A multimodal signal detection device for brain hyperpolarized xenon magnetic resonance imaging

Abstract

The invention discloses a multimodal signal detection device for brain hyperpolarized xenon magnetic resonance imaging, comprising a transmitter coil, a receiving coil, and a control box. A fixed airbag is arranged on the transmitter coil, and the transmitter coil can be quickly installed and removed in a gradient coil by inflating and deflating the fixed airbag, and can be stably placed by an airbag fixing tray and a coil fixing tray, thereby saving time and labor. The receiving coil can be installed on the transmitter coil by a receiving coil positioning slide groove and a slider, and the position of the receiving coil can be changed by sliding. The acquisition of physiological signals and the transmission and reception switching functions are integrated in a single-chip FPGA chip in the control box, so that the transmitter coil transmits radio frequency signals and the receiving coil receives magnetic resonance signals in a time-sharing switching manner, thereby preventing mutual interference, and can also detect the physiological state of animals in real time, provide multi-dimensional information, and improve integration and scalability.

Description

Technical Field

[0001] The present invention belongs to the technical field of magnetic resonance imaging, and in particular relates to a multimodal signal detection device for brain hyperpolarized xenon magnetic resonance imaging, which is suitable for a magnetic resonance host without multi-core radio frequency signal transmission and reception switching functions. Background Art

[0002] Magnetic resonance imaging (MRI) is an important method for studying brain science and brain diseases. The signal of traditional MRI comes from the hydrogen nuclei (protons) in the human body. In addition to protons, there are many other nuclei that can be used for magnetic resonance imaging, called multi-nuclear MRI. 129 Xe can increase its nuclear magnetic signal by tens of thousands times (called hyperpolarization) through spin exchange optical pumping technology. 129 Xe). 129 After Xe gas is inhaled into the lungs, it first enters the alveoli, then passes through the alveolar wall into the capillaries and dissolves in the blood (called dissolved state). 129 Xe) is transported throughout the body through the bloodstream. 129 Xe images have no background signal interference, so they naturally have the advantage of evaluating brain perfusion information. This is of great value in studying cerebral hemodynamics and evaluating brain functional status.

[0003] The RF coil is an important component in the MRI instrument. It is responsible for emitting excitation pulses to the imaging nuclei and receiving MRI signals. In clinical MRI, in order to uniformly excite the nuclei in the target imaging area and receive MRI signals with high sensitivity, a coil structure with separate transmission and reception is usually used. Specifically, the conventional configuration is to use B 1 The volume coil with uniform field is used as the transmitting coil to stimulate the magnetic resonance signal in the entire imaging area. 1The surface coil with the highest field strength is used as the receiving coil, because the surface coil is closer to the tissue of interest and can provide a higher signal-to-noise ratio. In some preclinical MRI instruments, the RF transmission and reception of multi-cores share one channel, which means that the RF transmission and reception cannot occupy the fixed channel of the MRI instrument alone, so the separation of the transmission and reception of multi-core signals faces challenges. Some clinical MRI instruments have opened multi-core ports and have separate multi-core transmission and reception channels, so independent transmission and reception of hyperpolarized MRI experiments can be achieved. For example, AA et al. made a dual-tuned coil with separate transmission and reception adapted to the field strength of 2.35 T on this basis, and finally obtained a dual-core image of the rat brain. In recent years, the coil structure with separate transmission and reception has gradually been applied to the human body, such as MR, Rao et al. used the 8-channel separate transmission and reception coil of the human brain to obtain gray matter images of the brain. However, since multi-core MRI is not popular at present, most instruments only have a single multi-core RF port for the transmission and reception of multi-core signals. For such instruments, only one integrated transceiver magnetic resonance coil is usually available. For example, Scott D. S et al. used an integrated transceiver dual-core surface coil to image the rat brain; Friedlander, Y, Z et al. used an integrated transceiver body coil to achieve dissolved state imaging of the rat brain. 129 Xe image acquisition.

[0004] In summary, for magnetic resonance imaging devices that share a radio frequency channel for transmission and reception, there are still many challenges in improving the image signal-to-noise ratio by separating the transmission and reception of signals.

[0005] In addition, for preclinical brain hyperpolarized gas MRI studies, factors such as the animal's body temperature, blood oxygen concentration, and heart rate will greatly affect the relaxation of the gas magnetic resonance signal in the brain and the process of establishing a steady-state signal, thereby affecting the experimental results related to brain perfusion. Therefore, real-time monitoring of the animal's body temperature, heart rate, blood oxygen, and the ambient temperature of the animal in the experiment, and adjusting the required experimental conditions such as anesthesia depth and ambient temperature are crucial to obtaining effective brain hyperpolarized gas MRI results. At present, the monitoring of animal signs in preclinical experiments is generally completed by an independent physiological monitoring system. However, the aperture of the separate transceiver coil used in brain hyperpolarized gas MRI is small, and the independent physiological monitoring module is difficult to use in a narrow aperture. Summary of the invention

[0006] The object of the present invention is to provide a multimodal signal detection device for brain hyperpolarized xenon magnetic resonance imaging in view of the above-mentioned problems existing in the prior art.

[0007] The above-mentioned purpose of the present invention is achieved by the following technical means:

[0008] A multimodal signal detection device for brain hyperpolarized xenon magnetic resonance imaging comprises a transmitting body coil, a receiving coil, and a control box. The control box is provided with a detuning circuit BNC interface and a physiological signal transmission aviation socket. The detuning circuit BNC interface comprises a first detuning circuit BNC interface and a second detuning circuit BNC interface. The transmitting body coil comprises a birdcage coil, a transmitting detuning circuit module, and a physiological signal transmission module. The birdcage coil is connected to the transmitting detuning circuit module. A radio frequency input port and a transmitting detuning control port are provided on the transmitting detuning circuit module. The transmitting detuning control port is connected to the first detuning circuit BNC interface through a first detuning control BNC line. The receiving coil comprises a proton transceiver integrated surface coil, a Xe nuclear receiving surface coil, and a receiving detuning circuit module. The Xe nuclear receiving surface coil is connected to the receiving detuning circuit module. A radio frequency output port and a receiving detuning control port are provided on the receiving detuning circuit module. The receiving detuning control port is connected to the second detuning circuit BNC interface through a second detuning control BNC line. The physiological signal transmission module is connected to the physiological signal transmission aviation socket through a physiological signal transmission multi-channel aviation plug.

[0009] As described above, the control box is provided with an FPGA chip and an FPGA power supply board, the FPGA chip is connected to the output interface of the FPGA power supply board, the FPGA chip is provided with a detuning circuit control module and a physiological signal receiving module, the detuning circuit control module is respectively connected to the transmitting detuning control port and the receiving detuning control port through the first detuning circuit BNC interface and the second detuning circuit BNC interface, the physiological signal receiving module is connected to the physiological signal transmission module through the physiological signal transmission multi-channel aviation plug, and the FPGA chip is also provided with a blink signal input port and a USB interface.

[0010] As described above, the transmitter coil also includes a semi-cylindrical animal bed bracket and a birdcage coil fixing cylinder. The birdcage coil fixing cylinder is sleeved on the animal bed bracket, and the birdcage coil is sleeved and fixed on the birdcage coil fixing cylinder. A receiving coil positioning groove is provided on the inner wall of the birdcage coil fixing cylinder, and the receiving coil positioning groove is along the axial direction of the birdcage coil fixing cylinder.

[0011] As described above, the transmitter coil also includes a plurality of semicircular coil fixing trays, an airbag fixing tray, a fixed airbag, an airbag control line, and a hot air delivery pipe. The coil fixing trays are all sleeved and fixed on the animal bed bracket. All coil fixing trays are provided with wire support holes. The airbag fixing tray is provided with a fixing hole. The airbag fixing tray is sleeved and fixed on one end of the birdcage coil fixing cylinder through the fixing hole. The diameter of the airbag fixing tray is the same as the outer diameter of the coil fixing tray. A fixed airbag is arranged on the side of the airbag fixing tray. One end of the airbag control line is connected to the fixed airbag, and the other end of the airbag control line passes through the line support holes of all coil fixing trays and extends out of the transmitter coil. The hot air delivery pipe is fixed on the inner wall of the animal bed bracket. One end of the hot air delivery pipe extends into the birdcage coil fixing cylinder, and the other end extends out of the animal bed bracket.

[0012] As described above, the physiological signal transmission module includes an animal rectal temperature test probe, a temperature test probe, a blood oxygen clamp, and a photoelectric converter. The animal rectal temperature test probe, the temperature test probe, and the blood oxygen clamp are all arranged in the animal bed bracket. The transmitter coil also includes a physiological monitoring signal transmission line. The physiological monitoring signal transmission line includes a protective shell, multiple wires, and an optical fiber. The blood oxygen clamp is connected to the input end of the photoelectric converter through the optical fiber. The output end of the photoelectric converter is connected to the wire. The animal rectal temperature test probe and the temperature test probe are both connected to wires. The wires of the animal rectal temperature test probe, the wires of the temperature test probe, and the wires of the output end of the photoelectric converter are all arranged in the protective shell, and sequentially pass through the wire support holes of all coil fixing trays to extend out of the transmitter coil, and then are connected to the physiological signal transmission multi-channel aviation plug.

[0013] As described above, the receiving coil includes a surface coil fixing bracket, on which a flexible circuit board is arranged. The proton transceiver surface coil, the Xe core receiving surface coil, and the receiving detuning circuit module are all arranged on the flexible circuit board. The proton transceiver surface coil is arranged outside the Xe core receiving surface coil. A slider is also arranged on the surface coil fixing bracket. The shape and size of the slider are adapted to the shape and size of the end face of the receiving coil positioning slot.

[0014] Compared with the prior art, the present invention has the following beneficial effects:

[0015] (1) The device of the present invention is suitable for use in a multi-core 129 Preclinical MRI instruments with Xe radio frequency channels or MRI instruments without transmit and receive switching functions can achieve uniform excitation and high signal-to-noise ratio reception of animal brain signals, plug and play, and simple operation;

[0016] (2) The device of the present invention integrates the acquisition of physiological signals and the switching functions of transmission and reception into a single FPGA chip, realizing the time-sharing switching of the transmitting coil transmitting radio frequency signals and the receiving coil receiving magnetic resonance signals, thereby preventing mutual interference. It can also detect the physiological state of animals in real time, provide multi-dimensional information, and improve integration and scalability.

[0017] (3) The present invention can realize the rapid installation and removal of the emitter coil in the gradient coil by inflating and deflating the fixed airbag, and stably place it through the airbag fixing tray and the coil fixing tray. The installation and removal method is simple and convenient, saving time and labor;

[0018] (4) The device of the present invention can detect proton signals and Xe nuclear signals simultaneously, which is convenient for the correction and registration of magnetic resonance images. BRIEF DESCRIPTION OF THE DRAWINGS

[0019] FIG. 1( a ) is a schematic structural diagram of a transmitter coil of a device of the present invention;

[0020] FIG1( b ) is a schematic diagram of the structure of a physiological signal probe in a transmitting body coil of the device of the present invention;

[0021] Figure 2 is a schematic diagram of the structure of the receiving coil of the device of the present invention;

[0022] Figure 3 is a schematic diagram of the structure of a control box of the device of the present invention;

[0023] FIG4( a ) is a schematic diagram of the structure of a magnetic resonance mainframe in an embodiment in which the device of the present invention is not applied;

[0024] FIG4( b ) is a schematic diagram of the structure of applying the device of the present invention to a magnetic resonance host in an embodiment;

[0025] Reference numerals and corresponding component names:

[0026] 101—physiological signal transmission multi-channel aerial plug; 102—animal bed bracket; 103—hot air delivery duct; 104—bird cage coil; 105—air bag fixing tray; 106—fixed air bag; 107—bird cage coil fixing cylinder; 108—air bag control line; 109—coil signal transmission BNC line; 110—physiological monitoring signal transmission line; 111—coil fixing tray; 112—receiving coil positioning slide; 113—animal rectal temperature test probe; 114—temperature test probe; 115—blood oxygen clamp; 117—optical fiber; 201—surface coil fixing bracket; 202—proton transceiver integrated surface coil; 203—Xe nuclear receiving surface coil; 204—slider; 205—proton coil signal transmission line; 206—Xe nuclear coil signal transmission line; 207—receiving detuning circuit module; 301—blink signal input port; 302—physiological signal transmission aviation socket; 303—220V AC plug; 304—detuning circuit BNC interface; 305—FPGA power supply board; 306—FPGA chip; 307—detuning circuit control module; 308—physiological signal receiving module; 309—USB interface; 401—RF power amplifier; 402—RF receiving electronic unit; 403—control box; 404—photoelectric converter; 405—optical probe; 406—thermistor; 407—transmitter coil; 408—receiving coil; 409—detuning control circuit. DETAILED DESCRIPTION

[0027] In order to facilitate those skilled in the art to understand and implement the present invention, the present invention is further described in detail below in conjunction with embodiments. The embodiments described herein are only used to illustrate and explain the present invention and are not intended to limit the present invention.

[0028] Example

[0029] A multimodal signal detection device for brain hyperpolarized xenon magnetic resonance imaging, comprising a transmitting body coil 407, a receiving coil 408, and a control box 403, wherein the control box 403 is provided with a detuning circuit BNC interface 304 and a physiological signal transmission aviation socket 302, wherein the detuning circuit BNC interface 304 comprises a first detuning circuit BNC interface and a second detuning circuit BNC interface, wherein the transmitting body coil 407 comprises a birdcage coil 104, a transmitting detuning circuit module, and a physiological signal transmission module, wherein the birdcage coil 104 is connected to the transmitting detuning circuit module as a resonant inductor of the transmitting detuning circuit module, wherein the transmitting detuning circuit module is provided with a radio frequency input port and a transmitting detuning control port ... receiving coil 408, wherein the transmitting detuning circuit module is provided with a receiving coil 403, wherein the transmitting detuning circuit module is provided with a receiving coil 408, wherein the transmitting detuning circuit module is provided with a receiving coil 408, wherein the transmitting detuning circuit module is provided with a receiving coil 408, wherein the transmitting detuning circuit module is provided with a receiving coil 408, wherein the transmitting de The control port is connected to the first detuning circuit BNC interface through a first detuning control BNC line, the receiving coil 408 includes a proton transceiver integrated surface coil 202, a Xe core receiving surface coil 203, and a receiving detuning circuit module 207, the Xe core receiving surface coil 203 is connected to the receiving detuning circuit module 207 as a resonant inductor in the receiving detuning circuit module 207, and the receiving detuning circuit module 207 is provided with a radio frequency output port and a receiving detuning control port, the receiving detuning control port is connected to the second detuning circuit BNC interface through a second detuning control BNC line, and the physiological signal transmission module is connected to the physiological signal transmission aviation socket 302 through the physiological signal transmission multi-channel aviation socket 101.

[0030] The control box 403 is provided with an FPGA chip 306 and an FPGA power supply board 305. The FPGA chip 306 is connected to the output interface of the FPGA power supply board 305. The FPGA chip 306 is provided with a detuning circuit control module 307 and a physiological signal receiving module 308. The detuning circuit control module 307 is connected to the transmitting detuning control port and the receiving detuning control port through the first detuning circuit BNC interface and the second detuning circuit BNC interface, respectively. The physiological signal receiving module 308 is connected to the physiological signal transmission module through the physiological signal transmission multi-channel aviation plug 101. The FPGA chip 306 is also provided with a blink signal input port 301 and a USB interface 309.

[0031] The transmitting coil 407 also includes a semi-cylindrical animal bed bracket 102 and a birdcage coil fixing cylinder 107. The birdcage coil fixing cylinder 107 is sleeved on the animal bed bracket 102. The radius of the birdcage coil fixing cylinder 107 is adapted to the radius of the animal bed bracket 102. The birdcage coil 104 is sleeved and fixed on the birdcage coil fixing cylinder 107. The inner wall of the birdcage coil fixing cylinder 107 is provided with a receiving coil positioning groove 112. The receiving coil positioning groove 112 is along the axial direction of the birdcage coil fixing cylinder 107.

[0032] The transmitting coil 407 also includes two semicircular coil fixing trays 111, an airbag fixing tray 105, a fixed airbag 106, an airbag control line 108, and a hot air delivery duct 103. The two coil fixing trays 111 are both mounted and fixed on the animal bed bracket 102. The two coil fixing trays 111 are both provided with a wire support hole. One end of the first detuning control BNC line is connected to the transmitting detuning control port. The other end of the first detuning control BNC line passes through the wire support holes of the two coil fixing trays 111 in turn and extends out of the transmitting coil 407, and then is connected to the first detuning circuit BNC interface. The airbag fixing tray 105 is provided with a fixing hole, and the radius of the fixing hole is the same as the birdcage line. The radius of the coil fixing cylinder 107 is adapted, the diameter of the airbag fixing tray 105 is the same as the outer diameter of the coil fixing tray 111, the airbag fixing tray 105 is fixed to one end of the birdcage coil fixing cylinder 107 through a fixing hole, a fixed airbag 106 is arranged on the side of the airbag fixing tray 105, one end of the airbag control line 108 is connected to the fixed airbag 106, the other end of the airbag control line 108 passes through the line support holes of all the coil fixing trays 111 and extends out of the transmitter coil 407, the hot air delivery duct 103 is fixed to the inner wall of the animal bed bracket 102, one end of the hot air delivery duct 103 extends into the birdcage coil fixing cylinder 107, and the other end extends out of the animal bed bracket 102.

[0033] The physiological signal transmission module includes an animal anal temperature test probe 113, a temperature test probe 114, a blood oxygen clamp 115, and a photoelectric converter 404. The animal anal temperature test probe 113, the temperature test probe 114, and the blood oxygen clamp 115 are all arranged in the animal bed bracket 102. The transmitter coil 407 also includes a physiological monitoring signal transmission line 110. The physiological monitoring signal transmission line 110 includes a protective shell, multiple wires, and an optical fiber 117. The blood oxygen clamp 115 is connected to the input end of the photoelectric converter 404 through the optical fiber 117. The output end of the photoelectric converter 404 is connected to a wire. The animal anal temperature test probe 113 and the temperature test probe 114 are both connected to wires. The wires of the animal anal temperature test probe 113, the wires of the temperature test probe 114, and the wires of the output end of the photoelectric converter 404 are all arranged in the protective shell, and sequentially pass through the wire support holes of all coil fixing trays 111 to extend out of the transmitter coil 407, and then are connected to the physiological signal transmission multi-channel aviation plug 101.

[0034] The animal anal temperature test probe 113 is provided with a first thermistor, the temperature test probe 114 is provided with a second thermistor, and the blood oxygen clamp 115 is provided with an optical probe 405; the thermistor 406 includes a first thermistor and a second thermistor.

[0035] The blood oxygen clamp 115 is used to clamp on the fixed part of the experimental animal to ensure the constant optical path, and measure the blood oxygen information of the experimental animal through the optical probe 405, and transmit the optical signal containing the blood oxygen information of the experimental animal to the photoelectric converter 404 through the optical fiber 117; the photoelectric converter 404 is used to convert the optical signal containing the blood oxygen information of the experimental animal transmitted through the optical fiber 117 into an electrical signal;

[0036] The animal rectal temperature test probe 113 measures the animal body temperature of a specific part of the animal through a first thermistor arranged inside, and the temperature test probe 114 measures the temperature inside the birdcage coil fixing cylinder 107 through a second thermistor. The hot air delivery duct 103 is used to deliver external hot air into the birdcage coil fixing cylinder 107 to maintain the internal temperature of the birdcage coil fixing cylinder 107 and the body temperature of the experimental animal.

[0037] By placing the physiological signal probe (i.e., the animal rectal temperature test probe 113, the temperature test probe 114, and the blood oxygen clamp 115) inside the transmitter coil 407, the time for installing the physiological signal probe in each experiment can be greatly reduced. Meanwhile, providing a protective shell can reduce external interference with the electrical signal.

[0038] The receiving coil 408 includes a surface coil fixing bracket 201, on which a flexible circuit board is pasted. The proton transceiver surface coil 202, the Xe nucleus receiving surface coil 203, and the receiving detuning circuit module 207 are all arranged on the flexible circuit board. The proton transceiver surface coil 202 is arranged outside the Xe nucleus receiving surface coil 203. A slider 204 is also arranged on the surface coil fixing bracket 201. The shape and size of the slider 204 are adapted to the shape and size of the end face of the receiving coil positioning slot 112, and a locking mechanism is arranged on the slider 204.

[0039] The present invention is applicable to a magnetic resonance host without a multi-core radio frequency signal transmission and reception switching function, the magnetic resonance host comprises a permanent magnet, a gradient coil, a radio frequency power amplifier 401, and a radio frequency receiving electronic unit 402, the permanent magnet is sleeved outside the gradient coil, the permanent magnet and the gradient coil respectively generate uniform B 0 The gradient coil is set outside the transmitter coil 407 of the present invention, and the position of the transmitter coil 407 is adjusted so that the birdcage coil 104 on the transmitter coil 407 is located at the center of the permanent magnet and the gradient coil, so that the birdcage coil 104 and the B inside the birdcage coil 104 0The field is uniform, and the fixed airbag 106 can be inflated through the airbag control line 108 to fix the position of the transmitter coil 407 in the gradient coil. The coil fixing tray 111 and the airbag fixing tray 105 can place the transmitter coil 407 stably in the gradient coil; the RF power amplifier 401 is provided with an RF output interface and a blink signal interface, the RF receiving electronic unit 402 is provided with a multi-core receiving interface and a hydrogen nucleus receiving interface, the blink signal input port 301 of the control box 403 is connected to the blink signal interface of the RF power amplifier 401, the USB interface 309 of the control box 403 is connected to an external computer, and the input interface of the FPGA power supply board 305 is connected to the 220V AC power plug 303.

[0040] The RF input port of the transmitting detuning circuit module is connected to one end of the coil signal transmission BNC line 109, and the other end of the coil signal transmission BNC line 109 passes through the wire support holes of the two coil fixing trays 111 in turn and extends out of the transmitting body coil 407, and then is connected to the RF output port of the RF power amplifier 401; the proton transceiver integrated surface coil 202 is connected to the hydrogen nucleus receiving interface of the RF receiving electronic unit 402 through the proton coil signal transmission line 205, and the RF output port of the receiving detuning circuit module 207 is connected to the multi-core receiving interface of the RF receiving electronic unit 402 through the Xe nucleus coil signal transmission line 206.

[0041] Usually in hyperpolarization 129 Xe In vivo brain imaging animal experiments require the use of a customized animal bed, where the experimental animal is placed on the animal bed, which is then placed on the animal bed bracket 102, and the brain of the experimental animal is placed in a B 0 The receiving coil 408 is positioned at the center of the radio frequency field, the gradient field G, and the birdcage coil 104, and then the slider 204 on the receiving coil 408 is placed in the receiving coil positioning slot 112 of the transmitter coil 407, and the position of the receiving coil 408 is changed by sliding the slider 204 in the receiving coil positioning slot 112, so that the proton transceiver integrated surface coil 202 and the Xe nucleus receiving surface coil 203 on the receiving coil 408 are located directly below the brain of the experimental animal, and then the position of the receiving coil 408 is fixed by the locking mechanism on the slider 204.

[0042] The proton transceiver surface coil 202 can obtain the positioning image of the experimental animal, the brain proton image and other information. The Xe core receiving surface coil 203 transmits the received Xe signal to the multi-core receiving interface through the Xe core coil signal transmission line 206. The receiving detuning circuit module 207 can control the normal resonance operation or detuning of the Xe core receiving surface coil 203, and can prevent the DC component from entering the RF receiving electronic unit 402 of the magnetic resonance host, thereby playing a protective role. The receiving coil positioning slide groove 112 is used to cooperate with the slider 204 on the receiving coil 408.

[0043] The transmission detune circuit module and the reception detune circuit module 207 constitute a detune control circuit 409 .

[0044] The physiological signal receiving module 308 receives the electrical signal containing blood oxygen information and temperature, and transmits the waveform of the electrical signal containing blood oxygen information and temperature to an external computer for recording through the USB interface 309.

[0045] The entire control box 403 is powered by the FPGA power supply board 305. The output interface of the FPGA power supply board 305 includes multiple output interfaces of different levels (such as -30V output interface, -5V output interface, and +5V output interface). The main function of the FPGA power supply board 305 is to provide different levels for the FPGA chip 306.

[0046] The control box 403 is used to switch between the receiving mode and the transmitting mode. The RF power amplifier 401 inputs the 0.3V / 3.3V switching blink signal into the FPGA chip 403 in the control box 403, and is processed into a -30V / +5V switching pulse signal with the same phase and output to the transmitting detuning circuit module and the receiving detuning circuit module 207, thereby controlling the detuning of the birdcage coil 104 and the Xe core receiving surface coil 203. The birdcage coil 104 and the Xe core receiving surface coil 203 are controlled by the same level signal. When the level signal is +5V, the birdcage coil 104 is in a resonant state and the Xe core receiving surface coil 203 is in a detuned state; when the level signal is -30V, the birdcage coil 104 is in a detuned state and the Xe core receiving surface coil 203 is in a resonant state.

[0047] The FPGA chip 306 is used to determine whether the birdcage coil 104 is detuned, whether the Xe core receiving surface coil 203 is detuned, to transmit and collect electrical signals for blood oxygen information of experimental animals and to receive electrical signals containing blood oxygen information of experimental animals, as well as to transmit and collect electrical signals for the internal temperature of the birdcage coil fixing cylinder 107 and the body temperature of experimental animals and to receive electrical signals for the internal temperature of the birdcage coil fixing cylinder 107 and the body temperature of experimental animals.

[0048] It should be noted that the embodiments described in the present invention are merely examples of the spirit of the present invention. Those skilled in the art may make various modifications or additions to the described embodiments or replace them in similar ways, but they will not deviate from the spirit of the present invention or exceed the scope defined by the attached claims.

Claims

1. A multimodal signal detection device for brain hyperpolarized xenon magnetic resonance imaging, comprising a transmitting body coil (407), a receiving coil (408), and a control box (403), characterized in that: The control box (403) is provided with a detuning circuit BNC interface (304) and a physiological signal transmission aviation socket (302); the detuning circuit BNC interface (304) includes a first detuning circuit BNC interface and a second detuning circuit BNC interface; the transmitting body coil (407) includes a birdcage coil (104), a transmitting detuning circuit module, and a physiological signal transmission module; the birdcage coil (104) is connected to the transmitting detuning circuit module; the transmitting detuning circuit module is provided with a radio frequency input port and a transmitting detuning control port; the transmitting detuning control port is connected to the first detuning circuit BNC interface via a first detuning control BNC line. The receiving coil (408) comprises a proton transceiver integrated surface coil (202), a Xe nucleus receiving surface coil (203), and a receiving detuning circuit module (207); the Xe nucleus receiving surface coil (203) is connected to the receiving detuning circuit module (207); a radio frequency output port and a receiving detuning control port are provided on the receiving detuning circuit module (207); the receiving detuning control port is connected to the second detuning circuit BNC interface via a second detuning control BNC line; and the physiological signal transmission module is connected to the physiological signal transmission aviation socket (302) via a physiological signal transmission multi-channel aviation socket (101); The transmitting coil (407) further comprises a semi-cylindrical animal bed bracket (102) and a birdcage coil fixing cylinder (107); the birdcage coil fixing cylinder (107) is sleeved on the animal bed bracket (102); the birdcage coil (104) is sleeved and fixed on the birdcage coil fixing cylinder (107); a receiving coil positioning slide groove (112) is provided on the inner wall of the birdcage coil fixing cylinder (107); the receiving coil positioning slide groove (112) is along the axial direction of the birdcage coil fixing cylinder (107); The transmitter coil (407) further comprises a plurality of semi-circular coil fixing trays (111), an airbag fixing tray (105), a fixed airbag (106), an airbag control line (108), and a hot air delivery duct (103); the coil fixing trays (111) are all sleeved and fixed on the animal bed bracket (102); all coil fixing trays (111) are provided with a line support hole; the airbag fixing tray (105) is provided with a fixing hole; the airbag fixing tray (105) is sleeved and fixed on one end of the bird cage coil fixing cylinder (107) through the fixing hole; the airbag fixing tray (105) is sleeved and fixed on one end of the bird cage coil fixing cylinder (107) through the fixing hole; ) has a diameter that is the same as the outer diameter of the coil fixing tray (111), a fixed air bag (106) is arranged on the side of the air bag fixing tray (105), one end of the air bag control line (108) is connected to the fixed air bag (106), the other end of the air bag control line (108) passes through the line support holes of all the coil fixing trays (111) and extends out of the transmitter coil (407), the hot air delivery pipe (103) is fixed to the inner wall of the animal bed bracket (102), one end of the hot air delivery pipe (103) extends into the bird cage coil fixing cylinder (107), and the other end extends out of the animal bed bracket (102); The receiving coil (408) comprises a surface coil fixing bracket (201), a flexible circuit board is arranged on the surface coil fixing bracket (201), a proton transceiver integrated surface coil (202), a Xe nucleus receiving surface coil (203), and a receiving detuning circuit module (207) are all arranged on the flexible circuit board, the proton transceiver integrated surface coil (202) is arranged outside the Xe nucleus receiving surface coil (203), and a slider (204) is also arranged on the surface coil fixing bracket (201), and the shape and size of the slider (204) are both adapted to the shape and size of the end face of the receiving coil positioning slide groove (112).

2. A multimodal signal detection device for brain hyperpolarized xenon magnetic resonance imaging according to claim 1, characterized in that: The control box (403) is provided with an FPGA chip (306) and an FPGA power supply board (305) inside. The FPGA chip (306) is connected to the output interface of the FPGA power supply board (305). The FPGA chip (306) is provided with a detuning circuit control module (307) and a physiological signal receiving module (308). The detuning circuit control module (307) is connected to the transmitting detuning control port and the receiving detuning control port respectively through a first detuning circuit BNC interface and a second detuning circuit BNC interface. The physiological signal receiving module (308) is connected to the physiological signal transmission module through a physiological signal transmission multi-channel aerial plug (101). The FPGA chip (306) is also provided with a blink signal input port (301) and a USB interface (309).

3. A multimodal signal detection device for brain hyperpolarized xenon magnetic resonance imaging according to claim 1, characterized in that: The physiological signal transmission module comprises an animal rectal temperature test probe (113), a temperature test probe (114), a blood oxygen clamp (115), and a photoelectric converter (404); the animal rectal temperature test probe (113), the temperature test probe (114), and the blood oxygen clamp (115) are all arranged in the animal bed bracket (102); the transmitting body coil (407) further comprises a physiological monitoring signal transmission line (110); the physiological monitoring signal transmission line (110) comprises a protective housing, a plurality of wires, and an optical fiber (117); the blood oxygen clamp (115) is connected to the optical fiber (117); 17) is connected to the input end of the photoelectric converter (404), the output end of the photoelectric converter (404) is connected to a wire, the animal rectal temperature test probe (113) and the temperature test probe (114) are both connected to wires, the wires of the animal rectal temperature test probe (113), the wires of the temperature test probe (114), and the wires at the output end of the photoelectric converter (404) are all arranged in a protective housing, and sequentially pass through the wire support holes of all coil fixing trays (111) to extend outside the transmitter coil (407), and then connected to the physiological signal transmission multi-channel aviation plug (101).

Images