CN115281650A - Multi-frequency bidirectional magnetic induction tomography device and method based on SAE - Google Patents
Multi-frequency bidirectional magnetic induction tomography device and method based on SAE Download PDFInfo
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Abstract
The invention relates to a multi-frequency bidirectional magnetic induction tomography device and method based on SAE. The invention generates an excitation signal based on the generated sinusoidal signal, the excitation signal generates an alternating primary magnetic field in the space, the primary magnetic field acts on the biological tissue, the inside of the biological tissue generates an eddy current under the action of the primary magnetic field, and generates a disturbance magnetic field opposite to the primary magnetic field under the action of the eddy current, so that the magnetic field information of the biological tissue can be detected and obtained, then, a detection image of the biological tissue is generated based on the magnetic field information, and further, the imaging accuracy can be improved while the cerebral hemorrhage position positioning accuracy is improved.
Description
Technical Field
The invention relates to the technical field of image processing, in particular to a multi-frequency bidirectional magnetic induction tomography device and method based on SAE.
Background
Magnetic Induction Tomography (MIT) is a new detection imaging technology, and can be used as a detection technology for diseases such as stroke. With the continuous acceleration of the aging and urbanization process of society, the risk factors of cerebral apoplexy are generally exposed, and the incidence rate rapidly rises. The traditional imaging equipment cannot realize long-time, continuous and dynamic bedside detection due to the large size and radiation. The MIT overcomes the defects of the existing medical imaging equipment, and has the advantages of low equipment frequency, almost no radiation, small volume, head-wearing portable movement realization, low equipment cost, high imaging speed and the like.
However, in the single-frequency MIT imaging used in the current research, because the magnetic field information of a patient before the disease attack cannot be acquired, the single-frequency MIT imaging cannot be applied to actual detection, and meanwhile, the single-frequency MIT imaging is used for unidirectional detection at present, the anti-noise performance is poor, and the imaging accuracy is low under the noisy condition.
Disclosure of Invention
In order to solve the problems in the prior art, the invention provides a multi-frequency bidirectional magnetic induction tomography device and method based on SAE.
In order to achieve the purpose, the invention provides the following scheme:
a multi-frequency bi-directional magnetic induction tomography imaging apparatus based on SAE, comprising:
a signal generator for generating a sinusoidal signal;
the power amplifier is connected with the signal generator and is used for amplifying the sinusoidal signal;
the exciting coil is connected with the power amplifier and is used for generating an exciting signal based on the sinusoidal signal; the excitation signal generates an alternating primary magnetic field in the space, the primary magnetic field acts on biological tissues, the interior of the biological tissues is acted by the primary magnetic field to generate an eddy current, and a disturbance magnetic field opposite to the primary magnetic field is generated under the action of the eddy current;
a detection coil for detecting magnetic field information of the biological tissue;
and the processor is connected with the detection coil and used for generating a detection image of the biological tissue based on the magnetic field information.
Preferably, a magnetic induction tomography imaging model is implanted in the processor; the magnetic induction tomography model is a trained neural network model which takes magnetic field information as input and detection images as output.
Preferably, the method further comprises the following steps:
and the lock-in amplifier is connected with the detection coil and the processor and is used for determining the amplitude of the signal based on the magnetic field information detected by the detection coil.
Preferably, the detecting coils generate proportional phase relations under different excitation signal frequencies under the condition that the conductivity of the imaging body is unchanged.
Preferably, in use, the positions of the excitation and detection coils are moved by rotation.
Preferably, the position of the excitation coil and the position of the detection coil are both rotated by 90 degrees.
A multi-frequency bidirectional magnetic induction tomography imaging method based on SAE comprises the following steps:
acquiring magnetic field information of a biological tissue to be detected;
acquiring a magnetic induction tomography imaging model; the magnetic induction tomography model is a trained neural network model taking magnetic field information as input and detection images as output
And inputting the magnetic field information into the magnetic induction tomography imaging model to obtain a detection image of the biological tissue.
Preferably, before acquiring the magnetic induction tomography imaging model, the method further comprises:
changing the frequency of the excitation signal to obtain magnetic field information at a plurality of frequencies;
separating the magnetic field information under a plurality of frequencies to obtain the magnetic field information generated by the bleeding tissue;
taking magnetic field information under multiple frequencies and magnetic field information generated by bleeding tissues as a training sample pair to form a training sample set;
constructing an initial neural network model;
and training the initial neural network model by adopting the training sample set to obtain the magnetic induction tomography imaging model.
According to the specific embodiment provided by the invention, the invention discloses the following technical effects:
the multi-frequency bidirectional magnetic induction tomography device and the method based on SAE provided by the invention have the advantages that the excitation signal is generated based on the generated sinusoidal signal, the excitation signal generates an alternating primary magnetic field in the space, the primary magnetic field acts on the biological tissue, the inside of the biological tissue generates an eddy current under the action of the primary magnetic field, and a disturbance magnetic field opposite to the primary magnetic field is generated under the action of the eddy current, so that the magnetic field information of the biological tissue can be detected and obtained, then, the detection image of the biological tissue is generated based on the magnetic field information, and the imaging accuracy is improved while the cerebral hemorrhage position positioning accuracy is improved.
Drawings
In order to more clearly illustrate the embodiments of the present invention or the technical solutions in the prior art, the drawings needed in the embodiments will be briefly described below, and it is obvious that the drawings in the following description are only some embodiments of the present invention, and it is obvious for those skilled in the art to obtain other drawings without creative efforts.
FIG. 1 is a schematic diagram of an embodiment of a multi-frequency bi-directional magnetic induction tomography apparatus based on SAE according to an embodiment of the present invention;
fig. 2 is a schematic diagram of 5 detection points under unidirectional detection with different noises according to an embodiment of the present invention; wherein, part (a) of fig. 2 is an actual schematic diagram; part (b) of fig. 2 is a schematic diagram of detecting points under 40dB noise of unidirectional detection; part (c) of fig. 2 is a schematic diagram of detecting points under 30dB noise of unidirectional detection; part (d) of fig. 2 is a schematic diagram of detecting points under 20dB noise of unidirectional detection;
fig. 3 is a schematic diagram of 10 detection points for detecting different noises in a single direction according to an embodiment of the present invention; wherein, part (a) of fig. 3 is an actual schematic diagram; part (b) of fig. 3 is a schematic diagram of detecting points under 40dB noise of unidirectional detection; part (c) of fig. 3 is a schematic diagram of detecting points under 30dB noise of unidirectional detection; part (d) of fig. 3 is a schematic diagram of detecting points under 20dB noise of unidirectional detection;
fig. 4 is a schematic diagram of 5 detection points under different noises detected in two directions according to an embodiment of the present invention; wherein, part (a) of fig. 4 is an actual schematic diagram; part (b) of fig. 4 is a schematic diagram of detection points under 40dB noise of bidirectional detection; part (c) of fig. 4 is a schematic diagram of detection points under 30dB noise of bidirectional detection; part (d) of fig. 4 is a schematic diagram of detection points under 20dB noise of bidirectional detection;
FIG. 5 is a graphical illustration of imaging results provided by an embodiment of the present invention; wherein, part (a) of fig. 5 is a schematic diagram of actual imaging; part (b) of FIG. 5 is a SAE imaging scheme;
FIG. 6 is a flow chart of a multi-frequency bi-directional magnetic induction tomography imaging method based on SAE provided by the invention;
FIG. 7 is a schematic representation of exemplary results provided by embodiments of the present invention; FIG. 7 is a schematic diagram of a real situation provided by an embodiment of the present invention; FIG. 7, part (b), is a schematic diagram of a unidirectional detection situation provided by an embodiment of the present invention; FIG. 7 (c) is a schematic diagram of a bidirectional detection situation provided by an embodiment of the present invention;
fig. 8 is a distribution diagram of the bidirectional detection coil according to the embodiment of the present invention.
Detailed Description
The technical solutions in the embodiments of the present invention will be clearly and completely described below with reference to the drawings in the embodiments of the present invention, and it is obvious that the described embodiments are only a part of the embodiments of the present invention, and not all of the embodiments. All other embodiments, which can be obtained by a person skilled in the art without making any creative effort based on the embodiments in the present invention, belong to the protection scope of the present invention.
The invention aims to provide a multi-frequency bidirectional magnetic induction tomography imaging device and method based on SAE, which can improve the accuracy of cerebral hemorrhage position positioning and the imaging accuracy.
In order to make the aforementioned objects, features and advantages of the present invention comprehensible, embodiments accompanied with figures are described in further detail below.
As shown in FIG. 1, the multi-frequency bi-directional magnetic induction tomography apparatus based on SAE provided by the invention comprises an excitation coil, a detection coil, a power amplifier, a signal generator, a lock-in amplifier and a signal acquisition card.
The signal generator generates a sinusoidal signal, the power amplifier amplifies the signal, and the amplified signal is connected into the exciting coil.
The exciting coil generates exciting signal to generate alternating primary magnetic field B in space 0 Primary magnetic field B 0 Act on the biological tissue to generate a current, i.e. an eddy current, inside the biological tissue, thereby generating a primary magnetic field B 0 The opposite disturbing magnetic field is Δ B, and different biological tissues can generate eddy currents with different magnitudes. If abnormal changes occur in the biological tissue, such as cerebral hemorrhage, the blood changes the electrical characteristics of the hemorrhage site, causing the change of the eddy current and the Δ B. The magnetic field information detected by the detection coil is B 0 +∆B。
The detection coil detects the magnetic field information outside the biological tissue, and the detection signal is accessed into the phase-locked amplifier to obtain the signal amplitude.
By changing the frequency of the excitation signal, magnetic field information at multiple frequencies is obtained. The frequency range of the signal is selected, simulation is carried out according to the acceptable error, and the frequency range is determined, wherein the frequency range selected by the method is 1M to 7.5M. Wherein the number of the selected frequencies is equal to the number of the tissue layers of the imaging body. In the frequency range, the sizes of the heterogenous body equal interval conductivity corresponding to the frequency are selected according to the size equal interval distribution of the heterogenous body single layer tissue conductivity. In actual medical examination, since most patients have cerebral hemorrhage, the magnetic field information before hemorrhage (prior information) cannot be obtained. The limitation that single frequency can not acquire prior information can be overcome by a multi-frequency signal separation mode.
And separating the obtained signals to obtain the information of the magnetic field generated by the bleeding tissue alone. The signal phase information obtained in practice not only includes phase signals generated by different tissues of the head, but also includes the phase of coupling signals between different tissues of the head. The frequency range is selected to ensure that the coupling signal has a negligible effect on the imaging result, so that the phase of the detection signal can be assumed to produce a superposition of the phases of the signals for the respective tissues. The phase of the head detection signal is a linear superposition of the phases of the signals generated by the various tissues inside the head. As shown in the formula (1), different frequencies are detected in actual imagingThe magnitude of the electrical conductivity of the next different tissue is known information. Wherein Δφ fdhead (f k ) Representing the magnetic field information, Δ, obtained for the entire head at a frequency k of the excitation signalφ i (f j ) Denotes the firstiThe monolayer tissue has a frequency ofjThe magnetic field information obtained under the excitation signal of (1).
Under the condition that the conductivity of the biological tissue is not changed, the detection coil generates a phase proportional relation under different excitation signal frequencies; the phases of the detection coils generated under different conductivities are also in a proportional relationship under the condition that the frequency of the excitation signal is not changed. The relational expression is shown in formula (2), and the following information is known in the actual imaging detection. Wherein
Is shown asnLayer organization in frequencykLower conductivity level.
Wherein, the first and the second end of the pipe are connected with each other,
is as followsnLayer organization at a frequency ofkThe resulting magnetic field information under the excitation signal of (a),
is a biological tissue nf k The electrical conductivity of the steel when it is used,
is at the same time
Electrical conductivity andf 1 magnetic field producible under conditionsAnd (4) information.
Combining equations (1) and (2) can be simplified to equation (3), wherein,
for the coefficient matrix of the known information, the right side of the equal sign in the formula (3) is the known information, and the left side of the equal sign is the solving information in parentheses.
the positions of the exciting coil and the detecting coil are moved by rotating, and the rotation is 90 degrees.
And after the rotation, the magnetic field information of the other side of the biological tissue is detected to obtain the magnetic field information of the other side.
And obtaining two-direction magnetic field information and biological tissue conductivity as deep learning training samples. The MIT model with the two-direction magnetic field information can be used for predicting and imaging the bleeding condition more accurately. As shown in fig. 2-4, it can be obtained that under the condition of different 5 detection points with different noises, the positioning of the bleeding position by the bidirectional imaging is better than the unidirectional imaging effect. When increasing to 10 detection points unidirectionally, the effect is still inferior to the bidirectional result, and thus the importance of the bidirectional to the MIT technique is seen.
And carrying out SAE deep learning training on the sample to obtain the magnetic induction tomography model.
For a patient to be detected, the detection is only needed, and then the magnetic induction tomography imaging model obtained through training can be used for imaging. As shown in fig. 5, the SAE multi-frequency and bi-directional combination mode can overcome the limitation that single-frequency prior information cannot be obtained, and can also realize the positioning of the bleeding position.
And constructing a magnetic induction tomography imaging model through finite element calculation software, carrying out analysis calculation by using the magnetic induction tomography imaging model, and setting materials according to the actual impedance. And sequentially exciting and detecting according to the selected signal frequency to obtain the magnetic field information in a single direction.
In order to improve the imaging accuracy, the magnetic field information in the other direction is detected by moving the coil. And calculating the phase difference of the two directional magnetic field information to construct a deep learning sample set. SAE deep learning training is carried out on the sample set and used for subsequent image prediction.
The phase difference in actual detection is obtained similarly to simulation, sinusoidal signals are generated through a signal generator, the sinusoidal signals are amplified after being connected to a power amplifier, and then the sinusoidal signals are connected to a coil to generate a magnetic field with larger intensity. The head of a patient is excited by magnetic fields with different frequencies, and magnetic field information in two directions is excited and detected in a mode of moving a coil. After the detection signal detects the signal, the phase difference is obtained by multi-frequency signal processing, and imaging can be performed through a deep learning prediction model.
Based on the above description, the present invention further provides a multi-frequency bi-directional magnetic induction tomography method based on SAE, which is applied to the above-provided apparatus of the present invention, as shown in fig. 6, and the method includes:
step 100: and acquiring magnetic field information of the biological tissue to be detected.
Step 101: and acquiring a magnetic induction tomography imaging model. The magnetic induction tomography model is a trained neural network model which takes magnetic field information as input and detection images as output
Step 102: and inputting the magnetic field information into a magnetic induction tomography imaging model to obtain a detection image of the biological tissue.
Before obtaining the magnetic induction tomography imaging model, the multi-frequency bidirectional magnetic induction tomography imaging method based on SAE provided by the invention further comprises the following steps:
the frequency of the excitation signal is varied to obtain magnetic field information at a plurality of frequencies.
And separating the magnetic field information under a plurality of frequencies to obtain the magnetic field information generated by the bleeding tissue.
And taking the magnetic field information under a plurality of frequencies and the magnetic field information generated by the bleeding tissue as a training sample pair to form a training sample set.
And constructing an initial neural network model.
And training the initial neural network model by adopting a training sample set to obtain a magnetic induction tomography model.
Based on the above description, the present invention also has the following advantages over the prior art:
1. in the actual detection imaging, the magnetic field information (prior information) before the cerebral hemorrhage of the patient cannot be acquired. However, the invention adopts a multi-frequency technology, so that the limitation that single frequency cannot acquire prior information is solved, and multi-frequency imaging can still be carried out under the condition of no prior information. The SAE image is a result of multi-frequency imaging, which is seen to be very close to reality. The results of the specific experiments are shown in fig. 5 (a) and 5 (b).
2. The position of the aluminum bar is positioned wrongly only by a single-direction detection mode, but the imaging accuracy can be realized by a mode of detecting two directions. The results of the specific experiments are shown in fig. 7 (a) to 7 (c).
3. In the practical application process, the adopted coils of the coil group which are arranged up and down are more sensitive to the magnetic flux density x component of the magnetic field change, and the coils of the coil group which are arranged left and right are more sensitive to the magnetic flux density y component of the magnetic field change. According to the invention, the phase difference is obtained by calculating the magnetic flux density information in two mutually perpendicular directions, and the cerebral hemorrhage position can be more accurately positioned and the imaging is more accurate by means of imaging. The specific experimental results are shown in fig. 8.
In the present specification, the embodiments are described in a progressive manner, each embodiment focuses on differences from other embodiments, and the same and similar parts among the embodiments are referred to each other. For the system disclosed by the embodiment, the description is relatively simple because the system corresponds to the method disclosed by the embodiment, and the relevant points can be referred to the method part for description.
The principles and embodiments of the present invention have been described herein using specific examples, which are provided only to help understand the method and the core concept of the present invention; meanwhile, for a person skilled in the art, according to the idea of the present invention, the specific embodiments and the application range may be changed. In view of the above, the present disclosure should not be construed as limiting the invention.
Claims (8)
1. A multi-frequency bi-directional magnetic induction tomography imaging apparatus based on SAE, comprising:
a signal generator for generating a sinusoidal signal;
the power amplifier is connected with the signal generator and is used for amplifying the sinusoidal signal;
the exciting coil is connected with the power amplifier and is used for generating an exciting signal based on the sinusoidal signal; the excitation signal generates an alternating primary magnetic field in the space, the primary magnetic field acts on biological tissues, the interior of the biological tissues generates an eddy current under the action of the primary magnetic field, and a disturbance magnetic field opposite to the primary magnetic field is generated under the action of the eddy current;
a detection coil for detecting magnetic field information of the biological tissue;
and the processor is connected with the detection coil and used for generating a detection image of the biological tissue based on the magnetic field information.
2. The SAE-based multi-frequency bi-directional magnetic induction tomography apparatus of claim 1 wherein a magnetic induction tomography model is implanted in the processor; the magnetic induction tomography model is a trained neural network model which takes magnetic field information as input and detection images as output.
3. The multi-frequency bi-directional magnetic induction tomography apparatus based on SAE as claimed in claim 1, further comprising:
and the lock-in amplifier is connected with the detection coil and the processor and is used for determining the amplitude of the signal based on the magnetic field information detected by the detection coil.
4. A multi-frequency bi-directional magnetic induction tomography apparatus based on SAE as claimed in claim 1, wherein the detecting coils generate proportional phase relationship at different excitation signal frequencies with the conductivity of the imaging body unchanged.
5. A multi-frequency bi-directional magnetic induction tomography apparatus based on SAE as claimed in claim 1, wherein in use, the positions of said excitation coil and said detection coil are moved by rotation.
6. A multi-frequency bi-directional magnetic induction tomography apparatus based on SAE as claimed in claim 5, wherein the position of the excitation coil and the position of the detection coil are both rotated 90 degrees.
7. A multi-frequency bidirectional magnetic induction tomography imaging method based on SAE is characterized by comprising the following steps:
acquiring magnetic field information of a biological tissue to be detected;
acquiring a magnetic induction tomography model; the magnetic induction tomography model is a trained neural network model taking magnetic field information as input and detection images as output
And inputting the magnetic field information into the magnetic induction tomography imaging model to obtain a detection image of the biological tissue.
8. The multi-frequency bi-directional magnetic induction tomography imaging method based on SAE as claimed in claim 7, further comprising, before acquiring the magnetic induction tomography imaging model:
changing the frequency of the excitation signal to obtain magnetic field information at a plurality of frequencies;
separating the magnetic field information under a plurality of frequencies to obtain the magnetic field information generated by the bleeding tissue;
taking magnetic field information under multiple frequencies and magnetic field information generated by bleeding tissues as a training sample pair to form a training sample set;
constructing an initial neural network model;
and training the initial neural network model by adopting the training sample set to obtain the magnetic induction tomography imaging model.
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