CN113616181B - Multi-mode optical and magnetic nanoparticle imaging fusion brain detection system - Google Patents

Multi-mode optical and magnetic nanoparticle imaging fusion brain detection system Download PDF

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CN113616181B
CN113616181B CN202111090418.2A CN202111090418A CN113616181B CN 113616181 B CN113616181 B CN 113616181B CN 202111090418 A CN202111090418 A CN 202111090418A CN 113616181 B CN113616181 B CN 113616181B
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CN113616181A (en
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钟江宏
岳杭琪
郑婵钰
陈重衡
田捷
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Beihang University
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/05—Detecting, measuring or recording for diagnosis by means of electric currents or magnetic fields; Measuring using microwaves or radio waves 
    • A61B5/0515—Magnetic particle imaging
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/0033—Features or image-related aspects of imaging apparatus classified in A61B5/00, e.g. for MRI, optical tomography or impedance tomography apparatus; arrangements of imaging apparatus in a room
    • A61B5/0035—Features or image-related aspects of imaging apparatus classified in A61B5/00, e.g. for MRI, optical tomography or impedance tomography apparatus; arrangements of imaging apparatus in a room adapted for acquisition of images from more than one imaging mode, e.g. combining MRI and optical tomography
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/0033—Features or image-related aspects of imaging apparatus classified in A61B5/00, e.g. for MRI, optical tomography or impedance tomography apparatus; arrangements of imaging apparatus in a room
    • A61B5/004—Features or image-related aspects of imaging apparatus classified in A61B5/00, e.g. for MRI, optical tomography or impedance tomography apparatus; arrangements of imaging apparatus in a room adapted for image acquisition of a particular organ or body part
    • A61B5/0042—Features or image-related aspects of imaging apparatus classified in A61B5/00, e.g. for MRI, optical tomography or impedance tomography apparatus; arrangements of imaging apparatus in a room adapted for image acquisition of a particular organ or body part for the brain
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
    • A61B5/0071—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence by measuring fluorescence emission
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B2503/00—Evaluating a particular growth phase or type of persons or animals
    • A61B2503/40—Animals
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B2503/00—Evaluating a particular growth phase or type of persons or animals
    • A61B2503/42—Evaluating a particular growth phase or type of persons or animals for laboratory research
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B2576/00—Medical imaging apparatus involving image processing or analysis
    • A61B2576/02—Medical imaging apparatus involving image processing or analysis specially adapted for a particular organ or body part
    • A61B2576/026—Medical imaging apparatus involving image processing or analysis specially adapted for a particular organ or body part for the brain
    • Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y02—TECHNOLOGIES OR APPLICATIONS FOR MITIGATION OR ADAPTATION AGAINST CLIMATE CHANGE
    • Y02A—TECHNOLOGIES FOR ADAPTATION TO CLIMATE CHANGE
    • Y02A50/00—TECHNOLOGIES FOR ADAPTATION TO CLIMATE CHANGE in human health protection, e.g. against extreme weather
    • Y02A50/30—Against vector-borne diseases, e.g. mosquito-borne, fly-borne, tick-borne or waterborne diseases whose impact is exacerbated by climate change

Abstract

The invention discloses a brain detection system integrating multi-mode optical and magnetic nanoparticle imaging, which comprises a scanner, a control module and a signal receiving module, wherein the scanner comprises a driving coil, a selecting coil and a receiving coil, the selecting coil is arranged at two ends of the receiving coil and is used for constructing a static gradient magnetic field, namely a selecting field, and driving all magnetic nanoparticles except particles near a field-free point to be saturated; the driving coil is arranged outside the receiving coil and used for constructing a sine excitation magnetic field, namely a driving field; the receiving coil is used for collecting voltage signals; the control module is used for controlling the current to enable the driving coil to apply a uniform oscillating magnetic field, particles near the field-free point are driven to pass through an object of interest, and the magnetization intensity of the particles is changed, so that a voltage signal is induced in the receiving coil, and the signal is processed by the signal receiving module and then image reconstruction is carried out by adopting an X space MPI. The invention effectively improves the experimental efficiency and the analysis efficiency, and can be used for the extracellular trap imaging analysis of monocytes and T cells.

Description

Multi-mode optical and magnetic nanoparticle imaging fusion brain detection system
Technical Field
The invention belongs to the technical field of biomedical images, and particularly relates to a brain detection system with multi-mode optical and magnetic nanoparticle imaging fusion.
Background
Systemic Lupus Erythematosus (SLE) is a complex autoimmune disease affecting multiple organs and tissues. Patterns of clinical manifestations and organ involvement have a wide variety, with cognitive impairment occurring in up to 80% of lupus patients (Nat Rev Rheumatol 2019; 15:137-152). The lupus encephalopathy is unknown in cause, and has very important significance in exploring the evolution process and molecular mechanism of the lesion. In a physiological environment, the redox balance system is maintained by reactive oxygen species (Reactive oxygen species, ROS) and antioxidants. ROS are involved in a variety of cellular pathways, as signal molecules for immunomodulation, in the generation of Neutrophil Extracellular Traps (NET) and in physiological and pathological processes such as autophagy. Earlier studies in this subject group found that mutations in the Ncf1 gene resulted in reduced ROS release and enhanced inflammation in the NOX2 complex. ROS are considered important signaling molecules that regulate autoimmune diseases and lupus, but the mechanisms are unknown.
Optical imaging has been widely applied to the biomedical engineering field, and has the technical advantages of high specificity, high sensitivity and the like; magnetic Particle Imaging (MPI) is a novel imaging technique, the principle of which is to use the non-linear magnetization characteristic of magnetic nanoparticles in a zero magnetic field to detect the spatial distribution of magnetic nanoparticle tracers. In recent years, MPI has begun to be applied in basic research fields such as cell tracking, angiography, and inflammatory imaging.
In recent years, research and development of the conventional magnetic particle imaging have the advantages of high sensitivity, high resolution, no limitation of tissue penetration depth and the like, but few multi-mode optical-magnetic nanoparticle fusion equipment are developed; most MPI receiving coils are cylindrical, and special-shaped coils attached to the detection part are rarely designed; in addition, the diameters of the magnetic nano particles are mainly distributed in the range of 2-20 nanometers, and although millimeter-level resolution can be realized in the MPI of small animals, the magnetic particles can be endocytosed by immune cells and the like, so that the molecular marker off-target effect exists, and the problem of imaging accuracy reduction is caused. Therefore, the specificity defect of single cell imaging still exists, and imaging analysis and research on regulatory mechanisms such as extracellular traps induced by active oxygen are difficult.
Disclosure of Invention
In order to solve the defects existing in the prior art, the invention provides a brain detection system with multi-mode optical and magnetic nanoparticle imaging fusion, which has the following specific technical scheme:
a multi-modal optical and magnetic nanoparticle imaging fused brain detection system comprising: scanner, control module, signal receiving module, wherein,
the scanner comprises a driving coil, a selecting coil and a receiving coil, wherein the selecting coil is arranged at two ends of the receiving coil and is used for constructing a static gradient magnetic field, namely a selecting field, and driving all magnetic nano particles except particles near a field-free point to be saturated; the driving coil is arranged outside the receiving coil and used for constructing a sine excitation magnetic field, namely a driving field; the receiving coil is used for collecting voltage signals; the signal receiving module comprises a band-stop filter, a low noise amplifier and an analog-to-digital converter which are connected in sequence;
the control module comprises a PC end, a digital-to-analog converter, a power amplifier and a band-pass filter which are sequentially connected, and is used for controlling current to enable the driving coil to apply a uniform oscillating magnetic field, particles near a field-free point are driven to pass through an object of interest, the magnetization intensity of the particles is changed, voltage signals are induced in the receiving coil, and the voltage signals are processed by the signal receiving module and then subjected to image reconstruction by adopting an X space MPI.
Further, a permanent magnet is used as a selection coil, an excitation coil is used as a driving coil, and a gradiometer coil composed of litz wire is used as a receiving coil.
Further, the receiving coil is attached to the brain of the tested object and is in a semi-elliptical cone shape, one end face is semi-elliptical, the other end face is semi-circular, the two end faces are parallel, and the connecting line of the central points of the receiving coil and the receiving coil is perpendicular to the long axis of the ellipse.
Further, the long half-axis length a of the semi-elliptical end face is 20mm at maximum, the short-axis length b is 25mm at maximum, and the included angle theta between the line between the vertex of the semi-elliptical end face and the vertex of the semi-circular end face and the horizontal line is 18 DEG to 24 deg.
Further, the permanent magnet forms a static gradient magnetic field of 4-8T/m, and the exciting coil forms a sine exciting magnetic field of 15-25 mT/m.
Further, the permanent magnet forms a static gradient magnetic field of 6T/m, and the exciting coil forms a sinusoidal exciting magnetic field of 20 mT/m.
Further, in order to realize imaging analysis of extracellular traps of brain of a detected object, the detection system is matched with a multi-mode optical and magnetic nanoparticle probe, firstly fluorescent dye is adopted to modify magnetic nanoparticles to obtain optically marked magnetic nanoparticles, then the magnetic nanoparticles are combined with polypeptides to form the multi-mode optical and magnetic nanoparticle probe, and then the brain of the detected object is imaged by the scanner.
A method for detecting a brain detection system with multi-modal optical and magnetic nanoparticle imaging fusion, comprising the following steps:
s1: establishing a tested object model;
s2: combining the wrapped magnetic nano particles with the polypeptide to form a multi-mode optical and magnetic nano particle probe, and using an in-vivo labeling method for imaging analysis of a brain extracellular trap mechanism;
s3: moving the brain of the tested object into the receiving coil;
s4: the control module controls the current to enable the driving coil to apply a uniform oscillating magnetic field;
s5: the signal collected by the receiving coil is collected after being processed by the signal receiving module;
s6: the acquired data is reconstructed using X-space MPI.
The invention has the beneficial effects that:
1. the invention adopts the reverse winding gradiometer coil which is attached to the head of the measured object and has the size and the structure as the receiving coil, thereby achieving the purpose of being closer to the region of interest (ROI), improving the signal quality and the imaging sensitivity and weakening the strong signals from other parts of the measured object; thereby improving the analysis efficiency;
2. the invention adopts the bimodal molecular image to effectively improve the experimental efficiency;
3. the invention combines functional molecule neutral avidin on the surface of the optically marked low-diameter magnetic nano particle with biotin conjugated marked polypeptide to form a multi-mode magnetic nano particle probe, which can achieve single-cell specific level imaging.
Drawings
For a clearer description of an embodiment of the invention or of the solutions of the prior art, reference will be made to the accompanying drawings, which are used in the embodiments and which are intended to illustrate, but not to limit the invention in any way, the features and advantages of which can be obtained according to these drawings without inventive labour for a person skilled in the art. Wherein:
FIG. 1 is an overall block diagram of the present invention;
FIG. 2 is a scanner configuration diagram of the present invention;
fig. 3 is a schematic diagram of a receiving coil structure according to the present invention.
Detailed Description
In order that the above-recited objects, features and advantages of the present invention will be more clearly understood, a more particular description of the invention will be rendered by reference to the appended drawings and appended detailed description. It should be noted that, without conflict, the embodiments of the present invention and features in the embodiments may be combined with each other.
In the following description, numerous specific details are set forth in order to provide a thorough understanding of the present invention, however, the present invention may be practiced in other ways than those described herein, and therefore the scope of the present invention is not limited to the specific embodiments disclosed below.
As shown in fig. 1, a brain detection system with multi-modal optical and magnetic nanoparticle imaging fusion, comprising: scanner, control module, signal receiving module, wherein,
as shown in fig. 2, the scanner includes a driving coil, a selection coil and a receiving coil, wherein the selection coil is disposed at two ends of the receiving coil, and is used for constructing a static gradient magnetic field, namely a selection field, and driving all magnetic nanoparticles except for particles near a field-free point to be saturated; the driving coil is arranged outside the receiving coil and used for constructing a sine excitation magnetic field, namely a driving field; the receiving coil is used for collecting voltage signals; the signal receiving module comprises a band-stop filter, a low-noise amplifier and an analog-to-digital converter which are connected in sequence;
the control module comprises a PC end, a digital-to-analog converter, a power amplifier and a band-pass filter which are sequentially connected, and is used for controlling current to enable the driving coil to apply a uniform oscillating magnetic field, particles near a field-free point are driven to pass through an object of interest, the magnetization intensity of the particles is changed, and therefore voltage signals are induced in the receiving coil, and the voltage signals are processed through the signal receiving module and then are reconstructed by adopting X space MPI.
In some embodiments, a permanent magnet is used as the selection coil, an excitation coil is used as the drive coil, and a gradiometer coil of litz wire is used as the receiving coil.
Preferably, the receiving coil is attached to the brain of the tested object and is in a semi-elliptical cone shape, one end face is semi-elliptical, the other end face is semi-circular, the two end faces are parallel, and the connecting line of the central points of the receiving coil and the receiving coil is perpendicular to the long axis of the ellipse.
In some embodiments, the long half-axis length a of the semi-elliptical end face is at most 20mm, the short-axis length b is at most 25mm, and the included angle θ between the line between the vertex of the semi-elliptical end face and the vertex of the semi-circular end face and the horizontal is 18 ° -24 °; for different measured objects, the size of the receiving coil can be adjusted in equal proportion according to the shape and the size of the head.
In some embodiments, the permanent magnets constitute a static gradient magnetic field of 4-8T/m and the excitation coils constitute a sinusoidal excitation magnetic field of 15-25 mT/m.
Preferably, the permanent magnet forms a static gradient magnetic field of 6T/m and the excitation coil forms a sinusoidal excitation magnetic field of 20 mT/m.
In some embodiments, to realize imaging analysis of extracellular traps of a brain of a detected object, a detection system is matched with a multi-mode optical and magnetic nanoparticle probe, firstly, fluorescent dye is adopted to modify magnetic nanoparticles to obtain optically marked magnetic nanoparticles, then the magnetic nanoparticles are combined with polypeptides to form the multi-mode optical and magnetic nanoparticle probe, and then a scanner is used for imaging the brain of the detected object.
A method for detecting a brain detection system with multi-modal optical and magnetic nanoparticle imaging fusion, comprising the following steps:
s1: establishing a tested object model;
s2: combining the wrapped magnetic nano particles with the polypeptide to form a multi-mode optical and magnetic nano particle probe, and adopting an in-vivo labeling method for imaging analysis of an active oxygen induced brain extracellular trap mechanism;
s3: moving the brain of the tested object into the receiving coil;
s4: the control module controls the current to enable the driving coil to apply a uniform oscillating magnetic field;
s5: the signal collected by the receiving coil is collected after being processed by the signal receiving module;
s6: the acquired data is reconstructed using X-space MPI.
In order to facilitate understanding of the above technical solutions of the present invention, the following detailed description of the above technical solutions of the present invention is provided by specific embodiments.
Example 1
The brain detection system with the multi-mode optical and magnetic nanoparticle imaging fusion is used for carrying out experiments on mice, and the extracellular trap specificity imaging of monocytes and T cells is carried out on the brains of the mice, so that the action mechanism of active oxygen in autoimmune diseases is analyzed. The method comprises the following specific steps:
s1: a mouse model was established.
In the experiment, 5 healthy female C57BL/6J mice are adopted firstly, the weight is 25g, and the age is 7-8 weeks;
injecting 0.5ml pristane into each mouse body by adopting an intraperitoneal injection method, and establishing a lupus mouse model.
S2: combining the wrapped magnetic nano particles with the polypeptide to form a multi-mode optical and magnetic nano particle probe, and using the multi-mode nano particle molecular probe in-vivo labeling method for brain extracellular trap imaging;
s3: the special shape coil attached to the brain of the mouse is adopted to improve the sensitivity, and the mouse brain is moved into the receiving coil by using the mouse bed;
s4: the control module controls the current to enable the driving coil to apply a uniform oscillating magnetic field;
s5: the signal collected by the receiving coil is collected after being processed by the signal receiving module;
s6: the acquired data is reconstructed using X-space MPI.
In vivo imaging system control and image processing was performed on a computer equipped with an Intel-Rui 2 dual-core processor, 2.33GHz and 3GB RAM.
Conventional harmonic space MPI image reconstruction relies on a system matrix to pre-characterize the signal response of magnetic nanoparticles, meaning that the system matrix is specific to the nanoparticle sample, and if the nanoparticle behaves differently in tissue, the system drifts or the model is inaccurate, the accuracy of the reconstruction will be reduced. Importantly, MPI must undergo well-conditioned image reconstruction to avoid any signal-to-noise ratio (SNR) loss. And the signal reconstructed by the MPI image in the X space is scanned by the time of the X space, and only the speed compensation and the gridding are involved, so that the robustness and the speed of the MPI image reconstruction are improved to a certain extent.
The in-vivo imaging information is implemented according to the following calculation method:
the basic principle of magnetic particle imaging is the langevin equation:
wherein, the liquid crystal display device comprises a liquid crystal display device,saturation moment for a single magnetic particle, m is the concentration of the particle, +.>Represents Fe 3 O 4 Saturation magnetization, mu 0 Represents vacuum permeability, d is the particle diameter of the magnetic nano particle, and
wherein alpha is Langmuir parameter, k B The magnetic particle characteristic is the particle diameter d and the saturation magnetization M S Characterization.
The magnetic field used by MPI is the time-varying drive field W D (t) and static gradient field W S (x) If the gradient field is uniform, W S (x) By W S (x)＝QxDescribing, Q represents the applied gradient strength, assuming diagonal, q=diag (Q 1 ,q 2 ,q 3 )。
The drive field is typically chosen to have a period length T D Is a periodic track W of (2) D (t) obtaining X for the position of the field-free point (FFP) FFP ＝-Q (-1) W D (t) Voltage Signal U in MPI n (t) is:
wherein s is n (X, t) (n.epsilon. {1,2,3 }) represents the number of systems that depend on space and time, a factorg n Is the inductivity of the nth receiving coil, x n FFP (t) represents the nth coordinate of FFP, x n Is the nth spatial coordinate, z represents the magnetic moment of a nanoparticle, m (x) is the spatial SPIO distribution, ">Representing Langmuin (Langmuin) function for describing the magnetization behavior of SPIOs as a function of external magnetic field,/L->Representing a multi-dimensional langevin function with respect to the nth receive coil.
The reconstruction of the X-space MPI image is achieved according to the following method:
in x-space MPI theory, the image is represented as a convolution of the nanoparticle spatial distribution with the system Point Spread Function (PSF), the key result of the analysis is to obtain a one-dimensional signal equation, indicating that the MPI signal pair is FFP x at the instantaneous position s True spatial convolution of magnetic nanoparticle density ρ of (t) with PSF z (x)Sampling:
wherein the PSF of the system is determined by the magnetization characteristics of the nanoparticles and the magnetic field gradient. The magnetization of superparamagnetic nanoparticles is nonlinear and follows a so-called langevin function. The receiving coil detects only the change in magnetization level and therefore the PSF is the derivative of the langevin function.
The one-dimensional PSF is similar to a lorentz function, dividing the slew rate of the excitation field by various constants, generating the original image in x-space:
the shape h (x) of the system PSF defines the original resolution of the imaging system, using the derivative of the Langiwan function, the spatial resolution of MPI is:
wherein Δx is the full width at half maximum, M of the PSF sat Is the saturation magnetization of the nanoparticle; d is the nanoparticle diameter; k (k) B Is Boltzmann constant, T is temperature, μ 0 Is vacuum permeability.
In the present invention, unless explicitly specified and limited otherwise, the terms "mounted," "connected," "secured," and the like are to be construed broadly, and may be, for example, fixedly connected, detachably connected, or integrally formed; can be mechanically or electrically connected; can be directly connected or indirectly connected through an intermediate medium, and can be communicated with the inside of two elements or the interaction relationship of the two elements. The specific meaning of the above terms in the present invention can be understood by those of ordinary skill in the art according to the specific circumstances.
In the present invention, unless expressly stated or limited otherwise, a first feature "above" or "below" a second feature may include both the first and second features being in direct contact, as well as the first and second features not being in direct contact but being in contact with each other through additional features therebetween. Moreover, a first feature being "above," "over" and "on" a second feature includes the first feature being directly above and obliquely above the second feature, or simply indicating that the first feature is higher in level than the second feature. The first feature being "under", "below" and "beneath" the second feature includes the first feature being directly under and obliquely below the second feature, or simply means that the first feature is less level than the second feature.
In the present invention, the terms "first," "second," "third," "fourth" are used for descriptive purposes only and are not to be construed as indicating or implying relative importance. The term "plurality" refers to two or more, unless explicitly defined otherwise.
The above description is only of the preferred embodiments of the present invention and is not intended to limit the present invention, but various modifications and variations can be made to the present invention by those skilled in the art. Any modification, equivalent replacement, improvement, etc. made within the spirit and principle of the present invention should be included in the protection scope of the present invention.

Claims (8)

1. A multi-modal optical and magnetic nanoparticle imaging fused brain detection system, comprising: scanner, control module, signal receiving module, wherein,
the scanner comprises a driving coil, a selecting coil and a receiving coil, wherein the selecting coil is arranged at two ends of the receiving coil and is used for constructing a static gradient magnetic field, namely a selecting field, and driving all magnetic nano particles except particles near a field-free point to be saturated; the driving coil is arranged outside the receiving coil and used for constructing a sine excitation magnetic field, namely a driving field; the receiving coil is used for collecting voltage signals; the signal receiving module comprises a band-stop filter, a low noise amplifier and an analog-to-digital converter which are connected in sequence;
the control module comprises a PC end, a digital-to-analog converter, a power amplifier and a band-pass filter which are sequentially connected, and is used for controlling current to enable the driving coil to apply a uniform oscillating magnetic field, particles near a field-free point are driven to pass through an object of interest, the magnetization intensity of the particles is changed, so that a voltage signal is induced in the receiving coil, and the voltage signal is processed by the signal receiving module and then subjected to image reconstruction by adopting an X space MPI;
the multi-mode magnetic nanoparticle probe is formed by combining functional molecules of the surface of the optically marked low-diameter magnetic nanoparticle, namely, avidin and biotin conjugated marked polypeptide.
2. The brain detection system of claim 1, wherein a permanent magnet is used as a selection coil, an excitation coil is used as a driving coil, and a gradiometer coil made of litz wire is used as a receiving coil.
3. The brain detection system of claim 1 or 2, wherein the receiving coil is attached to the brain of the detected object, and is semi-elliptical cone-shaped, one end face is semi-elliptical, the other end face is semi-circular, the two end faces are parallel, and the connecting line of the central points of the two end faces is perpendicular to the long axis of the ellipse.
4. A multi-modal optical and magnetic nanoparticle imaging fusion brain detection system as in claim 3 wherein the semi-elliptical end faces have a long semi-axis length a of at most 20mm and a short axis length b of at most 25mm, and the angle θ between the line of the vertices of the semi-elliptical end faces and the horizontal line is 18 ° -24 °.
5. The brain detection system of claim 4, wherein the permanent magnet forms a static gradient magnetic field of 4-8T/m and the exciting coil forms a sinusoidal excitation magnetic field of 15-25 mT/m.
6. The brain detection system of claim 5, wherein the permanent magnet forms a static gradient magnetic field of 6T/m and the excitation coil forms a sinusoidal excitation magnetic field of 20 mT/m.
7. The brain detection system with multi-modal optical and magnetic nanoparticle imaging fusion according to claim 6, wherein to realize imaging analysis of extracellular traps of the brain of the detected object, the detection system is matched with a multi-modal optical and magnetic nanoparticle probe, firstly, the magnetic nanoparticle is modified by fluorescent dye to obtain optically marked magnetic nanoparticle, then the magnetic nanoparticle is combined with polypeptide to form the multi-modal optical and magnetic nanoparticle probe, and then the brain of the detected object is imaged by the scanner.
8. A method of detecting a multimodal optical and magnetic nanoparticle image fusion brain detection system according to any one of claims 1-7, comprising the steps of:
s1: establishing a tested object model;
s2: combining the wrapped magnetic nano particles with the polypeptide to form a multi-mode optical and magnetic nano particle probe, and using an in-vivo labeling method for imaging analysis of a brain extracellular trap mechanism;
s3: moving the brain of the tested object into the receiving coil;
s4: the control module controls the current to enable the driving coil to apply a uniform oscillating magnetic field;
s5: the signal collected by the receiving coil is collected after being processed by the signal receiving module;
s6: the acquired data is reconstructed using X-space MPI.
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