Multinuclear magnetic resonance scanning device

Abstract

This application provides a multi-nucleus magnetic resonance imaging (MRI) device, belonging to the field of medical device technology. A multi-nucleus radio frequency (RF) transmitting unit is used to generate RF signals from at least two different nuclides. A gradient magnetic field unit is used to provide the gradient magnetic field required for spatial encoding. A multi-nucleus RF receiving unit is used to receive echo signals from different nuclides. A control unit is configured to adjust the timing sequence of the multi-nucleus RF transmitting unit, the multi-nucleus RF receiving unit, and the gradient magnetic field unit to achieve parallel excitation and synchronous reception of at least two different nuclides. Through the multi-nucleus RF transmitting unit, the gradient magnetic field unit, the multi-nucleus RF receiving unit, and the control unit in this application, parallel excitation of RF signals from at least two different nuclides and synchronous reception of echo signals from different nuclides are achieved, reducing the number of excitations and reception time required for imaging, improving imaging speed, and solving the problem of slow imaging speed in traditional devices.

Description

Technical Field

[0001] This application belongs to the field of medical device technology, and in particular relates to a multinucleus magnetic resonance scanning device. Background Technology

[0002] Magnetic resonance imaging (MRI) is an analytical and detection technique based on the physical phenomenon of the magnetism of atomic nuclei and their interaction with an external magnetic field. MRI offers advantages such as non-invasiveness, high safety, strong soft tissue resolution, and the ability to image any plane and observe from any angle, making it widely used in fields such as chemistry, biomedicine, and materials science.

[0003] However, traditional devices rely on time-division multiplexing or alternating acquisition at the receiving end, which results in slow magnetic resonance imaging. Utility Model Content

[0004] The purpose of this application is to provide a multi-nuclear magnetic resonance scanning device, which aims to solve the problem of slow imaging speed in traditional multi-nuclear magnetic resonance scanning devices.

[0005] This application provides a multinuclear magnetic resonance scanning device, comprising:

[0006] A multi-nucleoside radio frequency transmitting unit is used to generate radio frequency signals of at least two different nuclides;

[0007] Gradient magnetic field unit, used to provide the gradient magnetic field required for spatial encoding;

[0008] A multi-nucleus radio frequency receiving unit is used to receive the echo signals of the different nuclides;

[0009] The control unit is configured to adjust the timing sequence of the multi-nucleus radio frequency transmitting unit, the multi-nucleus radio frequency receiving unit, and the gradient magnetic field unit to achieve parallel excitation and synchronous reception of at least two different nuclides.

[0010] In one embodiment, the multi-nucleoside radio frequency receiving unit includes a parallel processing unit for digitizing the received echo signal.

[0011] In one embodiment, the parallel processing unit includes multiple independent processing cores, each of which performs the digitization processing of the echo signal of a nuclide.

[0012] In one embodiment, the parallel processing unit includes:

[0013] At least two separate radio frequency receiving channels, each of which receives the echo signal of a nuclide and performs digital processing accordingly;

[0014] The radio frequency receiving channel includes at least a signal processing module, a filtering and frequency conversion processing module, and an acquisition and control module.

[0015] In one embodiment, the filtering and frequency conversion processing module is connected to the receiving signal processing module and is used to perform filtering and frequency conversion processing on the digital signal according to the filtering coefficient and frequency conversion parameters corresponding to each nuclide to obtain the signal to be imaged.

[0016] In one embodiment, the filter frequency conversion processing module includes:

[0017] An extraction module is used to extract data from the frequency conversion signal to obtain the signal to be imaged;

[0018] The communication parsing module is used to send the radio frequency coil identifier to the digital filtering module and the down-conversion processing module to determine the filtering coefficient and the conversion parameter corresponding to each nuclide;

[0019] The communication parsing module is connected to the extraction module and is used to acquire the imaging signal corresponding to each nuclide.

[0020] In one embodiment, the multi-nucleoside radio frequency transmitting unit includes:

[0021] At least two separate radio frequency (RF) transmitting modules, each of which is connected to the control unit and the RF coil module, for transmitting RF signals of the corresponding nuclide to the RF coil module according to the sequence timing.

[0022] In one embodiment, each of the radio frequency transmitting modules includes:

[0023] A radio frequency signal generation module, which is connected to the control unit, is used to generate a digital pulse signal for each nuclide according to the sequence timing and the radio frequency coil identifier;

[0024] A transmission signal processing module, which is connected to the radio frequency signal generation module, is used to process the digital pulse signal to obtain the radio frequency signal corresponding to each nuclide.

[0025] In one embodiment, the acquisition control module is connected to the control unit and is used to acquire the sequence timing and radio frequency coil identifier. The acquisition control module controls the synchronous reception of the receiving signal processing module according to the sequence timing.

[0026] In one embodiment, the control unit is connected to the radio frequency transmitting module and is used to send the radio frequency coil identifier to the radio frequency transmitting module and control the parallel excitation of the radio frequency transmitting module according to the sequence timing.

[0027] The beneficial effects of this utility model embodiment compared with the prior art are:

[0028] The multi-nucleoside radio frequency (RF) transmitter unit can generate RF signals from at least two different nuclides, or from three or more different nuclides. Each nuclide corresponds to one RF signal. The timing sequence of the multi-nucleoside RF transmitter unit, the multi-nucleoside RF receiver unit, and the gradient magnetic field unit can be adjusted via the control unit. The timing sequence includes the sequence information and timing control information required for magnetic resonance imaging (MRI). The sequence information can be understood as a series of combinations of RF signals, gradient magnetic fields, and signal reception and acquisition sequences formed according to different clinical needs and imaging purposes, such as spin echo sequences, gradient echo sequences, or gradient echo sequences, which can be adjusted according to actual needs. The timing control information can be understood as the time parameters and execution order of each sequence combination in the sequence information, ensuring precise timing control of the RF signals, gradient magnetic fields, and signal reception and acquisition.

[0029] The multi-nucleus radio frequency (RF) transmitting unit transmits RF signals of at least two different nuclides in a single transmission and provides the gradient magnetic field required for spatial encoding through a gradient magnetic field unit. This enables selective parallel excitation of different layers or regions within the target area, generating excitation signals at multiple spatial locations, reducing the number of excitations required for imaging and shortening the scanning time. Consequently, the multi-nucleus RF receiving unit simultaneously receives echo signals from different nuclides at different spatial locations, achieving the reception of echo signals from at least two different nuclides in a single transmission. This reduces the reception time required for imaging and avoids the time consumption of traditional point-by-point acquisition.

[0030] Thus, through the multi-nucleus radio frequency transmitting unit, gradient magnetic field unit, multi-nucleus radio frequency receiving unit and control unit in the multi-nucleus magnetic resonance scanning device provided in this application, parallel excitation of radio frequency signals of at least two different nuclides and synchronous reception of echo signals of different nuclides are realized, reducing the number of excitations and reception time required for imaging, improving imaging speed, and solving the problem of slow imaging speed of traditional devices. Attached Figure Description

[0031] To more clearly illustrate the technical solutions in the embodiments of this application, the drawings used in the description of the embodiments or exemplary technologies will be briefly introduced below. Obviously, the drawings described below are only some embodiments of this application. For those skilled in the art, other drawings can be obtained based on these drawings without creative effort.

[0032] Figure 1 The following are schematic diagrams of the structure of the multinuclear magnetic resonance scanning device in some embodiments provided in this application.

[0033] Figure 2The following are schematic diagrams of the structure of the multi-nucleoside radio frequency receiving unit in some embodiments provided in this application.

[0034] Figure 3 The following are schematic diagrams of the structure of the multi-nucleoside radio frequency emission unit in some embodiments provided in this application.

[0035] Figure 4 The following are schematic diagrams of the imaging reconstruction module and data storage module in some embodiments provided in this application. Detailed Implementation

[0036] To make the technical problems, technical solutions, and beneficial effects to be solved by this application clearer, the following detailed description is provided in conjunction with the accompanying drawings and embodiments. It should be understood that the specific embodiments described herein are merely illustrative and are not intended to limit the scope of this application.

[0037] It should be noted that when a component is referred to as being "fixed to" or "set on" another component, it can be directly on or indirectly on that other component. When a component is referred to as being "connected to" another component, it can be directly connected to or indirectly connected to that other component.

[0038] It should be understood that the terms "length", "width", "upper", "lower", "front", "rear", "left", "right", "vertical", "horizontal", "top", "bottom", "inner", "outer", etc., indicate the orientation or positional relationship based on the orientation or positional relationship shown in the accompanying drawings. They are only for the convenience of describing this application and simplifying the description, and do not indicate or imply that the device or element referred to must have a specific orientation, or be constructed and operated in a specific orientation. Therefore, they should not be construed as limitations on this application.

[0039] Furthermore, the terms "first" and "second" are used for descriptive purposes only and should not be construed as indicating or implying relative importance or implicitly specifying the number of technical features indicated. Thus, a feature defined as "first" or "second" may explicitly or implicitly include one or more of that feature. In the description of this application, "multiple" means two or more, unless otherwise explicitly specified.

[0040] Please see Figure 1This application provides a multi-nucleus magnetic resonance scanning device 100. The multi-nucleus magnetic resonance scanning device 100 includes a multi-nucleus radio frequency transmitting unit, a gradient magnetic field unit, a multi-nucleus radio frequency receiving unit, and a control unit 60. The multi-nucleus radio frequency transmitting unit is used to generate radio frequency signals of at least two different nuclides. The gradient magnetic field unit is used to provide the gradient magnetic field required for spatial encoding. The multi-nucleus radio frequency receiving unit is used to receive echo signals from different nuclides. The control unit 60 is configured to adjust the sequence timing of the multi-nucleus radio frequency transmitting unit, the multi-nucleus radio frequency receiving unit, and the gradient magnetic field unit to achieve parallel excitation and synchronous reception of at least two different nuclides.

[0041] In this embodiment, the multi-nucleoside radio frequency (RF) transmitting unit can generate RF signals from at least two different nuclides, or from three or more different nuclides. Each nuclide corresponds to one RF signal. The control unit 60 can adjust the timing sequence of the multi-nucleoside RF transmitting unit, the multi-nucleoside RF receiving unit, and the gradient magnetic field unit. The timing sequence includes the sequence information and timing control information required for magnetic resonance imaging. The sequence information can be understood as a series of combinations of RF signals, gradient magnetic fields, and signal reception and acquisition sequences formed according to different clinical needs and imaging purposes, such as spin echo sequences, gradient echo sequences, or gradient echo sequences, which can be adjusted according to actual needs. The timing control information can be understood as the time parameters and execution order of each sequence combination in the sequence information to ensure precise timing control of the RF signals, gradient magnetic fields, and signal reception and acquisition.

[0042] The multi-nucleus radio frequency (RF) transmitting unit transmits RF signals of at least two different nuclides in a single transmission and provides the gradient magnetic field required for spatial encoding through a gradient magnetic field unit. This enables selective parallel excitation of different layers or regions within the target area, generating excitation signals at multiple spatial locations, reducing the number of excitations required for imaging and shortening the scanning time. Consequently, the multi-nucleus RF receiving unit simultaneously receives echo signals from different nuclides at different spatial locations, achieving the reception of echo signals from at least two different nuclides in a single transmission. This reduces the reception time required for imaging and avoids the time consumption of traditional point-by-point acquisition.

[0043] Thus, through the multi-nucleus radio frequency transmitting unit, gradient magnetic field unit, multi-nucleus radio frequency receiving unit and control unit 60 in the multi-nucleus magnetic resonance scanning device 100 provided in this application, parallel excitation of radio frequency signals of at least two different nuclides and synchronous reception of echo signals of different nuclides are realized, reducing the number of excitations and reception time required for imaging, improving imaging speed, and solving the problem of slow imaging speed of traditional devices.

[0044] In one embodiment, the multi-nucleoside radio frequency receiving unit includes a parallel processing unit for digitizing the received echo signal.

[0045] In this embodiment, the parallel processing unit can simultaneously receive and process echo signals corresponding to multiple different nuclides, realizing the digital processing of multiple data streams. Furthermore, the parallel processing unit can synchronously and parallelly receive echo signals from different nuclides and synchronously and parallelly digitize them, achieving fully digital data processing of the echo signals. Thus, by digitizing the received echo signals, the accuracy and anti-interference capability of the echo signal processing are improved, analog distortion is avoided, and the stability of the digital signal is higher. This solves the problems of noise accumulation and signal distortion caused by the reliance on analog circuits for signal processing in traditional devices.

[0046] In one embodiment, the parallel processing unit includes multiple independent processing cores, each processing core corresponding to the digital processing of the echo signal of a nuclide.

[0047] In this embodiment, each processing core has its own logic resources, registers, and local memory, enabling it to independently perform digitization processing of the echo signals of a corresponding nuclide. Furthermore, multiple processing cores can perform digitization processing of their respective echo signals without waiting for each other. Through multiple independent processing cores, the digitization processing of echo signals from various different nuclides can run simultaneously and independently, offering greater flexibility and efficiency.

[0048] In one embodiment, the parallel processing unit can be a Field-Programmable Gate Array (FPGA), a Multi-core Application-Specific Integrated Circuit (ASIC), or a Multi-core Central Processing Unit (CPU). Multiple independent processing cores are computing units within an FPGA, ASIC, or CPU that can run simultaneously and independently.

[0049] In one embodiment, the parallel processing unit includes at least two discrete radio frequency (RF) receiving channels. Each RF receiving channel receives the echo signal of a specific nuclide and performs digitization processing. Each RF receiving channel includes at least a received signal processing module 30, a filtering and frequency conversion processing module 40, and an acquisition control module 70.

[0050] In this embodiment, the receiving signal processing module 30 receives the echo signal and amplifies and performs analog-to-digital conversion on the echo signal to obtain a digital signal. The filtering and frequency conversion processing module 40 is connected to the receiving signal processing module 30. According to the filtering coefficient and frequency conversion parameters corresponding to each nuclide, it performs filtering and frequency conversion processing on the digital signal to obtain the signal to be imaged. The acquisition control module 70 is connected to the filtering and frequency conversion processing module 40, enabling the transmission and exchange of various data between the two, as well as the control and analysis of related equipment and operations. Thus, a radio frequency receiving channel is formed by the receiving signal processing module 30, the filtering and frequency conversion processing module 40, and the acquisition control module 70, which receives the echo signal of a corresponding nuclide and performs digital processing.

[0051] In one embodiment, the receiving signal processing module 30 is used to receive the echo signal and amplify and perform analog-to-digital conversion on the echo signal to obtain a digital signal.

[0052] In this embodiment, the echo signal received by each receiving signal processing module 30 is relatively weak. Amplifying the echo signal by the receiving signal processing module 30 increases its signal strength, improving the signal-to-noise ratio to match subsequent processing circuits. Performing analog-to-digital conversion on the amplified echo signal by the receiving signal processing module 30 improves signal processing accuracy and stability, facilitating processing by the subsequent filtering and frequency conversion module 40, and enabling data storage and transmission.

[0053] By using at least two receiving signal processing modules 30, echo signals from different nuclides can be received synchronously, and the echo signals can be amplified and converted from analog to digital to obtain digital signals. This enables fully digital data processing of the echo signals, improves the anti-interference capability during echo signal processing, avoids analog distortion, and makes the digital signals more stable. It also solves the problems of noise accumulation and signal distortion caused by the reliance on analog circuits for signal processing in traditional devices.

[0054] Furthermore, by directly receiving echo signals from different nuclides through at least two receiving signal processing modules 30, direct front-end acquisition is achieved, allowing the echo signals to directly enter the receiving acquisition circuit. In other words, an ADC is used to directly convert the analog echo signals into digital signals. Compared to indirect acquisition structures such as quadrature demodulators in traditional devices, the direct front-end acquisition structure provided in this application ensures high signal fidelity, strong real-time performance, and is simple and efficient. It is also more conducive to improving the accuracy of echo signals from multiple different nuclides, resulting in higher accuracy in magnetic resonance imaging.

[0055] In one embodiment, the filtering and frequency conversion processing module 40 is connected to the receiving signal processing module 30 and is used to perform filtering and frequency conversion processing on the digital signal according to the filtering coefficient and frequency conversion parameters corresponding to each nuclide to obtain the signal to be imaged.

[0056] In this embodiment, a filtering and frequency conversion processing module 40 is connected to a receiving signal processing module 30. Each filtering and frequency conversion processing module 40 is used to perform filtering and frequency conversion processing on the digital signal according to the filtering coefficient and frequency conversion parameters corresponding to each nuclide to obtain the signal to be imaged. The filtering and frequency conversion processing module 40 can determine the amplitude frequency response and phase frequency response according to the filtering coefficient corresponding to each nuclide, so that the digital signal in the frequency range corresponding to each nuclide can pass smoothly, and while meeting the amplitude frequency response requirements, the phase distortion is reduced.

[0057] The filtering and frequency conversion processing module 40, based on the frequency conversion parameters corresponding to each nuclide, can reduce the frequency of the digital signal from a high frequency range to a low frequency range, achieving down-conversion processing. This facilitates signal processing and analysis, enhances anti-interference capabilities, and improves signal transmission and storage. After undergoing fully digital data processing by the filtering and frequency conversion processing module 40, the digital signal exhibits advantages such as high precision and strong anti-interference capabilities, avoiding analog distortion and obtaining a more accurate imaging signal, thus achieving a more accurate reconstructed magnetic resonance image.

[0058] Thus, by using the receiving signal processing module 30 and the filtering and frequency conversion processing module 40 in the multi-nucleoside RF receiving unit, the echo signal is fully digitally processed, solving the problems of noise accumulation and signal distortion caused by the traditional device's receiving link relying on analog circuits for signal processing.

[0059] In one embodiment, the multi-nuclear magnetic resonance scanning device 100 further includes at least two radio frequency coil modules 20. Each receiving signal processing module 30 is connected to each radio frequency coil module 20. The receiving signal processing module 30, connected to the radio frequency coil module 20, amplifies and performs analog-to-digital conversion on the echo signal, enabling direct front-end acquisition so that the echo signal directly enters the receiving acquisition circuit of the receiving signal processing module 30.

[0060] In one embodiment, each RF coil module 20 may include a pair of RF coils, namely an RF transmitting coil and an RF receiving coil. Each RF coil module 20 may also include a transceiver coil, using an RF switch to switch between transmitting and receiving functions. The RF coil module 20 can be adjusted and selected according to the actual application scenario. The RF coil module 20 can be selected as a volume transmit coil (VTC) or an LC coil, depending on the sequence information.

[0061] In one embodiment, multiple radio frequency (RF) coil modules 20 are identical. Each coil interface in the bedside setup supports data acquisition from up to 24 channels. Based on the required imaging sequence timing and multiple RF coil identifiers, multiple nuclides, corresponding RF signals, and multiple RF coil modules 20 are configured for different RF coil identifiers. Furthermore, the multiple RF coil modules 20 can adapt to different nuclide transmission and reception based on the different matching of RF coil identifiers and RF signals. All coil interfaces can support various different nuclide coils.

[0062] Please see Figure 2 In one embodiment, the receiving signal processing module 30 includes a wideband RF preamplifier module 310 and an analog-to-digital converter module 320. The wideband RF preamplifier module 310 amplifies the echo signal to obtain an amplified echo signal. The analog-to-digital converter module 320 is connected to the wideband RF preamplifier module 310 and performs analog-to-digital conversion on the amplified echo signal to obtain a digital signal.

[0063] In this embodiment, the broadband RF preamplifier module 310 can be a broadband RF receiver with high sensitivity and low noise. The wide frequency response range obtained by amplifying the echo signal through the broadband RF preamplifier module 310 allows for stable amplification of signals corresponding to different resonant frequencies of different nuclides, thereby improving signal detection sensitivity and signal strength.

[0064] The analog-to-digital converter (ADC) module 320 is connected to the broadband RF preamplifier module 310 and is used to perform analog-to-digital conversion on the amplified echo signal to obtain a digital signal, which is then sent to the digital filter module 410. The ADC module 320 converts the analog characteristics of the amplified echo signal output from the broadband RF preamplifier module 310 into digital characteristics to obtain a digital signal, thereby improving signal processing accuracy and facilitating signal storage and transmission. The ADC module 320 can be an analog-to-digital converter.

[0065] At least two receiving signal processing modules 30 can each receive echo signals from at least two channels of at least two nuclides. Within each receiving signal processing module 30, the echo signals received by the broadband RF preamplifier module 310 are uniformly amplified and converted from analog to digital, eliminating the need to process any specific nuclide. Thus, the compatibility of the receiver end of the multi-nucleus magnetic resonance scanning device 100 is improved through the broadband RF preamplifier module 310 and the analog-to-digital converter module 320.

[0066] Furthermore, the broadband RF preamplifier module 310 directly receives the echo signal, realizing direct front-end acquisition, allowing the echo signal to directly enter the broadband RF preamplifier module 310 and the analog-to-digital converter module 320. Compared with the indirect acquisition structure through quadrature demodulators and other methods in traditional devices, the direct front-end acquisition structure adopted by the multi-nucleus magnetic resonance scanning device 100 provided in this application can ensure high signal fidelity, strong real-time performance, and simplicity and efficiency of the nuclear magnetic resonance signal, which is more conducive to improving the accuracy of the echo signals of multiple nuclides, resulting in higher accuracy of magnetic resonance imaging.

[0067] In one embodiment, a broadband RF preamplifier module 310 is connected to an RF coil module 20. Multiple identical receiving signal processing modules 30 do not require matching to a specific nuclide and can arbitrarily acquire and process echo signals from different types of nuclides. The multi-nucleus magnetic resonance scanning device 100 provided in this application comprises a receiving signal processing module 30, a filtering and frequency conversion processing module 40, and an acquisition control module 70 forming an RF receiving channel, and an RF transmitting module 10 forming an RF transmitting channel. The RF transmitting module 10, RF coil module 20, receiving signal processing module 30, and filtering and frequency conversion processing module 40 form one RF channel to excite and receive the magnetic resonance signal of one nuclide. Multiple RF transmitting modules 10, multiple RF coil modules 20, multiple receiving signal processing modules 30, and multiple filtering and frequency conversion processing modules 40 can form multiple RF channels to excite and receive echo signals corresponding to multiple nuclides. Each RF channel is independent of the others, and nuclides can be arbitrarily matched, enabling parallel excitation and synchronous reception of at least two different nuclides under the sequence timing requirements of imaging, making it more flexible than traditional devices.

[0068] In one embodiment, the broadband RF preamplifier module 310 can be a unified broadband RF circuit, capable of covering the frequency bands of all target nuclides. It does not require matching to a specific nuclide and can freely acquire and process echo signals from different types of nuclides, improving the compatibility of the receiver of the multi-nucleus magnetic resonance scanning device 100. Furthermore, in the subsequently connected digital filtering module 410 and down-conversion processing module 420, the filtering coefficients and conversion parameters corresponding to each nuclide are determined by RF coil identifiers, enabling the differentiation of different nuclides through software-set filtering coefficients and conversion parameters.

[0069] In one embodiment, the broadband RF preamplifier module 310 can also be a front-end dedicated RF circuit, which can be understood as a circuit customized and optimized for each nuclide, processing the characteristic signal frequency band of the corresponding nuclide, realizing the use of different front-end dedicated RF circuits for different nuclides, and having the advantages of high sensitivity and low power consumption.

[0070] In one embodiment, each filter-conversion processing module 40 includes a digital filtering module 410 and a down-conversion processing module 420. The digital filtering module 410 is connected to the received signal processing module 30 and is used to filter the digital signal according to the filtering coefficients to obtain a digital filtered signal. The down-conversion processing module 420 is connected to the digital filtering module 410 and is used to perform down-conversion processing on the digital filtered signal according to the conversion parameters to obtain a frequency-converted signal.

[0071] In this embodiment, the digital filtering module 410 filters the digital signal according to filtering coefficients to obtain a digital filtered signal. The digital filtering module 410 includes multiple filtering coefficients. In one embodiment, the digital filtering module 410 includes... 1 H, 2 H, 3 He 9 Li, 13 C 17 O、 19 F, 23 Na、 31 P and 129 Multiple filter coefficients are available for more than 10 nuclides, including Xe. These filter coefficients determine the filtering effect on the input digital signal. Different filter coefficients will achieve different filtering effects.

[0072] The digital filtering module 410 selects the required filtering coefficients for the corresponding nuclide. Then, the digital filtering module 410 filters the digital signal according to the filtering coefficients. Each digital filtering module 410 can perform different digital filtering functions depending on the different filtering coefficients, and can filter frequencies corresponding to different nuclides. Regardless of the corresponding nuclide, the digital filtering function can be achieved through the digital filtering module 410. Therefore, the analog-to-digital converter module 320, the broadband RF preamplifier module 310, and the RF coil module 20 connected to the digital filtering module 410 do not need to be matched with a fixed nuclide; different types of nuclides can be freely selected and connected without affecting the filtering function of the digital filtering module 410 on the digital signal.

[0073] The down-conversion processing module 420 is connected to the digital filtering module 410 and is used to perform frequency conversion processing on the digital signal according to the frequency conversion parameters to obtain a frequency-converted signal. The frequency conversion parameters can reflect the magnetic resonance frequency of the nuclide. The down-conversion processing module 420 includes multiple frequency conversion parameters. In one embodiment, the down-conversion processing module 420 includes... 1 H, 2 H, 3 He 9 Li, 13 C 17 O、 19 F, 23 Na、 31 P and129 Multiple frequency conversion parameters are corresponding to more than 10 nuclides, including Xe. The local oscillation frequency is determined based on the nuclide's magnetic resonance frequency and the target down-conversion frequency, thus determining the frequency of the frequency-converted signal output by the down-conversion processing module 420. The down-conversion processing module 420 mixes the local oscillation frequency with the input digital signal to achieve frequency conversion and obtain the frequency-converted signal.

[0074] Each downconversion processing module 420 can perform different downconversion functions depending on the conversion parameters, and can perform downconversion processing on frequencies corresponding to different nuclides. Regardless of the corresponding nuclide, the downconversion processing module 420 can achieve the downconversion processing function. Therefore, the digital filter module 410, analog-to-digital converter module 320, broadband RF preamplifier module 310, and RF coil module 20 connected to the downconversion processing module 420 do not need to be matched with a fixed nuclide, and can be arbitrarily connected to select different types of nuclides without affecting the downconversion processing module 420's downconversion function for digital signals.

[0075] In one embodiment, each filter frequency conversion processing module 40 further includes an extraction module 430 and a communication parsing module 440. The extraction module 430 is used to extract data from the frequency conversion signal to obtain the signal to be imaged.

[0076] The communication parsing module 440 is used to send the RF coil identifier to the digital filtering module 410 and the down-conversion processing module 420. The digital filtering module 410 determines the filtering coefficients corresponding to each nuclide based on the RF coil identifier. The down-conversion processing module 420 determines the conversion parameters corresponding to each nuclide based on the RF coil identifier. The communication parsing module 440 is also connected to the extraction module 430 to acquire the imaging signal corresponding to each nuclide.

[0077] In this embodiment, the extraction module 430 is connected to the down-conversion processing module 420 and is used to extract data from the frequency conversion signal to obtain the signal to be imaged. The extraction module 430 can select sample points from the frequency conversion signal to form a new discrete signal sequence with fewer data points, further reducing the data volume and processing complexity, lowering data requirements and storage needs, and improving anti-interference capabilities. Therefore, by processing the digital signal through the digital filtering module 410, the down-conversion processing module 420, and the extraction module 430, the compatibility of the multi-nuclear magnetic resonance scanning device 100 of this application is increased, allowing for the arbitrary excitation and reception of signals corresponding to different types of nuclides, thus improving the efficiency and accuracy of nuclear magnetic resonance imaging.

[0078] The communication parsing module 440 enables the transmission and exchange of various data between the filtering and frequency conversion processing module 40 and the acquisition and control module 70, as well as the control and analysis of related equipment and operations. The communication parsing module 440 can send the acquired imaging signal to the acquisition and control module 70. The communication parsing module 440 can also send the RF coil identifier obtained from the acquisition and control module 70 to the digital filtering module 410 and the down-conversion processing module 420, respectively.

[0079] Therefore, the digital filtering module 410 selects the filter coefficient corresponding to the nuclide corresponding to the RF coil identifier. Regardless of which nuclide the RF coil identifier corresponds to, the digital filtering module 410 can select the corresponding filter coefficient to achieve the digital filtering function. The downconversion processing module 420 selects the conversion parameters corresponding to the nuclide corresponding to the RF coil identifier. Regardless of which nuclide the RF coil identifier corresponds to, the downconversion processing module 420 can select the corresponding conversion parameters to achieve the downconversion processing function.

[0080] In one embodiment, the control unit 60 is connected to the acquisition control module 70, which acquires the sequence timing and RF coil identifier, controls the synchronous reception of the receiving signal processing module 30 according to the sequence timing, and sends the RF coil identifier to the communication parsing module 440. Each acquisition control module 70 is also connected to the communication parsing module 440 for acquiring the signal to be imaged.

[0081] In this embodiment, each acquisition control module 70 is connected to the control unit 60 and the communication parsing module 440, and is used to acquire the radio frequency coil identifier and send the radio frequency coil identifier to the communication parsing module 440. Each acquisition control module 70 is connected to the communication parsing module 440, and is used to acquire the imaging signal output by the communication parsing module 440, and send the imaging signal to the data storage module 80 for storage.

[0082] Each acquisition control module 70 is also connected to the broadband RF preamplifier module 310 in the receiving signal processing module 30, and is used to send RF switching signals, tuning signals or detuning signals to the broadband RF preamplifier module 310 to control the working state of the broadband RF preamplifier module 310, so as to control the receiving time of the receiving signal processing module 30.

[0083] In one embodiment, the control unit 60 is also configured to adjust the sequence timing of the multi-nucleus radio frequency transmitting unit, the multi-nucleus radio frequency receiving unit, and the gradient magnetic field unit, as well as the configuration of multiple different nuclides, according to different imaging requirements.

[0084] In this embodiment, the multi-nucleus radio frequency receiving unit, with at least two broadband radio frequency preamplifier modules 310 and at least two analog-to-digital conversion modules 320, does not have a fixed configuration for any particular nuclide, allowing for the reception, acquisition, and processing of echo signals from different types of nuclides. Similarly, the multi-nucleus radio frequency receiving unit, with at least two digital filtering modules 410 and at least two down-conversion processing modules 420, also does not have a fixed configuration for any particular nuclide, allowing for the reception, acquisition, and processing of echo signals from different types of nuclides. 1 H, 2 H, 3 He 9 Li, 13 C 17 O、 19 F, 23 Na、 31 P and 129 The filter coefficients and frequency conversion parameters corresponding to more than 10 nuclides such as Xe are selected from those that match the imaging requirements to achieve digital filtering and down-conversion processing functions.

[0085] Therefore, by adjusting the sequence timing and configuration of multiple different nuclides of the multi-nucleus radio frequency transmitting unit, multi-nucleus radio frequency receiving unit, and gradient magnetic field unit according to different imaging requirements, the control unit 60 sends the corresponding sequence timing and configuration of multiple different nuclides to each unit. This enables each radio frequency channel to be independent of each other and nuclides to be arbitrarily matched. Under the sequence timing requirements required for imaging, it can achieve parallel excitation and synchronous reception of at least two different nuclides, which is more flexible and faster than traditional devices.

[0086] In one embodiment, the control unit 60 is connected to the radio frequency transmitting module 10 and is used to send radio frequency coil identifiers to the radio frequency transmitting module 10 and control the parallel excitation of the radio frequency transmitting module 10 according to the sequence timing.

[0087] In this embodiment, based on the sequence timing, information on multiple nuclides required for imaging can be obtained. Combined with multiple radio frequency coil identifiers, each radio frequency coil module 20 is assigned a corresponding nuclide, thus each radio frequency coil module 20 corresponds to one nuclide and one radio frequency coil identifier. The radio frequency coil identifier can be understood as the identification identifier of the radio frequency coil, or as its ID. Each radio frequency coil identifier corresponds to one radio frequency coil module 20, characterizing the identity of the radio frequency coil module 20.

[0088] Each radio frequency (RF) transmitting module 10 generates an RF signal with a specific frequency and energy corresponding to each nuclide based on the matching relationship between each nuclide and the RF coil identifier in the sequence timing. Each nuclide corresponds to an RF signal with a specific frequency and energy. Thus, a correspondence is formed between each RF transmitting module 10, each RF coil identifier, each nuclide, and each RF signal. Therefore, the parallel excitation of the RF transmitting modules 10 can be controlled by the control unit 60. At the receiving end, the control unit 60 can control the synchronous reception of the receiving signal processing module 30, and further enable the digital filtering module 410 and the down-conversion processing module 420 to select the corresponding filter coefficients and conversion parameters for the corresponding nuclide based on the RF coil identifier.

[0089] In one embodiment, the multi-nucleus radio frequency (RF) transmitting unit includes at least two discrete RF transmitting modules 10. Each RF transmitting module 10 is connected to the control unit 60 and the RF coil module 20, and is used to transmit the corresponding nuclide's RF signal to the RF coil module 20 according to the sequence timing.

[0090] In this embodiment, multiple radio frequency (RF) coil modules 20 are connected to multiple RF transmitting modules 10 to generate multiple excitation magnetic fields based on multiple RF signals, thereby exciting the tissue under test. Each RF coil module 20 is connected to one RF transmitting module 10, corresponding to one RF signal, one radionuclide, and one RF coil identifier. When clinical needs (which can also be understood as imaging needs) differ, the sequence timing also differs, as do the required types and numbers of radionuclides. The radionuclides, RF signals, and RF coil identifiers are matched.

[0091] The multi-nuclear magnetic resonance scanning device 100 provided in this application comprises a radio frequency (RF) transmission module 10, an RF coil module 20, a receiving signal processing module 30, and a filtering and frequency conversion processing module 40 forming an RF channel to excite and receive the magnetic resonance signal of a single nuclide. At least two discrete RF transmission modules 10, at least two discrete RF coil modules 20, at least two discrete receiving signal processing modules 30, at least two discrete filtering and frequency conversion processing modules 40, and at least two discrete acquisition and control modules 70 can form at least two discrete RF channels to excite and receive echo signals corresponding to at least two different nuclides. Therefore, the multi-nuclear magnetic resonance scanning device 100 provided in this application can provide richer echo signals from multiple nuclides, resulting in high accuracy and fast imaging speed in magnetic resonance imaging, improving the efficiency and precision of nuclear magnetic resonance imaging, and meeting the needs of multi-dimensional and multi-parameter analysis of complex samples.

[0092] In one embodiment, multiple radio frequency (RF) transmitting modules 10, multiple RF coil modules 20, multiple receiving signal processing modules 30, and multiple filtering and frequency conversion processing modules 40 form multiple RF channels. Each RF channel is adapted to any one of different nuclides, such as hydrogen, helium, lithium, carbon, oxygen, fluorine, sodium, phosphorus, and xenon.

[0093] Multiple radio frequency (RF) transmitting modules 10, based on the required imaging sequence timing and multiple RF coil identifiers, construct a connection bridge between multiple RF signals, multiple nuclides, multiple RF coil modules 20, and multiple filtering and frequency conversion processing modules 40. Different RF coil identifiers can randomly correspond to different nuclides, thereby matching different RF signals with RF coil modules 20 to achieve parallel excitation and synchronous reception of signals. Furthermore, in the filtering and frequency conversion processing module 40, different filtering coefficients and frequency conversion parameters corresponding to different nuclides are set through different RF coil identifiers. The digital signals received by the RF coil modules 20 and processed by the received signal processing module 30 are filtered and frequency converted to obtain the signal to be imaged, thereby reconstructing the magnetic resonance image.

[0094] Therefore, the multi-nucleus magnetic resonance scanning device 100 provided in this application does not require multiple radio frequency transmission modules 10, multiple radio frequency coil modules 20, multiple receiving signal processing modules 30, and multiple filtering and frequency conversion processing modules 40 to be fixed to a certain nuclide, and can be matched with different nuclides according to the actual application scenario requirements.

[0095] In one embodiment, this application provides a multinuclear magnetic resonance scanning device 100 that can be configured 1 H, 2 H, 3 He 9 Li, 13 C 17 O、 19 F, 23 Na、 31 P and 129 More than 10 nuclides, including Xe.

[0096] In one embodiment, a radio frequency (RF) transmitting module 10, a radio frequency (RF) coil module 20, a receiving signal processing module 30, and a filtering and frequency conversion processing module 40 form an RF channel, which can be used to excite and receive signals from H nuclides. Four RF transmitting modules 10, four RF coil modules 20, four receiving signal processing modules 30, and four filtering and frequency conversion processing modules 40 form four separate RF channels, each capable of transmitting signals from four X nuclides (e.g., H nuclides). 3 He 9 Li, 13 C 17 O、19 F, 23 Na、 31 P and 129 Parallel excitation and synchronous reception of signals are performed using any 4 of Xe.

[0097] In one embodiment, multiple radio frequency channels can independently acquire multiple nuclides, acquire them simultaneously in parallel, acquire them in a time-division parallel manner, acquire them in a decoupled manner, or acquire them using the Nuclear Overhauser Effect (NOE). Therefore, the multi-nucleus magnetic resonance scanning device 100 provided in this application offers greater flexibility in acquiring and detecting multiple nuclides.

[0098] Please see Figure 3 In one embodiment, each radio frequency (RF) transmitting module 10 includes an RF signal generating module 110. The RF signal generating module 110 is connected to the control unit 60 and is used to generate a digital pulse signal for each nuclide based on the sequence timing and RF coil identification.

[0099] In this embodiment, each radio frequency signal generation module 110 is connected to the control unit 60 and is used to generate a digital pulse signal corresponding to each nuclide based on the sequence timing and radio frequency coil identification. The radio frequency signal generation module 110 includes a radio frequency transmitter capable of generating signals for multiple different types of nuclides (e.g., ...). 1 H, 2 H, 3 He 9 Li, 13 C 17 O、 19 F, 23 Na、 31 P and 129 Digital pulse signals of different frequencies for more than 10 nuclides (such as Xe). Furthermore, through at least two radio frequency signal generation modules 110, digital pulse signals corresponding to different types of nuclides can be generated at will without matching a specific fixed nuclide, thereby enabling the configuration of multiple different nuclides according to imaging requirements.

[0100] In one embodiment, multiple radio frequency signal generation modules 110 may use independent transmission power supplies.

[0101] In one embodiment, each radio frequency transmitting module 10 further includes a transmitting signal processing module 120. The transmitting signal processing module 120 is connected to the radio frequency signal generation module 110 and is used to perform digital-to-analog conversion, filtering, and amplification processing on the digital pulse signal to obtain the radio frequency signal corresponding to each nuclide.

[0102] In this embodiment, a transmit signal processing module 120 is connected to a radio frequency signal generation module 110. Each transmit signal processing module 120 is used to perform digital-to-analog conversion, filtering, and amplification on the digital pulse signal to obtain the radio frequency signal corresponding to each nuclide. After performing digital-to-analog conversion, filtering, and amplification on the digital pulse signal by each transmit signal processing module 120, the radio frequency signal corresponding to each nuclide is obtained, and the radio frequency signal is sent to the corresponding radio frequency coil module 20.

[0103] Furthermore, through at least two radio frequency signal generation modules 110 and at least two transmission signal processing modules 120 in the radio frequency transmission module 10, digital pulse signals corresponding to different types of nuclides can be generated arbitrarily without matching a specific fixed nuclide. These digital pulse signals are then subjected to digital-to-analog conversion, filtering, and amplification to form radio frequency signals corresponding to at least two nuclides, enabling matching. 1 H, 2 H, 3 He 9 Li, 13 C 17 O、 19 F, 23 Na、 31 P and 129 At least two of any 10 or more nuclides, such as Xe. Thus, the radio frequency transmission module 10 can achieve parallel transmission of radio frequency signals of at least two different nuclides to match the synchronous reception of the radio frequency receiving unit.

[0104] In one embodiment, each transmit signal processing module 120 includes a digital-to-analog converter module 121, an analog filtering module 122, and an RF power amplifier module 123. The digital-to-analog converter module 121 is connected to the RF signal generation module 110 and is used to perform digital-to-analog conversion on the digital pulse signal to obtain an analog pulse signal. The analog filtering module 122 is connected to the digital-to-analog converter module 121 and is used to filter the analog pulse signal to obtain an analog filtered signal. The RF power amplifier module 123 is connected to the analog filtering module 122 and is used to amplify the analog filtered signal to obtain the RF signal for each nuclide.

[0105] In this embodiment, the digital pulse signal generated by the radio frequency signal generation module 110 is converted from digital to analog by the digital-to-analog conversion module 121 to form an analog pulse signal, which is beneficial to excite the radio frequency coil module 20 to generate an excitation magnetic field to excite the nuclear magnetic resonance signal of the corresponding nuclide in the tissue under test.

[0106] The radio frequency signal generation module 110 is connected to the analog filtering module 122, and the operating state of the analog filtering module 122 is controlled by the radio frequency switch signal. The analog filtering module 122 filters the analog pulse signal to achieve frequency selection and signal purification for different types of nuclides, and suppresses harmonics and spurious signals to ensure the spectral purity of the radio frequency signal.

[0107] The analog filtered signal is amplified by the radio frequency power amplifier module 123, so that the radio frequency signal can drive the radio frequency coil module 20, thereby generating a strong radio frequency magnetic field around the tissue being measured, which excites the generation of magnetic resonance signal, thus improving imaging quality and efficiency.

[0108] In one embodiment, the RF power amplifier module 123 can be an RF power amplifier, the digital-to-analog converter module 121 can be a digital-to-analog converter, and the analog filter module 122 can be a filter.

[0109] Please see Figure 4 In one embodiment, the gradient magnetic field unit includes a gradient module 90 connected to the control unit 60 and the gradient coil assembly inside the main magnet. This module controls the gradient coil assembly to generate gradient magnetic fields in three spatial directions (X-axis, Y-axis, and Z-axis) according to a sequential timing sequence. These gradients correspond to the selected imaging plane, phase-encoded gradient, and frequency-encoded gradient, respectively, achieving spatial encoding. Furthermore, the gradient module 90 allows for the selection of specific imaging planes (e.g., transverse, coronal, and sagittal planes) in three-dimensional space.

[0110] Gradient magnetic field units apply the same gradient to all different nuclides synchronously during the spatial coding stage, enabling gradient magnetic field-assisted localization. The influence ratio of the gradient magnetic field applied by these units on the frequencies of different nuclides is fixed, making gradient field-based spatial coding universal and eliminating the need for a separate coding scheme for each nuclide, thus simplifying system design and signal processing.

[0111] In one embodiment, a Z-axis gradient field is generated by controlling a gradient coil assembly so that the frequencies of all different nuclides vary linearly in space, for example, the slopes of the frequency changes of 1H and 31P are consistent.

[0112] In one embodiment, the gradient module 90 includes devices such as a gradient amplifier, a gradient controller, a cooling system, a gradient power supply, and a feedback circuit.

[0113] In one embodiment, the multinuclear magnetic resonance scanning apparatus 100 further includes an imaging reconstruction module 50. The imaging reconstruction module 50 is used to acquire multiple radio frequency coil identifiers when multiple radio frequency coil modules 20 are respectively connected to multiple radio frequency transmitting modules 10 and multiple receiving signal processing modules 30. The imaging reconstruction module 50 is also used to acquire imaging requirement information.

[0114] The control unit 60 is connected to the imaging reconstruction module 50 and is used to acquire multiple radio frequency coil identifiers and imaging requirement information. It generates a timing sequence based on the imaging requirement information and sends the timing sequence along with the multiple radio frequency coil identifiers to each radio frequency transmission module 10.

[0115] When multiple radio frequency coil modules 20 are connected to multiple radio frequency transmitting modules 10 and multiple receiving signal processing modules 30 respectively, multiple radio frequency coil identifiers corresponding to the multiple radio frequency coil modules 20 are sent to the imaging reconstruction module 50. During each multi-nuclear magnetic resonance imaging (MMRI) session using the multi-nuclear magnetic resonance scanning device 100, a corresponding relationship is established between each radio frequency coil module 20, each radio frequency transmitting module 10, each radio frequency coil identifier, each nuclide, and each radio frequency signal, according to the imaging requirements.

[0116] The imaging reconstruction module 50 transmits multiple radio frequency coil identifiers to the control unit 60, and then via the control unit 60 to multiple radio frequency transmission modules 10 and multiple acquisition control modules 70. The imaging reconstruction module 50 is connected to the multiple acquisition control modules 70 through the data storage module 80 to acquire multiple signals to be imaged. The imaging reconstruction module 50 performs image reconstruction on the multiple signals to be imaged using an imaging reconstruction algorithm to obtain magnetic resonance imaging. In one embodiment, the imaging reconstruction module 50 can be a device such as a computer.

[0117] In one embodiment, the data storage module 80 can store multiple signals to be imaged output by multiple acquisition control modules 70, and send the multiple signals to be imaged to the imaging reconstruction module 50 for imaging.

[0118] In one embodiment, the broadband RF preamplifier module 310, analog-to-digital converter module 320, digital filter module 410, down-conversion processing module 420, decimation module 430, communication parsing module 440, and acquisition control module 70 can be integrated into a parallel processing unit, or they can be implemented as independent modules in the above embodiments.

[0119] In one embodiment, timing adjustment includes adjusting the timing based on a preset transmit / receive mode. The transmit / receive mode includes at least one or more of the following: independent mode, synchronous mode, NOE mode, and decoupling mode.

[0120] In this embodiment, in independent mode, independent transmission and reception time windows are assigned to different nuclides. Furthermore, based on the preset independent mode timing adjustment, each radio frequency transmission module 10 in the multi-nuctopic radio frequency transmission unit is controlled to transmit radio frequency signals within its corresponding independent transmission time window for each different nuctopic. Based on the preset independent mode timing adjustment, each receiving signal processing module 30 in the multi-nuctopic radio frequency reception unit is controlled to receive echo signals within its corresponding independent reception time window for each different nuctopic, thereby extracting the effective echo signals within each reception time window. By adjusting the timing in independent mode, mutual interference between different nuclides with similar frequency bands can be avoided, improving scanning accuracy and contributing to improved imaging quality and efficiency.

[0121] In synchronization mode, different nuclides are assigned the same transmission and reception time windows. Furthermore, based on the preset synchronization mode, the timing is adjusted to control each radio frequency transmission module 10 in the multi-nuclide radio frequency transmission unit to simultaneously transmit the radio frequency signals corresponding to all nuclides within the same transmission time window. Similarly, based on the preset synchronization mode, the timing is adjusted to control each receiving signal processing module 30 in the multi-nuclide radio frequency reception unit to simultaneously receive all echo signals within the same receiving time window. Adjusting the timing through synchronization mode allows for the capture of transient coupling effects, which is beneficial for obtaining more comprehensive imaging signals.

[0122] In the Nuclear Overhauser Effect (NOE) mode, molecular structure information is acquired using the NOE effect, and the NMR signal is enhanced through spatial proximity. Based on a preset NOE mode, the timing is adjusted so that the RF transmission module 10 in the multi-nucleus RF transmission unit first transmits the RF signal of the transit nuclide, and then transmits the RF signal of the target nuclide after a predetermined delay. Adjusting the timing through the NOE mode enhances the echo signal of low-sensitivity nuclides, thus improving imaging quality.

[0123] In decoupling mode, interfering radio frequency pulses are applied to eliminate or weaken coupling between nuclear spins (such as J-coupling, dipole coupling, etc.). Based on a preset decoupling mode timing adjustment, the radio frequency transmission module 10 in the multi-nucleus radio frequency transmission unit continuously transmits decoupling radio frequency pulses to the interfering nuclide, thereby controlling each receiving signal processing module 30 in the multi-nucleus radio frequency receiving unit to receive the echo signal of the target nuclide under the interference of the decoupling radio frequency pulses. Adjusting the timing through decoupling mode can eliminate or weaken spectral line splitting caused by J-coupling, which is beneficial for improving imaging quality.

[0124] When adjusting the timing using one or more preset modes such as independent mode, synchronous mode, NOE mode, and decoupling mode, the control unit 60 can adjust the sequence timing of the multi-nucleus radio frequency transmitting unit, the gradient magnetic field unit, and the multi-nucleus radio frequency receiving unit. Furthermore, when the control unit 60 adjusts the sequence timing of the multi-nucleus radio frequency transmitting unit, the multi-nucleus radio frequency receiving unit, and the gradient magnetic field unit, the architecture of the receiving signal processing module 30, the filtering and frequency conversion processing module 40, and the acquisition control module 70 at the receiving end will not change with the sequence timing under different acquisition modes. With the hardware-fixed support of the multi-nucleus magnetic resonance scanning device 100 provided in this application, multi-nucleus magnetic resonance scanning imaging under different acquisition modes can be realized.

[0125] In one embodiment, radio frequency signals of at least two different nuclides are excited simultaneously. Alternatively, radio frequency signals of at least two different nuclides are excited in a time-division manner.

[0126] In this embodiment, at least two different radionuclide radio frequency signals are excited within the same emission time window, which can save scanning time, greatly improve detection efficiency and time utilization, and enhance the time synchronization and physiological correlation of the signals.

[0127] By sequentially exciting radio frequency signals of at least two different nuclides within different emission time windows, radio frequency interference between nuclides can be avoided, signal purity can be improved, the risk of energy deposition can be reduced, and safety can be enhanced.

[0128] In one embodiment, echo signals from different nuclides simultaneously enter a parallel processing unit and undergo synchronous digital processing.

[0129] In this embodiment, echo signals from all different nuclides simultaneously enter the parallel processing unit, enabling digital processing of multiple data streams. The echo signals from different nuclides are received by a broadband RF preamplifier receiver in the parallel processing unit and uniformly sampled by an analog-to-digital converter (ADC). Due to differences in Larmor frequencies (e.g., 1H = 64MHz, 31P = 25MHz), the corresponding signals of different nuclides can be naturally separated in the frequency domain. Furthermore, the digital filtering and down-conversion processing functions in the parallel processing unit select the corresponding filter coefficients and conversion parameters for each nuclide in real time for filtering and frequency conversion, separating the echo signals in real time and achieving frequency division multiplexing to isolate signals in the target frequency band.

[0130] This application provides a medical device, including a multi-nuclear magnetic resonance scanning device 100 in any of the above embodiments. The medical device can be a magnetic resonance imaging system, a magnetic resonance angiography system, a magnetic resonance spectroscopy imaging system, a magnetic resonance functional imaging system, a magnetic resonance-guided radiotherapy system, or a magnetic resonance interventional device, etc.

[0131] Those skilled in the art will clearly understand that, for the sake of convenience and brevity, the above-described division of functional units and modules is merely an example. In practical applications, the above functions can be assigned to different functional units and modules as needed, that is, the internal structure of the device can be divided into different functional units or modules to complete all or part of the functions described above. The functional units and modules in the embodiments can be integrated into one processing unit, or each unit can exist physically separately, or two or more units can be integrated into one unit. The integrated unit can be implemented in hardware or as a software functional unit. Furthermore, the specific names of the functional units and modules are only for easy differentiation and are not intended to limit the scope of protection of this application.

[0132] In the above embodiments, the descriptions of each embodiment have different focuses. For parts that are not described in detail or recorded in a certain embodiment, please refer to the relevant descriptions of other embodiments.

[0133] Those skilled in the art will recognize that the units and algorithm steps of the various examples described in conjunction with the embodiments disclosed herein can be implemented in electronic hardware, or a combination of computer software and electronic hardware. Whether these functions are implemented in hardware or software depends on the specific application and design constraints of the technical solution. Those skilled in the art can use different methods to implement the described functions for each specific application, but such implementation should not be considered beyond the scope of this application.

[0134] The division of modules or units is merely a logical functional division. In actual implementation, there may be other division methods. For example, multiple units or components may be combined or integrated into another system, or some features may be ignored or not executed. Furthermore, the coupling or direct coupling or communication connection shown or discussed may be indirect coupling or communication connection through some interfaces, devices, or units, and may be electrical, mechanical, or other forms.

[0135] The units described as separate components may or may not be physically separate. The components shown as units may or may not be physical units; that is, they may be located in one place or distributed across multiple network units. Some or all of the units can be selected to achieve the purpose of this embodiment according to actual needs.

[0136] Furthermore, the functional units in the various embodiments of this application can be integrated into one processing unit, or each unit can exist physically separately, or two or more units can be integrated into one unit. The integrated unit can be implemented in hardware or as a software functional unit.

[0137] If the integrated module / unit is implemented as a software functional unit and sold or used as an independent product, it can be stored in a computer-readable storage medium. The computer program includes computer program code, which can be in the form of source code, object code, executable files, or certain intermediate forms. The computer-readable medium can include: any entity or device capable of carrying the computer program code, recording media, USB flash drives, portable hard drives, magnetic disks, optical disks, computer memory, read-only memory (ROM), random access memory (RAM), electrical carrier signals, telecommunication signals, and software distribution media, etc. It should be noted that the content included in the computer-readable medium can be appropriately added or removed according to the requirements of legislation and patent practice in the jurisdiction. For example, in some jurisdictions, according to legislation and patent practice, computer-readable media do not include electrical carrier signals and telecommunication signals.

[0138] The above-described embodiments are only used to illustrate the technical solutions of this application, and are not intended to limit them. Although this application has been described in detail with reference to the foregoing embodiments, those skilled in the art should understand that modifications can still be made to the technical solutions described in the foregoing embodiments, or equivalent substitutions can be made to some of the technical features. Such modifications or substitutions 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 this application, and should all be included within the protection scope of this application.

Claims

1. A multi-nuclear magnetic resonance scanning apparatus, characterized by comprising: include: A multi-nucleoside radio frequency transmitting unit is used to generate radio frequency signals of at least two different nuclides; Gradient magnetic field unit, used to provide the gradient magnetic field required for spatial encoding; A multi-nucleus radio frequency receiving unit is used to receive the echo signals of the different nuclides; The control unit (60) is configured to adjust the sequence timing of the multi-nucleus radio frequency transmitting unit, the multi-nucleus radio frequency receiving unit and the gradient magnetic field unit to achieve parallel excitation and synchronous reception of at least two different nuclides.

2. The multi-nuclear magnetic resonance scanning apparatus of claim 1, wherein, The multi-nucleoside radio frequency receiving unit includes a parallel processing unit for digitizing the received echo signal.

3. The multi-nuclear magnetic resonance scanning apparatus of claim 2, wherein, The parallel processing unit includes multiple independent processing cores, each of which performs the digitization processing of the echo signal of a specific nuclide.

4. The multinuclear magnetic resonance scanning device as described in claim 2, characterized in that, The parallel processing unit includes: At least two separate radio frequency receiving channels, each of which receives the echo signal of a nuclide and performs digital processing accordingly; The radio frequency receiving channel includes at least a receiving signal processing module (30), a filtering and frequency conversion processing module (40), and an acquisition control module (70).

5. The multi-nuclear magnetic resonance scanning apparatus of claim 4, wherein, The filtering and frequency conversion processing module (40) is connected to the receiving signal processing module (30) and is used to perform filtering and frequency conversion processing on the digital signal according to the filtering coefficient and frequency conversion parameters corresponding to each nuclide to obtain the signal to be imaged.

6. The multi-nuclear magnetic resonance scanning apparatus of claim 5, wherein, The filtering and frequency conversion processing module (40) includes: The extraction module (430) is used to extract data from the frequency conversion signal to obtain the signal to be imaged; The communication parsing module (440) is used to send the radio frequency coil identifier to the digital filtering module (410) and the downconversion processing module (420) to determine the filtering coefficient and the frequency conversion parameter corresponding to each nuclide; The communication parsing module (440) is connected to the extraction module (430) and is used to acquire the imaging signal corresponding to each nuclide.

7. The multi-nuclear magnetic resonance scanning apparatus of claim 1, wherein, The multi-nucleoside radio frequency transmitting unit includes: At least two separate radio frequency transmitting modules (10), each of which is connected to the control unit (60) and the radio frequency coil module (20), for transmitting radio frequency signals of the corresponding nuclide to the radio frequency coil module (20) according to the sequence timing.

8. The multi-nuclear magnetic resonance scanning apparatus of claim 7, wherein, Each of the radio frequency transmitting modules (10) includes: Radio frequency signal generation module (110), which is connected to the control unit (60), is used to generate a digital pulse signal for each nuclide according to the sequence timing and radio frequency coil identification; The transmission signal processing module (120) is connected to the radio frequency signal generation module (110) and is used to process the digital pulse signal to obtain the radio frequency signal corresponding to each nuclide.

9. A multi-nuclear magnetic resonance scanning apparatus as claimed in any one of claims 1-8, characterized in that, The control unit (60) is connected to the acquisition control module (70), which is used to acquire the sequence timing and radio frequency coil identifier, and control the synchronous reception of the receiving signal processing module (30) according to the sequence timing.

10. The multinuclear magnetic resonance scanning device according to any one of claims 1-8, characterized in that, The control unit (60) is connected to the radio frequency transmitting module (10) and is used to send the radio frequency coil identifier to the radio frequency transmitting module (10) and control the parallel excitation of the radio frequency transmitting module (10) according to the sequence timing.

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