CN111973172B - A cardiac structure imaging system and method based on MCG and ECG fusion - Google Patents

A cardiac structure imaging system and method based on MCG and ECG fusion Download PDF

Info

Publication number
CN111973172B
CN111973172B CN202010884783.XA CN202010884783A CN111973172B CN 111973172 B CN111973172 B CN 111973172B CN 202010884783 A CN202010884783 A CN 202010884783A CN 111973172 B CN111973172 B CN 111973172B
Authority
CN
China
Prior art keywords
ecg
cardiac
heart
magnetic
module
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Active
Application number
CN202010884783.XA
Other languages
Chinese (zh)
Other versions
CN111973172A (en
Inventor
宁晓琳
安楠
曹富智
韩邦成
房建成
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Beihang University
Original Assignee
Beihang University
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Beihang University filed Critical Beihang University
Priority to CN202010884783.XA priority Critical patent/CN111973172B/en
Publication of CN111973172A publication Critical patent/CN111973172A/en
Application granted granted Critical
Publication of CN111973172B publication Critical patent/CN111973172B/en
Active legal-status Critical Current
Anticipated expiration legal-status Critical

Links

Images

Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/72—Signal processing specially adapted for physiological signals or for diagnostic purposes
    • 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
    • A61B2576/023—Medical imaging apparatus involving image processing or analysis specially adapted for a particular organ or body part for the heart

Landscapes

  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Engineering & Computer Science (AREA)
  • Pathology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Psychiatry (AREA)
  • Signal Processing (AREA)
  • Physics & Mathematics (AREA)
  • Computer Vision & Pattern Recognition (AREA)
  • Biophysics (AREA)
  • Artificial Intelligence (AREA)
  • Biomedical Technology (AREA)
  • Physiology (AREA)
  • Medical Informatics (AREA)
  • Molecular Biology (AREA)
  • Surgery (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Measurement And Recording Of Electrical Phenomena And Electrical Characteristics Of The Living Body (AREA)

Abstract

本发明涉及一种基于MCG和ECG融合的心脏结构成像系统及方法，包括：磁屏蔽房、心电测量模块、心磁测量模块、数据同步及采集模块以及结构成像模块。该系统根据同步采集到的MCG(心磁信号)以及ECG(心电信号)，第一步，由心磁信号进行逆问题求解得到心脏源活动的位置和强度；第二步，根据预设的躯干‑心脏模型结构由第一步计算的心脏源活动进行正向计算，得出各心电电极位置的理论电势；第三步，将该理论电势同ECG实际采集的信号比较，通过不断修改第二步中的心脏内各部分结构大小，多次计算直至心电电极电势的理论值与实际值的差值小于设定值，此时心脏内各部分结构即为所得到的心脏结构成像结果。

Figure 202010884783

The invention relates to a cardiac structure imaging system and method based on MCG and ECG fusion, comprising: a magnetic shielding room, an electrocardiogram measurement module, a cardiomagnetic measurement module, a data synchronization and acquisition module and a structural imaging module. The system is based on the synchronously collected MCG (cardiac magnetic signal) and ECG (electrocardiographic signal). The first step is to solve the inverse problem of the cardiac magnetic signal to obtain the position and intensity of the heart source activity; the second step, according to the preset The torso-heart model structure is forward calculated by the heart source activity calculated in the first step to obtain the theoretical potential of each ECG electrode position; in the third step, the theoretical potential is compared with the signal actually collected by the ECG, and the The size of each part of the heart in the second step is calculated multiple times until the difference between the theoretical value and the actual value of the ECG electrode potential is less than the set value. At this time, each part of the heart structure is the obtained cardiac structure imaging result.

Figure 202010884783

Description

Cardiac structure imaging system and method based on MCG and ECG fusion
Technical Field
The invention relates to a cardiac structure imaging technology in the field of structural imaging, in particular to a cardiac structure imaging system and method based on MCG and ECG fusion.
Background
Heart diseases such as cardiomyopathy, heart tumor, congenital heart disease, particularly complex deformity, valvular heart disease and the like need to be diagnosed and analyzed by means of heart imaging technology. The current cardiac imaging techniques are mainly ultrasound imaging, CT imaging and MRI imaging. The CT imaging radiation dose is high, and certain harm is caused to a human body; MRI imaging is not suitable for patients with cardiac bypass. The current Magnetocardiogram (MCG) and Electrocardiograph (ECG) measuring equipment can detect electromagnetic field information, are used for reflecting functional information of the heart, and have the characteristics of ultrahigh time resolution, no wound and quick response. Both the heart magnet and the heart electricity are electromagnetic fields generated by the source activity of the heart, namely action potential of myocardial cells, and are conducted to the surface of a human body through the human body to be recorded, the difference of the conductivity at each part of the human body is large, and the change of the permeability is small, so that the conduction of the heart electricity in the human body is greatly influenced by the conductivity, the conduction of the heart magnet is basically not influenced by the permeability, namely, the human body is transparent to the heart magnet and can be completely transmitted. Imaging of cardiac structures using MCG and ECG fused systems is possible based on the fact that there are different aberrations in the conduction of cardiac source activity to the body surface.
Therefore, the cardiac structure imaging system and method based on MCG and ECG fusion of the invention overcome the defects that CT imaging radiation is harmful to human bodies and MRI is not suitable for patients with cardiac bypass, and become a novel cardiac structure imaging technology with the characteristics of harmlessness and suitability for all people.
Disclosure of Invention
The invention solves the problems: the defects of the prior art are overcome, the cardiac structure imaging system and method based on MCG and ECG fusion are provided, the cardiac structure imaging system and method are harmless to human bodies, the defect that CT imaging radiation is harmful to human bodies is overcome, the cardiac structure imaging system is suitable for various people, the defect that MRI cannot be suitable for patients with cardiac bypass is overcome, and high time resolution is used as a supplement to the existing cardiac imaging system.
The technical scheme of the invention is as follows: a cardiac structure imaging system based on MCG and ECG fusion mainly comprises: the system comprises a magnetic shielding room, an electrocardio measuring module, an electrocardio-magnetic measuring module, a data synchronization and acquisition module and a structure imaging module. The electrocardio measuring module and the magnetocardiogram measuring module are arranged in the magnetic shielding room and are respectively used for measuring electrocardio signals and magnetocardiogram signals, the acquired signals are output to the data synchronizing and acquiring module outside the magnetic shielding room, the acquired digital signals are input to the structure imaging module, the structure imaging module receives the electrocardio signals and the magnetocardiogram signals output by the data synchronizing and acquiring module, and cardiac structure imaging is carried out on the synchronously acquired electrocardio signals and magnetocardiogram signals at each moment.
1) Magnetic shielding room
The electrocardiographic measurement and the magnetocardiogram measurement are carried out in a magnetic shielding room. Since the earth magnetic field has a 50-60 μ T magnetic field, the magnetic field of the magnetocardiogram is in the order of 1-100pT, and thus magnetocardiogram measurements need to be performed in a magnetically shielded environment. The magnetic shielding room is used for shielding the magnetic field of the earth environment and needs the remanence to be less than 10 nT.
2) Electrocardio measuring module
The electrocardio measuring module is arranged in the magnetic shielding room and comprises an electrocardio electrode and an amplifier. The connection relationship is as follows: 64 or more electrocardio-electrodes are connected to the amplifier, the electrocardiosignals collected by the electrocardio-electrodes are subjected to signal amplification by the amplifier and are output to the data synchronization and collection module outside the magnetic shielding room by the optical fiber. The array electrocardio-electrode uses silver chloride as an electrode material, the silver chloride material can not generate magnetic interference to the magnetocardiogram measuring equipment, and 64 electrodes are arranged in an 8-by-8 array. The amplifier is a nuclear magnetism compatible amplifier, and the amplifier housing is magnetically shielded, so that the circuit in the amplifier does not generate magnetic noise outside the amplifier.
3) Magnetocardiogram measuring module
The magnetocardiogram measurement module is placed in a magnetic shielding room, and the module comprises 64 or more magnetometer probes. The magnetometer probes are used for measuring the normal and tangential magnetic fields of the body surface, are arranged in an 8 x 8 array and are inserted into an insertion plate for fixing the magnetometer probes, and 8 x 8 slots are formed in the insertion plate. And the magnetocardiogram signals measured by the magnetometer probe are output to a data synchronization and acquisition module outside the magnetic shielding room.
4) Data synchronization and acquisition module
The data synchronization and acquisition module comprises a data synchronization trigger clock and a data acquisition card. The data synchronization triggering clock is used for enabling the analog signals output by the electrocardio-measuring module and the magnetocardiogram-measuring module to be collected under the same clock, the electrocardio-signals and the magnetocardiogram signals are synchronously sampled under the synchronous clock, and the sampled signals are output to the structural imaging module.
5) Structural imaging module
The structural imaging module receives the electrocardiosignals and the magnetocardiogram signals output by the data synchronization and acquisition module and images the synchronously acquired electrocardiosignals and magnetocardiogram signals at each moment. The imaging process of the structural imaging module is as follows: firstly, electrocardio signals and magnetocardiogram signals and an initial torso-heart model structure are respectively input, the electrical conductivity of the heart is 0.0537-0.483S/m, the electrical conductivity of the torso is 0.216-0.241S/m, and the electrical conductivity of the interior of the ventricle is 0.4-1.0S/m. Secondly, solving an inverse problem of 64-channel magnetocardiogram signals at a single moment to obtain the activity position and the intensity of a heart source; thirdly, because the electrical conductivity of the electrocardiosignals at different parts of the human body is different, the voltage theoretical value of each electrode position of the electrocardio is obtained by forward calculation according to the heart source activity position estimated in the first step according to a preset trunk-heart model structure; step four, comparing actual signals collected by the electrocardio forward calculation estimated theoretical value and the electrocardio device in the step three, and verifying whether the difference value between the two signals is less than a preset value; and step four, if the difference obtained in the step three is smaller than a preset value, the assumed trunk-heart model structure is considered as the final imaging structure, otherwise, the trunk-heart model is modified, and the calculation is returned to the step three. And finally obtaining the imaging result of the heart structure and outputting the imaging result to a display screen.
The cardiac structure imaging method based on MCG and ECG fusion mainly realizes the following steps:
firstly, establishing a magnetocardiogram guiding field phi by using finite elements according to an initial torso-heart conduction modelE(Vi，σi) 1, 2, n and an ecg lead field MM(Vj，μj) J 1, 2.. m, where V denotes the finite volume element, σiRepresents ViElectrical conductivity, muiRepresents VjAnd (4) magnetic permeability.
Secondly, because the magnetocardiogram permeability changes little along with the change of the tissue, the magnetocardiogram guiding field is considered to be more accurate, so that the magnetocardiogram guiding field M is obtainedM(Vj，μj) Searching a source space, solving the heart source activity, wherein the solving method is shown as the following formula:
Figure BDA0002655242010000031
wherein, YMFor magnetocardiogram array signals measured by the magnetocardiogram measuring module, SMFor the solved cardiac source activity, G is the cardiac source space, i.e., the cardiac volume. Solving the above equation to obtain SM。
Thirdly, taking a threshold value Q, and continuously updating a conduction model of the trunk-heart, namely the electrocardio-guide field phiERepeating the second step to enable the electrocardiosignals measured by the electrocardio measuring module and the theoretical voltage values phi of the positions of the electrodes of the electrocardio to be measuredESMThe difference is less than or equal to the threshold Q, as shown in the following equation:
Figure BDA0002655242010000032
wherein, YEFor the electrocardiographic signal, S, measured by the electrocardiographic measuring moduleMFor the heart source activity, phi, obtained in the last stepEIs an updated electrocardiogram guide field.
Finally, from phiE(Vi，σi) N gives the imaging results of cardiac structures, characterizing different cardiac conductivity regions in different colors.
Compared with other structural imaging systems, the cardiac structural imaging system based on MCG and ECG fusion has the advantages that:
(1) compared with the CT cardiac imaging technology, the CT radiation dose is high and harmful to the human body, and the invention can overcome the defect and has no side effect on the human body.
(2) Compared with the MRI cardiac imaging technology, MRI is not suitable for pregnant women or patients with heart bypass, and the cardiac structure imaging technology based on MCG and ECG fusion can be suitable for various people including pregnant women, children and the like.
(3) Compared with the ultrasonic cardiac imaging technology, the structural imaging technology provided by the invention can not only provide structural information, but also reflect the electrical activity and magnetic activity conditions of the heart, and analyze the source activity condition of the heart with high time resolution.
In a word, the invention firstly provides a heart structure imaging graph obtained by combining the functional magnetocardiogram and electrocardio measurement results with modeling calculation, so that the information such as heart conductivity change and the like is visually reflected, and the invention can be expanded and applied to clinic in the future.
Drawings
FIG. 1 is a system block diagram of a cardiac structure imaging system based on MCG and ECG fusion;
FIG. 2 is a schematic layout of the electrocardio-electrode and magnetocardiogram probe;
FIG. 3 is an imaging flow diagram of a structural imaging module.
In the figure: the system comprises a magnetic shielding room 1, an electrocardio measuring module 2, a magnetocardiogram measuring module 3, a data synchronization and acquisition module 4, a structure imaging module 5, an electrocardio electrode 6 and a magnetocardiogram probe 7.
Detailed Description
The present invention will be described in detail below with reference to the accompanying drawings and examples.
As shown in fig. 1, a cardiac structure imaging system based on MCG and ECG fusion is presented, which mainly comprises: the system comprises a magnetic shielding room 1, an electrocardio measuring module 2, an electrocardio-magnetic measuring module 3, a data synchronization and acquisition module 4 and a structure imaging module 5. The electrocardio measuring module 2 and the magnetocardiogram measuring module 3 are arranged in the magnetic shielding room 1 and are respectively used for measuring electrocardio signals and magnetocardiogram signals, the acquired signals are output to the data synchronization and acquisition module 4 outside the magnetic shielding room 1, and the acquired digital signals are input to the structural imaging module 5 for cardiac structural imaging.
(1) Magnetic shielding room 1
The electrocardiographic measurement and the magnetocardiogram measurement are performed in the magnetic shielding room 1. Since the earth magnetic field has a 50-60 μ T magnetic field, the magnetic field of the magnetocardiogram is in the order of 1-100pT, and thus magnetocardiogram measurements need to be performed in a magnetically shielded environment. The magnetic shielding room 1 is used for shielding the magnetic field of the earth environment and needs the remanence to be less than 10 nT.
(2) Electrocardio measuring module 2
The electrocardio measuring module 2 is arranged in the magnetic shielding room 1 and comprises an electrocardio electrode 6 and an amplifier. The connection relationship of each part in the electrocardio measuring module 2 is as follows: 64 or more electrocardio-electrodes 6 are connected to the amplifier, the electrocardiosignals collected by the electrocardio-electrodes 6 are subjected to signal amplification by the amplifier and are output to the data synchronization and collection module 4 outside the magnetic shielding room 1 by the optical fiber. The amplifier is a nuclear magnetism compatible amplifier, and the amplifier housing is magnetically shielded, so that the circuit in the amplifier does not generate magnetic noise outside the amplifier. The arrangement of the array electrocardio-electrodes is shown in figure 2, the electrode material of the electrocardio-electrodes 6 is silver chloride, the silver chloride material can not generate magnetic interference to the magnetocardiogram measuring equipment, and 64 electrodes 1 are arranged in an 8 x 8 array.
(3) Magnetocardiogram measuring module 3
The magnetocardiogram measuring module 3 is placed in the magnetic shielding room 1, and comprises 64 or more magnetocardiogram probes 7. The magnetocardiometer probes 7 are used for measuring the magnetic field in the normal direction and the tangential direction of the body surface, are arranged in an 8 x 8 array, are inserted into an insertion plate for fixing the magnetocardiometer probes, are provided with 8 x 8 insertion slots, and are arranged as shown in fig. 2. The magnetocardiogram signals measured by the magnetocardiogram probe 7 are output to the data synchronization and acquisition module 4 outside the magnetic shielding room 1.
(4) Data synchronization and acquisition module 4
The data synchronization and acquisition module 4 comprises a data synchronization trigger clock and a data acquisition card. The data synchronization trigger clock is used for enabling the analog signals output by the electrocardio-measuring module 2 and the magnetocardiogram-measuring module 3 to be collected under the same clock, under the synchronous clock, the electrocardio signals and the magnetocardiogram signals are synchronously sampled, and the sampled signals are output to the structural imaging module 5.
(5) Structural imaging module 5
The structural imaging module 5 receives the electrocardio signals and the magnetocardiogram signals output by the data synchronization and acquisition module 4, and images the synchronously acquired electrocardio signals and magnetocardiogram signals at each moment. The imaging process of the structural imaging module is as follows:
firstly, respectively inputting electrocardio signals, magnetocardiogram signals and initial bodyThe dry-heart model structure is characterized in that the electrical conductivity of the heart is 0.0537-0.483S/m, the electrical conductivity of the trunk is 0.216-0.241S/m, and the electrical conductivity of the interior of the ventricle is 0.4-1.0S/m. Respectively adopting finite elements to establish a magnetocardiogram guiding field phi according to an initial torso-heart conduction modelE(Vi，σi) 1, 2, n and an ecg lead field MM(Vj，μj) J 1, 2.. m, where V denotes the finite volume element, σiRepresents ViElectrical conductivity, muiRepresents VjAnd (4) magnetic permeability.
And secondly, solving an inverse problem of the 64-channel magnetocardiogram signal at a single moment to obtain the activity position and the intensity of the heart source. Because the magnetocardiogram permeability changes little along with the change of the tissue, the magnetocardiogram guiding field is considered to be more accurate, so the magnetocardiogram guiding field M is based onM(Vj，μj) Searching a source space, and solving the heart source activity, wherein the solving method is shown as the following formula:
Figure BDA0002655242010000051
wherein, YMMagnetocardiogram array signals, M, measured for a magnetocardiogram measuring moduleMSimplified writing method for creating a magnetocardiogram guide field, SMFor the heart source activity to be solved, G is heart source space, and the heart source activity S is obtained by solving the above formulaM。
Thirdly, because the electrical conductivity of the electrocardiosignals at different parts of the human body is different, the theoretical voltage value phi of each electrode position of the electrocardio is obtained by forward calculation according to the preset torso-heart model structure from the heart source activity position estimated in the first stepESM。
And fourthly, comparing the voltage theoretical value of each electrode position obtained by the electrocardio forward calculation in the third step with the actual signal collected by the electrocardio device, and verifying whether the difference value between the two values is less than or equal to a preset value. Taking a threshold value Q, and continuously updating a conduction model of the trunk-heart, namely the electrocardiogram guide field phiERepeating the third step such that the following holds:
Figure BDA0002655242010000052
wherein, YEFor the electrocardiographic signal, S, measured by the electrocardiographic measuring moduleMFor the heart source activity, phi, obtained in the last stepEIs an updated electrocardiogram guide field.
Fifthly, if the difference obtained in the fourth step is smaller than a preset value, the assumed trunk-heart model structure is considered as a final imaging structure; otherwise, the body-heart structure model is modified, and the third step of calculation is returned. After iteration of calculation, finally the value is calculated by phiE(Vi，σi) N gives the imaging results of the cardiac structure, and different cardiac conductivity regions are characterized in different colors and output to a display screen.
Those skilled in the art will appreciate that the invention may be practiced without these specific details.

Claims (4)

1.一种基于MCG和ECG融合的心脏结构成像系统，其特征在于，所述系统包括：磁屏蔽房、心电测量模块、心磁测量模块、数据同步及采集模块及结构成像模块；心电测量模块和心磁测量模块置于磁屏蔽房内，分别用于测量心电和心磁信号，采集到的信号输出到磁屏蔽房外的数据同步及采集模块，经采集得到的数字信号输入至结构成像模块，结构成像模块接收数据同步及采集模块输出的心电信号和心磁信号，对同步采集到的心电和心磁信号的每一时刻进行心脏结构成像；1. a cardiac structure imaging system based on MCG and ECG fusion, is characterized in that, described system comprises: magnetic shielding room, electrocardiogram measurement module, cardiomagnetic measurement module, data synchronization and acquisition module and structural imaging module; The measurement module and the cardiomagnetic measurement module are placed in the magnetic shielding room and are used to measure the ECG and cardiomagnetic signals respectively. The collected signals are output to the data synchronization and acquisition module outside the magnetically shielded room, and the collected digital signals are input to the Structural imaging module, the structural imaging module receives the ECG signal and the cardiac magnetic signal output by the data synchronization and acquisition module, and performs cardiac structure imaging at each moment of the synchronously collected ECG and cardiac magnetic signal; 所述心电测量模块包括心电电极和放大器，64个或更多个数的心电电极连接到放大器上，心电电极采集到的心电信号经放大器进行信号放大，由光纤输出到磁屏蔽房外的数据同步及采集模块；阵列式心电电极的电极材料使用氯化银材料，64个电极呈8*8阵列摆放；放大器采用能与核磁兼容的放大器，放大器外壳进行磁屏蔽处理，使得放大器内电路不会在放大器外部产生磁噪声；The ECG measurement module includes ECG electrodes and an amplifier, 64 or more ECG electrodes are connected to the amplifier, the ECG signals collected by the ECG electrodes are amplified by the amplifier, and output to the magnetic shield by the optical fiber. The data synchronization and acquisition module outside the room; the electrode material of the array ECG electrode is made of silver chloride material, and the 64 electrodes are arranged in an 8*8 array; the amplifier adopts an amplifier that is compatible with nuclear magnetic resonance, and the amplifier shell is magnetically shielded. So that the circuit inside the amplifier will not generate magnetic noise outside the amplifier; 所述结构成像模块的成像过程如下：The imaging process of the structural imaging module is as follows: 第一步，分别输入心电信号和心磁信号，以及初始的躯干-心脏模型结构；The first step is to input the ECG signal and the cardiac magnetic signal, as well as the initial torso-heart model structure; 第二步，对单一时刻的多通道心磁信号进行逆问题求解，得到心脏源活动位置及强度；The second step is to solve the inverse problem of the multi-channel magnetic heart signal at a single moment to obtain the active position and intensity of the heart source; 第三步，根据预设的躯干-心脏模型结构由第二步中估计出的心脏源活动位置正向计算得到心电各电极位置的电势理论值；In the third step, according to the preset torso-heart model structure, the electric potential value of each electrode position of the ECG is obtained by forward calculation from the active position of the heart source estimated in the second step; 第四步，将第三步中所述的电势理论值与心电设备采集到的实际信号比较，验证两者之间的差值是否小于预设值；The fourth step is to compare the theoretical potential value described in the third step with the actual signal collected by the ECG device to verify whether the difference between the two is less than the preset value; 第五步，若得到的差值小于预设值，则认为所设的躯干-心脏模型结构即为最终的成像结构；否则，修改躯干—心脏结构模型，返回第三步重新计算，直到满足差值小于预设值，此时得到心脏结构成像结果，并输出到显示屏上。In the fifth step, if the obtained difference is less than the preset value, it is considered that the set torso-heart model structure is the final imaging structure; otherwise, modify the torso-heart structure model, and return to the third step to recalculate until the difference is satisfied If the value is smaller than the preset value, the imaging result of the cardiac structure is obtained and output to the display screen. 2.根据权利要求1所述的基于MCG和ECG融合的心脏结构成像系统，其特征在于：所述的心磁测量模块包括64个或更多个数的磁强计探头，磁强计探头用于测量体表法向和切向的心脏磁场，呈8*8阵列摆放，插入用于固定该磁强计探头的插板上，插板上有8*8个插槽。2. The cardiac structure imaging system based on MCG and ECG fusion according to claim 1, is characterized in that: described magnetometry module comprises 64 or more number of magnetometer probes, and the magnetometer probe is used for It is used to measure the normal and tangential cardiac magnetic fields of the body surface. It is placed in an 8*8 array and inserted into the board used to fix the magnetometer probe. There are 8*8 slots on the board. 3.根据权利要求1所述的基于MCG和ECG融合的心脏结构成像系统，其特征在于：所述数据同步及采集模块包括数据同步触发时钟和数据采集卡，数据同步触发时钟用于使心电测量模块和心磁测量模块输出的模拟信号在同一时钟下采集，在同步时钟下，心电信号和心磁信号被同步采样，采样后的信号输出到结构成像模块。3. the cardiac structure imaging system based on MCG and ECG fusion according to claim 1, is characterized in that: described data synchronization and acquisition module comprise data synchronization trigger clock and data acquisition card, and data synchronization trigger clock is used to make ECG The analog signals output by the measurement module and the magneto-cardiac measurement module are collected under the same clock. Under the synchronous clock, the ECG signal and the cardio-magnetic signal are sampled synchronously, and the sampled signal is output to the structural imaging module. 4.一种基于MCG和ECG融合的心脏结构成像方法，其特征在于，实现为：4. a cardiac structure imaging method based on MCG and ECG fusion, is characterized in that, is realized as: 第一步，根据初始的躯干-心脏的传导模型，分别采用有限元建立心电引导场ΦE(Vi，σi)，和心磁引导场MM(Vj，μj)，i＝1，2，...，n，j＝1，2，...，m，V表示有限体积元，σi表示Vi处电导率，μi表示Vj处磁导率；In the first step, according to the initial trunk-heart conduction model, the ECG guidance field Φ E (V i , σ i ) and the cardiac magnetic guidance field M M (V j , μ j ) are established by finite element, i= 1 , 2 , . 第二步，根据心磁引导场MM(Vj，μj)搜索源空间，得到心脏源活动，求解方法如下式所示：The second step is to search the source space according to the magnetic guidance field M M (V j , μ j ) to obtain the cardiac source activity. The solution method is as follows:
Figure FDA0003224281310000021
Figure FDA0003224281310000021
 其中，YM为心磁测量模块测量得到的心磁阵列信号，MM为建立的心磁引导场简化写法，SM为求解的心脏源活动，G为心脏源空间，求解上式得到心脏源活动SM；Among them, Y M is the magnetic field array signal measured by the magnetic field measurement module, M M is the simplified writing method of the established magnetic field guidance field, S M is the calculated cardiac source activity, G is the cardiac source space, and the cardiac source is obtained by solving the above formula activity S M ; 第三步，取阈值Q，不断更新躯干-心脏的传导模型即心电引导场ΦE，重复第二步，使得心电测量模块测量的心电信号与心电各电极位置的电势理论值ΦESM差值小于等于阈值Q，如下式所示：The third step is to take the threshold Q, and continuously update the conduction model of the trunk-heart, that is, the ECG guide field Φ E , and repeat the second step, so that the ECG signal measured by the ECG measurement module and the potential theoretical value Φ of each electrode position of the ECG The difference between E S M is less than or equal to the threshold Q, as shown in the following formula:
Figure FDA0003224281310000022
Figure FDA0003224281310000022
 其中，YE为心电测量模块测量得到的心电信号，SM为上一步求解得到的心脏源活动，ΦE为更新的心电引导场；Among them, Y E is the ECG signal measured by the ECG measurement module, SM is the heart source activity obtained by the previous step, and Φ E is the updated ECG guidance field; 最终，由ΦE(Vi，σi)给出心脏结构成像结果，以不同颜色表征不同心脏电导率区域。Finally, the cardiac structure imaging results are given by Φ E (V i , σ i ), which characterize different cardiac conductivity regions with different colors.
CN202010884783.XA 2020-08-28 2020-08-28 A cardiac structure imaging system and method based on MCG and ECG fusion Active CN111973172B (en)

Priority Applications (1)

Application Number Priority Date Filing Date Title
CN202010884783.XA CN111973172B (en) 2020-08-28 2020-08-28 A cardiac structure imaging system and method based on MCG and ECG fusion

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
CN202010884783.XA CN111973172B (en) 2020-08-28 2020-08-28 A cardiac structure imaging system and method based on MCG and ECG fusion

Publications (2)

Publication Number Publication Date
CN111973172A CN111973172A (en) 2020-11-24
CN111973172B true CN111973172B (en) 2021-10-08

Family

ID=73440091

Family Applications (1)

Application Number Title Priority Date Filing Date
CN202010884783.XA Active CN111973172B (en) 2020-08-28 2020-08-28 A cardiac structure imaging system and method based on MCG and ECG fusion

Country Status (1)

Country Link
CN (1) CN111973172B (en)

Cited By (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US12178580B2 (en) 2019-12-23 2024-12-31 Alimetry Limited Electrode patch and connection system

Families Citing this family (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN112842342B (en) * 2021-01-25 2022-03-29 北京航空航天大学 A Classification Method of Cardiac Electromagnetic Signals Combining Hilbert Curve and Ensemble Learning
CN112932492B (en) * 2021-01-29 2022-08-05 上海跃磁生物科技有限公司 Method, system, medium, and apparatus for synchronizing a plurality of scan data of a magnetocardiograph
CN112842343B (en) * 2021-02-01 2022-02-22 北京航空航天大学 Method for estimating position of magnetocardiogram three-dimensional source based on SERF atomic magnetometer
CN113662549B (en) * 2021-08-23 2022-08-05 北京航空航天大学 An automatic early warning and protection system for a cardiac magnetic measurement device
CN114287943B (en) * 2021-12-01 2023-07-14 北京航空航天大学杭州创新研究院 A three-dimensional imaging method based on a wearable three-dimensional cardiomagnetic measurement device
CN115844360B (en) * 2022-11-03 2024-08-27 北京原力辰超导技术有限公司 Open magnetic resonance heart magnetic detection equipment

Citations (14)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2000210288A (en) * 1999-01-25 2000-08-02 Aloka Co Ltd Ultrasonic diagnostic apparatus
CN1744927A (en) * 2003-01-27 2006-03-08 电脑医师美国公司 Online source reconstruction for EEG/MEG and ECG/MCG
CN101564294A (en) * 2009-06-01 2009-10-28 中国人民解放军第四军医大学 Method for structural information fused electrical impedance tomography
JP4495803B2 (en) * 1999-08-30 2010-07-07 株式会社東芝 Intracardiac electrical phenomenon diagnostic device
CN104068845A (en) * 2014-03-06 2014-10-01 武汉培威医学科技有限公司 Electrocardio ultrasonic signal fusion computed tomography imaging system and method
CN104334078A (en) * 2012-05-24 2015-02-04 皇家飞利浦有限公司 Reduction of MRI interference from the electrocardiogram using lead information
CN107137107A (en) * 2017-05-09 2017-09-08 上海联影医疗科技有限公司 Multi-modality medical image acquisition methods and multi-modality medical image imaging system
CN107753012A (en) * 2016-08-19 2018-03-06 中国科学院上海微系统与信息技术研究所 A kind of mcg-signalses method for evaluating quality, system and server
JP2018166856A (en) * 2017-03-30 2018-11-01 株式会社日立ハイテクノロジーズ Magnetic field data processing system
CN109700463A (en) * 2019-03-12 2019-05-03 四川大学 A kind of magneticencephalogram epileptic spike recognition methods and system
CN110621221A (en) * 2017-11-29 2019-12-27 克里沃医疗技术有限公司 Sensor configuration in a magnetometer for medical use
CN110755076A (en) * 2019-11-01 2020-02-07 上海联影医疗科技有限公司 Image acquisition method, device, equipment and medium of magnetic resonance scanner
CN110996776A (en) * 2017-08-01 2020-04-10 导管精密有限公司 Methods for Cardiac Mapping and Model Merging
CN111000549A (en) * 2019-12-30 2020-04-14 扬州大学 Magnetocardiogram measuring system

Family Cites Families (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US8230858B2 (en) * 2008-04-01 2012-07-31 General Electric Company Controlling the operation of a respiratory gas monitor

Patent Citations (14)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2000210288A (en) * 1999-01-25 2000-08-02 Aloka Co Ltd Ultrasonic diagnostic apparatus
JP4495803B2 (en) * 1999-08-30 2010-07-07 株式会社東芝 Intracardiac electrical phenomenon diagnostic device
CN1744927A (en) * 2003-01-27 2006-03-08 电脑医师美国公司 Online source reconstruction for EEG/MEG and ECG/MCG
CN101564294A (en) * 2009-06-01 2009-10-28 中国人民解放军第四军医大学 Method for structural information fused electrical impedance tomography
CN104334078A (en) * 2012-05-24 2015-02-04 皇家飞利浦有限公司 Reduction of MRI interference from the electrocardiogram using lead information
CN104068845A (en) * 2014-03-06 2014-10-01 武汉培威医学科技有限公司 Electrocardio ultrasonic signal fusion computed tomography imaging system and method
CN107753012A (en) * 2016-08-19 2018-03-06 中国科学院上海微系统与信息技术研究所 A kind of mcg-signalses method for evaluating quality, system and server
JP2018166856A (en) * 2017-03-30 2018-11-01 株式会社日立ハイテクノロジーズ Magnetic field data processing system
CN107137107A (en) * 2017-05-09 2017-09-08 上海联影医疗科技有限公司 Multi-modality medical image acquisition methods and multi-modality medical image imaging system
CN110996776A (en) * 2017-08-01 2020-04-10 导管精密有限公司 Methods for Cardiac Mapping and Model Merging
CN110621221A (en) * 2017-11-29 2019-12-27 克里沃医疗技术有限公司 Sensor configuration in a magnetometer for medical use
CN109700463A (en) * 2019-03-12 2019-05-03 四川大学 A kind of magneticencephalogram epileptic spike recognition methods and system
CN110755076A (en) * 2019-11-01 2020-02-07 上海联影医疗科技有限公司 Image acquisition method, device, equipment and medium of magnetic resonance scanner
CN111000549A (en) * 2019-12-30 2020-04-14 扬州大学 Magnetocardiogram measuring system

Non-Patent Citations (1)

* Cited by examiner, † Cited by third party
Title
浅谈心脏磁场的检测及心脏源模型建模;石明伟等;《高科技产品研发》;20180430;44-45 *

Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US12178580B2 (en) 2019-12-23 2024-12-31 Alimetry Limited Electrode patch and connection system
US12245862B2 (en) 2019-12-23 2025-03-11 Alimetry Limited Electrode patch and connection system

Also Published As

Publication number Publication date
CN111973172A (en) 2020-11-24

Similar Documents

Publication Publication Date Title
CN111973172B (en) A cardiac structure imaging system and method based on MCG and ECG fusion
JP2012179352A (en) System and method for constructing current dipole
US8838225B2 (en) Analysis of multi-channel measurement data using orthogonal virtual channels
US9125581B2 (en) Continuous modeling for dipole localization from 2D MCG images with unknown depth
WO1994028789A1 (en) Apparatus and process for determining the sources of biomagnetic activity
WO2020199367A1 (en) Electrical impedance tomography apparatus and method
CN112842343A (en) Method for estimating position of magnetocardiogram three-dimensional source based on SERF atomic magnetometer
US7400984B2 (en) Biomagnetic measurement apparatus
CN114287943A (en) A three-dimensional imaging method based on a wearable magnetic three-dimensional measurement device
CN113520399A (en) A Heart Magnetic Field Simulation System Based on Helmholtz Coil Arrays
Hu et al. Solving the magnetocardiography forward problem in a realistic three-dimensional heart-torso model
CN104825133B (en) The quasistatic ventricular heart magnetic field model being imaged based on color Doppler 3D
Hlavin et al. An experimental determination of a multipole representation of a turtle heart
CN117017300A (en) Cardiac source positioning method integrating magnetocardiogram and electrocardiograph
JPH10305019A (en) Biomagnetic field measurement method and biomagnetic field measurement device
WIKSWO JR NON-INVASIVE MAGNETIC MEASUREMENT OF THE ELECTRICAL AND MECHANICAL ACTIVITY OF THE HEART.
Bommel et al. Boundary element solution of biomagnetic problems
Pyo et al. Identification of current density distribution in electrically conducting subject with anisotropic conductivity distribution
Irimia et al. Theoretical and computational methods for the noninvasive detection of gastric electrical source coupling
CN118697353B (en) Method, system, medium and electronic equipment for apex calibration based on magnetocardiogram
Eichler et al. Reconstruction of stomach geometry using magnetic source localization
Acar et al. Neuroelectromagnetic forward modeling toolbox
JP2001087237A (en) Living body magnetic field measuring method
Bing et al. Sparse Representation for Cardiac Electrical Activity Imaging in Magnetocardiography
Cruttenden Artifact Reduction in the Integration of Neural Electrodes and Extracellular Recording with Ultrahigh Field Magnetic Resonance Imaging

Legal Events

Date Code Title Description
PB01 Publication
PB01 Publication
SE01 Entry into force of request for substantive examination
SE01 Entry into force of request for substantive examination
GR01 Patent grant
GR01 Patent grant