factor). The SWNSE technology is a parallel MRI, which is a technology that subsamples the phase encoding step length instead of receiving signals in parallel through multiple coils to reduce the imaging time. The g-factor is a value determined by the position of the coil and the SENSE algorithm.

[0003] The disadvantages of currently used coils include coupling loss, positioning limitation, size limitation, etc. The wired coil will generate coupling loss due to the impedance mismatch between the coil and the preamplifier, thereby reducing the signal-to-noise ratio (SNR) of the magnetic resonance imaging system. The cable length limits the coverage and accessibility of the wired coil. Wired coils often have large sizes and weights because they include various accessories such as connectors, preamplifiers, baluns, and plugs, which may increase the power consumption and heat dissipation of the magnetic resonance imaging system and enhance the discomfort of patients.

[0004] Wired MRI coils are crucial for high-quality imaging, but they also have obvious disadvantages:

[0005] 1. Volume and complexity: As the number of channels increases, the need for more wires and preamplifiers also increases, resulting in a cumbersome and complex setup. This complexity will hinder ease of use and increase the time required for setup and maintenance.

[0006] 2. High cost: The increase in the number of channels requires additional preamplifiers and wires, thus increasing the overall cost of the MRI system. In addition, mixers and multiplexers are usually required to manage numerous channels, which further increases the cost and complexity.

[0007] 3. Signal interference and quality: More wires and components will introduce potential sources of signal interference, affecting the quality of MRI images. Ensuring the harmonious operation of these components requires careful design and calibration. Summary of the Utility Model

[0008] A magnetic resonance imaging inductive resonant coil and an applied coil device proposed by the present utility model. The inductive resonator coil element provides a new solution to address the above challenges. These wireless coils operate based on inductive coupling and can transmit MRI signals without direct electrical connection.

[0009] To achieve the above object, the present utility model adopts the following technical solutions:

[0010] A magnetic resonance imaging inductive resonant coil and an applied coil device, the coil comprising:

[0011] A coil substrate, which is made of a flexible and MRI-compatible electrically insulating material into a planar material for attaching and fixing the coil;

[0012] A coil group, comprising a conductor material, and

[0013] At least one set of a series combination A consisting of an inductor L a and two anti-parallel PIN diodes V a After the series combination A is shunted with a decoupling capacitor C a and then a bridging capacitor C is serially connected through the conductor material one to form a circular passive coil or a rectangular passive coil or any other arbitrary-shaped coil form; and

[0014] At least one set of a series combination B consisting of an inductor L b and two anti-parallel PIN diodes V b After the series combination B is shunted with a decoupling capacitor C b and then a coil matching circuit is serially connected through the conductor material two to achieve a matching impedance with the minimum noise figure. The coil matching circuit is composed of an inductor L d and a capacitor C d connected in parallel. The coil matching circuit is shunted with a preamplifier to form a circular active coil or a rectangular active coil or any other arbitrary-shaped coil form;

[0015] The passive coils and the active coils are arranged symmetrically in a cross pattern, and the overlapping and crossing points of the coils are insulated from each other. The preamplifier in the active coil is connected to a signal receiving device through a wire interface.

[0016] Preferably, the preamplifiers in two adjacent sets of active coils are commonly connected to a mixer for signal combination and conversion, and the mixer is then connected to a signal receiving device through a wire interface;

[0017] Preferably, the conductor material is made of copper and is coated with an antioxidant material on the surface;

[0018] The coil group and the coil substrate are accommodated in a soft non-magnetic package to form a coil patch or a coil strip or a coil assembly cover.

[0019] An applied coil device comprising the above-mentioned coil patch or coil strip or coil assembly cover, comprising: a main magnetic field generator for generating a main magnetic field passing through the imaging region; a radio frequency exciter for applying radio frequency pulses of a certain frequency to the object to be imaged; and a signal receiver and an imaging display device, the region to be imaged covering the coil patch or coil strip or coil assembly cover, the radio frequency pulse magnetic field signal emitted by the radio frequency exciter forming a converted signal through the decoupling circuit of the coil patch or coil strip or coil assembly cover, and the converted signal being received and displayed by the signal receiver for imaging.

[0020] As can be seen from the above technical solutions, the present utility model has the following advantages:

[0021] 1. Reduction of wired components: By integrating the inductive resonator coil with the wired coil components, the number of wired coil components can be reduced by half or more. This integration greatly reduces the need for additional preamplifiers and eliminates the need for complex mixers and multiplexers;

[0022] 2. Simplified design and cost-effectiveness: Since there are fewer wired components, the MRI system becomes less bulky and complex. The reduced need for preamplifiers and multiplexers saves costs, making the system more economically feasible while maintaining or even enhancing its functions;

[0023] 3. Signal-to-noise ratio (SNR): The signal-to-noise ratio is a key determinant of the quality of MRI images. Hybrid coil systems have shown that they can maintain a high signal-to-noise ratio, which is crucial for clear and detailed imaging. Due to the efficient design of the inductive resonator coil, the reduction of wired components does not affect the signal quality. BRIEF DESCRIPTION OF THE DRAWINGS

[0024] Figure 1 is a schematic diagram of the basic layout of the present utility model;

[0025] Figure 2 is a schematic diagram of one layout of the present utility model;

[0026] Figure 3 is another schematic diagram of the layout of the present utility model;

[0027] Figure 4 is a schematic diagram of the lead connection of the active coil;

[0028] Figure 5 is a schematic diagram of the mixing connection of the active coil;

[0029] Figure 6 Schematic diagram of the equivalent of the passive coil or active coil;

[0030] Figure 7 is a schematic diagram of the layout of Embodiment 5;

[0031] Figure 8 is the layout schematic diagram of Embodiment VI;

[0032] Figure 9 is the layout schematic diagram of Embodiment VII;

[0033] Figure 10 is the layout schematic diagram of Embodiment VIII;

[0034] Figure 11 is the schematic diagram of the application scenario of the present utility model;

[0035] Figure 12 is the comparison diagram of the imaging effects of the UFL + inductance resonance combined coil and the single UFL. Detailed implementation manners

[0036] For the purpose of making the objectives, technical solutions and advantages of the embodiments of the present utility model clearer, the technical solutions in the embodiments of the present utility model will be clearly and completely described below with reference to the accompanying drawings in the embodiments of the present utility model. Obviously, the described embodiments are some, but not all, of the embodiments of the present utility model.

[0037] A magnetic resonance imaging inductance resonance coil, the coil comprising: a coil base material, which is made of a flexible and magnetically resonance-compatible electrically insulating material into a planar material for attaching and fixing the coil;

[0038] a coil group, which contains a conductor material, and

[0039] as Figure 1 shown, comprising a series combination A consisting of an inductor L a 1 and two PIN diodes V a 2 in reverse parallel connection. The series combination A is connected in parallel with a decoupling capacitor C a 3, and then connected in series with a bridging capacitor C4 through a conductor material 5 to form a ring-shaped passive coil; and

[0040] comprising a series combination B consisting of an inductor L b 6 and two PIN diodes V b 7 in reverse parallel connection. The series combination B is connected in parallel with a decoupling capacitor C b 8, and then connected in series with a coil matching circuit through a conductor material 9. The coil matching circuit is composed of an inductor L d 13 and a capacitor C d 12 in parallel connection. The coil matching circuit is connected in parallel with a preamplifier 10 to form a ring-shaped active coil; after the preamplifier 10 in the active coil, it is connected to a signal receiving device through a wire interface 11.

[0041] For the convenience of embodiment display, as Figure 6As shown, the passive coil and the active coil are simplified and equivalently processed. The combination of the active coil and the passive coil also effectively increases the coil coverage range, reduces the need for additional preamplifiers in traditional wired MRI coils, and eliminates the need for complex mixers and multiplexers. Embodiment

[0042] As Figure 2 shown, a magnetic resonance imaging inductive resonant coil includes a coil group and a coil substrate housed in a soft non-magnetic package, forming a coil patch.

[0043] A group of annular active coils are arranged symmetrically in a cross pattern on both sides with a group of annular passive coils on each side. Embodiment

[0044] As Figure 3 shown, a magnetic resonance imaging inductive resonant coil includes a coil group and a coil substrate housed in a soft non-magnetic package, forming a coil patch.

[0045] Three groups of annular passive coils are arranged symmetrically in a cross pattern around the annular active coil. Embodiment

[0046] As Figure 4 shown, a magnetic resonance imaging inductive resonant coil includes a coil group and a coil substrate housed in a soft non-magnetic package, forming a coil patch.

[0047] Two groups of annular active coils are arranged adjacent to each other in a cross pattern, and the preamplifier is separately led out on the same side. Annular passive coils are arranged on both sides of the axis direction away from the intersection point of the two groups of annular active coils. Embodiment

[0048] As Figure 5 shown, the same as the implementation method of Embodiment 3, the main difference is:

[0049] Two groups of annular active coils are arranged adjacent to each other in a cross pattern, and the preamplifier is separately led out on the same side and is commonly connected to the mixer, and the mixer is then connected to the signal receiving device through a wire interface. Embodiment

[0050] As Figure 7 shown, a magnetic resonance imaging inductive resonant coil includes a coil group and a coil substrate housed in a soft non-magnetic package, forming a coil strip.

[0051] It includes a coil strip composed of multiple groups of coil patch layouts arranged in a parallel cross single row as shown in Embodiment 1. Embodiment

[0052] As Figure 8A magnetic resonance imaging inductive resonance coil as shown includes a coil group and a coil substrate accommodated in a soft non-magnetic package, forming a coil strip.

[0053] It includes multiple groups of coil strips formed by arranging coil patches in a parallel-crossed single arrangement as shown in Embodiment 2. Embodiment

[0054] Such as Figure 9 A magnetic resonance imaging inductive resonance coil as shown includes a coil group and a coil substrate accommodated in a soft non-magnetic package, forming a coil strip.

[0055] It includes multiple groups of coil strips formed by arranging coil patches in a parallel-crossed double arrangement as shown in Embodiment 1. Embodiment

[0056] Such as Figure 10 A magnetic resonance imaging inductive resonance coil as shown includes a coil group and a coil substrate accommodated in a soft non-magnetic package, forming a coil assembly cover.

[0057] It includes multiple groups of coil assembly covers formed by arranging coil patches in a parallel-crossed three-dimensional enclosure as shown in Embodiment 3.

[0058] Similar to Embodiment 5, Embodiment 6, Embodiment 7, or Embodiment 8, respectively combined with Embodiment 4, the adjacent active coils are jointly led out by a mixer, further reducing the need for additional preamplifiers.

[0059] Such as Figure 10 Or in the application scenario of the head shown in 11, the area to be imaged covers the coil assembly cover. The radio frequency pulse magnetic field signal emitted by the radio frequency exciter forms a converted signal through the decoupling circuit of the coil assembly cover, and the converted signal is then received and displayed for imaging by the signal receiver.

[0060] The integration of a wired MRI coil and an inductive resonator coil element provides a promising solution to the challenges brought by traditional wired coil systems. By reducing the number of wired components and related preamplifiers, this hybrid approach simplifies the MRI setup, reduces costs, and maintains high standards of imaging performance.

[0061] The preliminary tests of the inductive resonance coil system have shown promising results in several key performance aspects;

[0062] Parallel imaging ability: The integration of inductive resonator coils has proven to have enhanced parallel imaging ability. By efficiently managing multiple channels wirelessly, the system can capture high-quality images faster, which is particularly beneficial for dynamic studies and reducing patient scan time.

[0063] Image uniformity: Maintaining image uniformity is crucial for accurate diagnosis. Our preliminary tests have shown that as Figure 12, on the left is the UFL + inductive resonance combined coil, and on the right is the UFL only. Under the same conditions: the combined coil system provides consistent image uniformity, comparable to that of traditional wired systems. The inductive element does not introduce significant artifacts or signal intensity variations across the entire imaging field.

[0064] The above embodiments are only used to illustrate the technical solutions of the present invention, rather than to limit it; although the present invention has been described in detail with reference to the foregoing embodiments, those of ordinary skill in the art should understand that: they can still modify the technical solutions recorded in the foregoing embodiments, or perform equivalent replacements on some of the technical features; and these modifications or replacements do not cause the essence of the corresponding technical solutions to deviate from the spirit and scope of the technical solutions of the embodiments of the present invention.

Claims

1. An inductive resonance coil for magnetic resonance imaging, characterized in that, The coil includes: A coil substrate, which is made of a flexible and MRI-compatible electrical insulating material into a planar material for attaching coil fixation; A coil group, including a conductor material, and Comprising at least one set of an inductor L a and two PIN diodes V connected in antiparallel a to form a series combination A, and a decoupling capacitor C is connected in parallel with the series combination A a and then a bridging capacitor C is connected in series through a conductor material to form a loop-shaped passive coil or a rectangular passive coil; and Comprising at least one set of an inductor L b and two PIN diodes V connected in antiparallel b in series combination B, and a decoupling capacitor C is connected in parallel with series combination B b and then a coil matching circuit is connected in series through a conductor material two to achieve a matching impedance with the minimum noise figure, and the coil matching circuit is connected in parallel with a preamplifier to form a loop active coil or a rectangular active coil; The passive coils and active coils are arranged symmetrically in a cross pattern, and the overlapping intersection points of the coils are insulated from each other. After the preamplifier in the active coils, it is connected to the signal receiving device through a wire interface.

2. The inductive resonant coil for magnetic resonance imaging according to claim 1, wherein The coil matching circuit consists of an inductor L d and a capacitor C d connected in parallel.

3. A magnetic resonance imaging inductive resonant coil according to claim 1, wherein The preamplifiers in two adjacent groups of active coils are commonly connected to a mixer, and the mixer is then connected to the signal receiving device through a wire interface.

4. The MRI inductive resonance coil according to claim 1 or 2 or 3, wherein The conductor material is made of copper and is coated with an antioxidant material on the surface.

5. The MRI inductive resonance coil according to claim 1 or 2 or 3, wherein The coil group and the coil substrate are accommodated in a soft non-magnetic package to form a coil patch or a coil strip or a coil assembly cover.

6. An applied coil device, comprising the magnetic resonance imaging inductive resonant coil according to any one of claims 1-5, further comprising: A main magnetic field generator for generating a main magnetic field passing through the imaging region; A radio frequency exciter for applying a radio frequency pulse of a certain frequency to the object to be imaged; And a signal receiver and an imaging display device, wherein: The coil group and the coil substrate are accommodated in a soft non-magnetic package to form a coil patch or a coil strip or a coil assembly cover; The region to be imaged covers the coil patch or the coil strip or the coil assembly cover. The radio frequency pulse magnetic field signal emitted by the radio frequency exciter forms a conversion signal through the decoupling circuit of the coil patch or the coil strip or the coil assembly cover, and the conversion signal is then received and displayed for imaging by the signal receiver.

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