CN106343999A - Magnetocardiography, compensation and optimization method based on same, system and server - Google Patents

Magnetocardiography, compensation and optimization method based on same, system and server Download PDF

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CN106343999A
CN106343999A CN201610882918.2A CN201610882918A CN106343999A CN 106343999 A CN106343999 A CN 106343999A CN 201610882918 A CN201610882918 A CN 201610882918A CN 106343999 A CN106343999 A CN 106343999A
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compensation
field signal
signal
gaussmeter
layer
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CN106343999B (en
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孔祥燕
杨康
鲁丽
陈威
谢晓明
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Shanghai Institute of Microsystem and Information Technology of CAS
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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
    • A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
    • A61B5/242—Detecting biomagnetic fields, e.g. magnetic fields produced by bioelectric currents
    • A61B5/243—Detecting biomagnetic fields, e.g. magnetic fields produced by bioelectric currents specially adapted for magnetocardiographic [MCG] signals
    • 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
    • A61B5/7203—Signal processing specially adapted for physiological signals or for diagnostic purposes for noise prevention, reduction or removal
    • 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
    • A61B5/7225—Details of analog processing, e.g. isolation amplifier, gain or sensitivity adjustment, filtering, baseline or drift compensation
    • 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
    • A61B5/7235—Details of waveform analysis
    • 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
    • A61B5/7235—Details of waveform analysis
    • A61B5/7253—Details of waveform analysis characterised by using transforms
    • A61B5/7257—Details of waveform analysis characterised by using transforms using Fourier transforms

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Abstract

The invention provides a magnetocardiography, a compensation and optimization method based on the same, a system and a server. The compensation and optimization method comprises the following steps that second magnetic field signals produced by magnetometers on a super-conducing quantum interference device array layer are compensated by utilizing first magnetic field signals produced by compensation magnetometers on a compensation layer in a preset compensation mode to form third magnetic field signals after compensation; evaluation parameters of third magnetic field signals after compensation are calculated, the third magnetic field signals are evaluated according to comprehensive evaluations of evaluation parameters to optimize the compensation layer and determine the best compensation channel on the compensation layer. The residual magnetic field in a shielded room environment is effectively inhibited, so that 36 SQUID magnetocardiogram signals having high signal-to-noise ratio and high fidelity are output in a column mode.

Description

Magnetocardiograph, the compensation optimizing method based on it, system and server
Technical field
The invention belongs to biomedical signal analysis field, more particularly to a kind of magnetocardiograph, based on its compensation optimizing method, System and server.
Background technology
Magnetocardiograph is the Weak magentic-field producing in a kind of detection cardiac electrophysiology active procedure and is applied to clinical medicine The armarium of diagnosis, the special benefits such as sensitivity is high, complete noinvasive, completely passive, noncontact that it has, the heart can be accurately positioned Dirty dysfunction, has good clinical diagnosises potentiality.
The Typical strengths of mcg-signalses are tens of pt (10-12T), and environment field noise is very strong, the such as allusion quotation in magnetic field of the earth Type intensity is 30～50 μ t, and urban environment noise has reached hundreds of nt.The extremely faint heart is extracted from powerful background magnetic field Magnetic signal depends on two aspects: (1) highly sensitive Magnetic Sensor, for detecting faint mcg-signalses；(2) noise suppressed skill Art, for suppressing background noise.At present, the Magnetic Sensor that magnetocardiograph main flow adopts is superconducting quantum interference device (squid), It has very high magnetic field sensitivity, typically has 3～5ft/hz.In terms of suppression noise, conventional has shielding techniques, ladder Degree meter technology, Digital Signal Processing etc..Wherein, shielding techniques are using in the metallic shield environment field of high conductivity Low-frequency component in the metallic shield environment field of radio-frequency component and high magnetic permeability, also remains certain low frequency ring in general screened room Border field, must coordinate gradiometer technology, environment could be reached with good inhibition.
Successfully developed the unshielded magnetocardiograph of 4 passages at present, its in unshielded environment, using 4 second order gradients It is counted as detection channels and one group of three axis magnetometer as compensating the detection that passage to complete to mcg-signalses and environment, then pass through Certain data processing and imaging technique, can obtain having much the medical image of value.But, 4 passage heart magnetic systems are due to depositing Gathering, signalling channel is few, need Multipoint movable to sweep, single patient's heart magnetic acquisition time length, imaging data are real-time, Yi Shouhuan , there are some problems in practical application with promoting in the limitation such as border interference.
In order to obtain high-quality mcg-signalses, reduce the useful signal loss causing because of signal processing, need to use Screened room technology suppresses to environmental magnetic field；Meanwhile, in order to obtain synchronous mcg-signalses, improve signal acquisition rate, lead to more Road magnetocardiograph becomes inevitable choice.For this reason, have developed 36 passage magnetocardiograph systems, the employing squid magnetic strength of this system again It is counted as signal detection passage, and be operated in shielding room environmental.But in magnetic shield room environment, also deposit due in applied environment In certain low-frequency fluctuation, lead to 36 passage magnetocardiograph system output signal-to-noise ratios relatively low, the high mcg-signalses of the distortion factor.
Therefore, a kind of magnetocardiograph, the compensation optimizing method based on it, system and server how are provided with, to solve In prior art, 36 passage magnetocardiograph cannot suppress to shield the remnant field in room environmental, leads to output signal-to-noise ratio relatively low, loses The defects such as the mcg-signalses of Zhen Dugao, have become practitioner in the art's technical problem urgently to be resolved hurrily in fact.
Content of the invention
The shortcoming of prior art in view of the above, it is an object of the invention to provide a kind of magnetocardiograph, based on its Compensation optimizing method, system and server, cannot suppress to shield room environmental for solving 36 passage magnetocardiograph in prior art In remnant field, lead to output signal-to-noise ratio relatively low, the problem of the high mcg-signalses of the distortion factor.
For achieving the above object and other related purposes, one aspect of the present invention provides a kind of magnetocardiograph, described magnetocardiogram Instrument includes: layer of compensation, is arranged above the superconducting quantum interference device array layer of described magnetocardiograph；Arrange on described layer of compensation There is at least one in order to the compensation gaussmeter compensating the field signal that described superconducting quantum interference device array layer produces.
In one embodiment of the invention, described layer of compensation is arranged above described superconducting quantum interference device array layer At predeterminable range；And on described layer of compensation setting the gaussmeter one compensating in gaussmeter and superconducting quantum interference device array layer One is corresponding.
In one embodiment of the invention, described compensation gaussmeter is fixed to described layer of compensation, described compensation by contact pin Layer is arranged on the printed circuit board (PCB) being electrically connected with the main body of described magnetocardiograph；Described magnetocardiograph need to be applied in magnetic shield In environment.
Another aspect of the present invention provides a kind of compensation optimizing method based on magnetocardiograph, and described compensation optimizing method includes Following steps: utilize the first field signal compensating gaussmeter generation on described layer of compensation to compensate institute by predesigned compensation mode State the second field signal that on superconducting quantum interference device array layer, each gaussmeter produces, to form the 3rd magnetic field after compensation Signal；Calculate the assessment parameter of the 3rd field signal after compensating, and described 3rd magnetic is assessed according to described assessment parametric synthesis Field signal, to optimize described layer of compensation, determines the optimal compensation passage thereon.
In one embodiment of the invention, described predesigned compensation mode is: the compensation gaussmeter on layer of compensation is produced First field signal is multiplied by a coefficient matrix, then deducts each gaussmeter on described superconducting quantum interference device array layer and produces The second field signal, get output difference；Count the quadratic sum of this output difference, obtain a least square and corresponding coefficient square Battle array；The second field signal that on described superconducting quantum interference device array layer, each gaussmeter produces deducts least square and correspondence Coefficient matrix and described layer of compensation on the product compensating the first field signal that gaussmeter produces, obtain the 3rd after compensating Field signal.
In one embodiment of the invention, described assessment parameter includes: the 3rd field signal and after compensation is in order to generation Time domain correlation coefficient for the pumping signal of mcg-signalses and frequency domain correlation coefficient；The characteristic wave of the 3rd field signal after compensation Crest value is than the standard deviation with the characteristic wave crest value ratio of described pumping signal；And/or the 3rd field signal after compensating The distortion grade of isomagnetic chart.
In one embodiment of the invention, described pumping signal is produced by a circular excitation coil, described circle excitation line Circle is located at the Dewar bottom part down in described magnetocardiograph；Described circle excitation coil is loading by connected mcg-signalses After the mcg-signalses of emitter transmitting, produce described pumping signal；The size of the magnetic field intensity of described pumping signal according to Biot- Safa law calculates；Described Biot's Safa law is:Wherein, μ0Represent permeability of vacuum, μ0=4 × 10-7t·m/a；R represents the radius of circular excitation coil；X represents that described Superconducting Quantum is done Relate to the abscissa of each gaussmeter and circular excitation coil distance on device array layer；Y represents described superconducting quantum interference device The vertical coordinate of the abscissa of each gaussmeter and circular excitation coil distance on array layer；H is that circular excitation coil is super with described Lead the vertical dimension of quantum interference device array layer；I is the size of current through described circle excitation coil.
In one embodiment of the invention, the 3rd field signal and after described compensation is in order to replace swashing of mcg-signalses The calculating process of the time domain correlation coefficient and frequency domain correlation coefficient of encouraging signal includes: to the 3rd field signal after the compensation obtaining Carry out 50hz bandreject filtering and 100hz low-pass filtering treatment, form the 3rd field signal after processed compensation；According to preset phase Closing property calculation, calculates the time domain correlation coefficient of the 3rd field signal after processed compensation and described pumping signal；Simultaneously The 3rd field signal after processed compensation and described pumping signal are carried out Fourier transformation, according to described preset dependency meter Calculation mode, calculates the frequency domain correlation coefficient of the 3rd field signal after processed compensation and described pumping signal.
In one embodiment of the invention, the characteristic wave crest value of the 3rd field signal after described compensation swashs than with described The calculating process encouraging the standard deviation of characteristic wave crest value ratio of signal includes: the 3rd field signal after the processed compensation of identification In characteristic wave；The crest value of statistical nature ripple, and the crest value according to characteristic wave, calculate the 3rd magnetic field after processed compensation The peak ratio of the characteristic wave in signal；Calculate processed compensate after the 3rd field signal in the peak ratio of characteristic wave with Standard deviation between the peak ratio of the characteristic wave in pumping signal.
Another aspect of the invention provides a kind of compensation optimizing system based on described magnetocardiograph, described compensation optimizing system System includes: compensating module, for utilizing the first magnetic compensating gaussmeter generation on described layer of compensation by predesigned compensation mode Field signal compensates the second field signal that on described superconducting quantum interference device array layer, each gaussmeter produces, to form compensation The 3rd field signal afterwards；Optimization module, for calculating the assessment parameter of the 3rd field signal after compensating, and according to institute's commentary Estimate parametric synthesis and assess described 3rd field signal, to optimize described layer of compensation, determine the optimal compensation passage thereon.
On the one hand the present invention finally provides a kind of server, including described based on described magnetocardiograph compensation optimizing system System.
As described above, the magnetocardiograph of the present invention, the compensation optimizing method based on it, system and server, have following Beneficial effect:
In magnetocardiograph of the present invention, the compensation optimizing method based on it, system and server by utilizing magnetocardiograph Compensation configuration, the effectively remnant field in suppression shielding room environmental, make 36 squid signal permutations output high s/n ratios, height The mcg-signalses of fidelity.
Brief description
Fig. 1 is shown as the magnetocardiograph of the present invention axonometric chart in an embodiment.
Fig. 2 is shown as the compensation optimizing method based on magnetocardiograph of the present invention schematic flow sheet in an embodiment.
Fig. 3 is shown as the dependency diagram compensating the 3rd field signal and pumping signal after channel compensation of the present invention.
Fig. 4 is shown as the compensation gaussmeter 111b of the present invention, and the qrst crest value of 111g, 111j compares schematic diagram.
Fig. 5 is shown as the compensation optimizing system based on magnetocardiograph of the present invention theory structure in an embodiment and illustrates Figure.
Fig. 6 is shown as the server of the present invention theory structure schematic diagram in an embodiment.
Component label instructions
1 magnetocardiograph/36 passage magnetocardiograph
11 layers of compensation
111 compensation gaussmeters
111a, compensates gaussmeter
111b,
111c,
111d,
111e,
111f,
111g,
111h,
111i,
111j,
111k,
111l
12 superconducting quantum interference device array layers
121 gaussmeters
The 2 compensation optimizing systems based on magnetocardiograph
21 compensating modules
22 optimization modules
3 servers
S1～s2 step
Specific embodiment
Below by way of specific instantiation, embodiments of the present invention are described, those skilled in the art can be by this specification Disclosed content understands other advantages and effect of the present invention easily.The present invention can also be by addition different concrete realities The mode of applying is carried out or applies, and the every details in this specification can also be based on different viewpoints and application, without departing from Carry out various modifications and changes under the spirit of the present invention.It should be noted that, in the case of not conflicting, following examples and enforcement Feature in example can be mutually combined.
It should be noted that the diagram provided in following examples only illustrates the basic structure of the present invention in a schematic way Think, then only show the assembly relevant with the present invention in schema rather than according to component count during actual enforcement, shape and size Draw, during its actual enforcement, the kenel of each assembly, quantity and ratio can be a kind of random change, and its assembly layout kenel It is likely more complexity.
Embodiment one
The present embodiment provides a kind of magnetocardiograph, and described magnetocardiograph includes:
Layer of compensation, is arranged above the superconducting quantum interference device array layer of described magnetocardiograph；
It is provided with least one in order to compensate the magnetic that described superconducting quantum interference device array layer produces on described layer of compensation The compensation gaussmeter of field signal.
Magnetocardiograph the present embodiment being provided below with reference to diagram is described in detail.Refer to Fig. 1, be shown as Axonometric chart in an embodiment for the magnetocardiograph.As shown in figure 1, the magnetocardiograph described in the present embodiment is 36 passage magnetocardiograph 1.Described 36 passage magnetocardiograph 1 include layer of compensation 11.
Described layer of compensation 11 is arranged above the superconducting quantum interference device array layer of described magnetocardiograph, specifically, The superconducting quantum interference device array layer of described magnetocardiograph, i.e. 36 superconducting quantum interference device battle arrays of 36 passage magnetocardiograph 1 At predeterminable range above row layer, this predeterminable range is can be arranged according to environment and signal characteristic in actual applications, Yu Ben In embodiment, predeterminable range is set at 50mm.And it is described super in order to compensate to be provided with least one on described layer of compensation 11 Lead quantum interference device array layer generation field signal compensation gaussmeter (compensate gaussmeter processing technology, overall package, Pin setting aspect is all identical with the gaussmeter of 36squid array layer, to improving the compatibility of system reading circuit, but is While compensated array layer, do not affect the quality of mcg-signalses, the compensation gaussmeter of layer of compensation reduces when designing and producing Its sensitivity, the area that is embodied in its search coil only has a quarter of array layer gaussmeter), in the present embodiment, Starting stage arranges 12 compensation gaussmeters 111 on layer of compensation 11, i.e. 111a shown in Fig. 1,111b ..., 111l, 12 Compensate gaussmeter 111 along the diagonal of described array layer 11, equidistant (in the present embodiment, between two compensation gaussmeters 111 Distance is 38mm) setting.Compensation gaussmeter 111a to 111f as shown in Figure 1 is arranged on a pair of linea angulata, from 111g to 111l Be arranged on another diagonal, and on described layer of compensation setting compensation gaussmeter 111a, the underface of 111b ..., 111l with Gaussmeter 121 on superconducting quantum interference device array layer 12 corresponds.In the present embodiment, using 12 compensation gaussmeters The field signal of 111 outputs compensates 36 squid gaussmeter outputs of setting on 36 superconducting quantum interference device array layers respectively Field signal.
In the present embodiment, described compensation gaussmeter 111 is fixed to described layer of compensation 11, described layer of compensation 11 by contact pin It is arranged on the printed circuit board (PCB) being electrically connected with the main body of described magnetocardiograph；Described magnetocardiograph need to be applied in ring shielding magnetism In border.
Embodiment two
The present embodiment provide a kind of compensation optimizing method based on the magnetocardiograph described in embodiment one it is characterised in that Described compensation optimizing method comprises the following steps:
Utilize the first field signal compensating gaussmeter generation on described layer of compensation to compensate institute by predesigned compensation mode State the second field signal that on superconducting quantum interference device array layer, each gaussmeter produces, to form the 3rd magnetic field after compensation Signal；
Calculate the assessment parameter of the 3rd field signal after compensating, and according to described assessment parametric synthesis assessment the described 3rd Field signal, to optimize described layer of compensation, is formed on the optimal compensation passage.
Below with reference to diagram to the compensation optimizing side based on the magnetocardiograph described in embodiment one described in the present embodiment Method.Refer to Fig. 2, schematic flow sheet in an embodiment for the compensation optimizing method based on magnetocardiograph of being shown as.As Fig. 2 institute Show, described following step specifically included based on the compensation optimizing method of magnetocardiograph:
S1, utilizes the first field signal compensating gaussmeter generation on described layer of compensation to compensate by predesigned compensation mode The second field signal that on described superconducting quantum interference device array layer, each gaussmeter produces, to form the 3rd magnetic after compensation Field signal.In the present embodiment, described predesigned compensation mode specifically refers to:
The first field signal compensating gaussmeter generation on layer of compensation is multiplied by a coefficient matrix, then deducts described 36 The second field signal that on superconducting quantum interference device array layer, each gaussmeter produces, gets output difference；
Count the quadratic sum of this output difference, obtain a least square and corresponding coefficient matrix；
The second field signal that on described 36 superconducting quantum interference device array layers, each gaussmeter produces deducts minimum flat The product compensating the first field signal that gaussmeter produces on square and corresponding coefficient matrix and described layer of compensation, obtains and compensates The 3rd field signal afterwards.
Above-described predesigned compensation mode is referred to as sliding window least-squares algorithm in the art.
S2, calculates the assessment parameter of the 3rd field signal after compensating, and according to described assessment parametric synthesis assessment 3rd field signal, to optimize described layer of compensation, is formed on the optimal compensation passage.In the present embodiment, mended by calculating The 3rd field signal after repaying to assess concordance with the dependency of a pumping signal applying, peakedness ratio, according to concordance Excellent principle, determines the required position of reference squid gaussmeter and number.Described pumping signal is produced by a circular excitation coil Raw, described circle excitation coil is located at the Dewar bottom part down in described magnetocardiograph, is located at described Dewar in the present embodiment At the about 6.6cm of bottom, and the described circle a diameter of 15cm of excitation coil；Described circle excitation coil two ends load by with its After the mcg-signalses of mcg-signalses emitter transmitting connecting, produce described pumping signal.In the present embodiment converges, described excitation The heart magnetic sizableness of the magnitude of field intensity of signal and medically described definition, that is, at (80pt, 100pt).
In the present embodiment, the size of the magnetic field intensity of described pumping signal calculates according to Biot's Safa law；Described complete Safa law difficult to understand is:
Wherein, μ0Represent permeability of vacuum, μ0=4 × 10-7t·m/a；R represents the radius of circular excitation coil；X represents The abscissa of each gaussmeter and circular excitation coil distance on described superconducting quantum interference device array layer；Y represents described super Lead the vertical coordinate of the abscissa of each gaussmeter and circular excitation coil distance on quantum interference device array layer；H is circular sharp Encourage the vertical dimension of coil and described superconducting quantum interference device array layer；I is big through the electric current of described circle excitation coil Little.
In the present embodiment, described assessment parameter includes:
The 3rd field signal after compensation and one in order to replace mcg-signalses pumping signal time domain correlation coefficient and frequency Domain correlation coefficient；
The characteristic wave crest value of the 3rd field signal after compensation than with the characteristic wave crest value ratio of described pumping signal Standard deviation；And/or
The distortion grade of the isomagnetic chart of the 3rd field signal after compensation.
Wherein, described compensate after the 3rd field signal to one in order to replace the time domain of the pumping signal of mcg-signalses related The calculating process of coefficient is:
50hz bandreject filtering and 100hz low-pass filtering treatment are carried out to the 3rd field signal after the compensation obtaining, is formed The 3rd field signal after processed compensation；
According to preset correlation calculations mode, calculate the 3rd field signal after processed compensation and described pumping signal Time domain correlation coefficient.In the present embodiment, described preset correlation calculations mode is
Wherein, xiFor the 3rd field signal after the processed compensation of sampled point serial number i,Average for n sampled point The 3rd field signal after processed compensation, yiFor the pumping signal of sampled point sequence number i,For the average excitation letter of n sampled point Number.
Simultaneously described compensate after the 3rd field signal to one in order to replace the frequency domain of the pumping signal of mcg-signalses related The calculating process of coefficient is:
The 3rd field signal after processed compensation and described pumping signal are carried out Fourier transformation, by Fourier transformation Processed compensation after the 3rd field signal and described pumping signal substitute into preset correlation calculations mode,
I.e.
Calculate the frequency domain correlation coefficient of the 3rd field signal after processed compensation and described pumping signal.
In the present embodiment, time domain related system and frequency domain correlation coefficient are bigger, and dependency is better.Refer to Fig. 3, display For compensating the dependency diagram of the 3rd field signal and pumping signal after channel compensation.As shown in figure 3,111b (r2) is worst, Its dependency is integrally low, and average is 0.82, serious distortion at point out of the ordinary；111g (r7) and 111l (r12) is optimal, dependency system Number average all reaches 0.95, assumes very high dependency.
The characteristic wave crest value of the 3rd field signal after described compensation is than the characteristic wave crest value with described pumping signal The calculating process of the standard deviation of ratio includes:
The characteristic wave in the 3rd field signal after the processed compensation of identification.In the present embodiment, characteristic wave refers to q ripple, s Ripple, t ripple, r ripple.Specifically the characteristic wave in the 3rd field signal after the processed compensation of identification refers to: after processed compensation 3rd field signal carries out differential, nonlinear transformation, again differential, obtains the point that result is not zero, by definition sharpness, that is, Can determine whether out qrs waveform.Subsequently, statistical average is carried out to the st wave space of the 3rd field signal after processed compensation, s ripple Position add average after st wave space get the position of t ripple, thus realizing the identification of qrst ripple.
The crest value of statistical nature ripple, and the crest value according to characteristic wave, calculate the 3rd magnetic field letter after processed compensation The peak ratio of the characteristic wave in number, that is, calculate q/r in the 3rd field signal after processed compensation, s/r, t/r.
Calculate the peak ratio of characteristic wave in the 3rd field signal after processed compensation and the feature in pumping signal Standard deviation between the peak ratio of ripple, with the deviation of the 3rd field signal after relatively more processed compensation and pumping signal.? In the present embodiment, the computing formula of standard deviation is
Wherein, n is the number of the gaussmeter on array layer, i.e. 36, x in the present embodimentiThe ripple of each characteristic wave of statistics Peakedness ratio, the crest value ratio of each characteristic wave of x pumping signal.Refer to Fig. 4, be shown as compensating gaussmeter 111b, 111g, 111j Qrst crest value compare schematic diagram.As shown in figure 4, the qrst peakedness ratio deviation standard value compensating gaussmeter 111b is the most serious, Therefore distortion is the most serious；The qrst peakedness ratio and the standard value deviation that compensate gaussmeter 111g are very little, and distortion level is low.
Qrst crest value is than the important parameter being assessment distortion level at characteristic point for the mcg-signalses, ratio time domain phase relation Number and frequency domain correlation coefficient more can assessment signal in detail concordance.
Obtain the distortion grade of the isomagnetic chart of the 3rd field signal after processed compensation.In the present embodiment, to locating The 3rd field signal after reason compensates carries out difference process, then inversion imaging, obtains the 3rd field signal after processed compensation Isomagnetic chart, that is, obtain and compensate gaussmeter 111a, the 3rd field signal after the processed compensation that 111b ..., 111l produce Isomagnetic chart, and be compared with the isomagnetic chart of pumping signal, and according to the 3rd magnetic field after the processed compensation of distortion degree arrangement The isomagnetic chart of signal, chooses distortion degree little.111g and 111l is the most clear as compensating passage post-compensation effect.
Based on concordance highest and the undistorted principle of signal, determine and compensate on 36 superconducting quantum interference device array layers most preferably Compensate passage i.e., the compensation passage that 111g and 111l is formed.
The compensation optimizing method based on magnetocardiograph described in the present embodiment utilizes the compensation configuration in magnetocardiograph, effectively Remnant field in suppression shielding room environmental, makes 36 squid signal permutation output high s/n ratios, Hi-Fi heart magnetic letters Number.
Embodiment three
The present embodiment provides a kind of compensation optimizing system 2 based on magnetocardiograph, refers to Fig. 5, is shown as based on heart magnetic Theory structure schematic diagram in an embodiment for the compensation optimizing system of figure instrument.As shown in figure 5, the described benefit based on magnetocardiograph Repay optimization system 2 to include: compensating module 21 and optimization module 22.
Described compensating module 21 is used for utilizing the compensation gaussmeter on described layer of compensation to produce by predesigned compensation mode First field signal compensates the second field signal that on described superconducting quantum interference device array layer, each gaussmeter produces, with shape Become the 3rd field signal after compensating.In the present embodiment, the predesigned compensation mode in described compensating module 21 refers to:
The first field signal compensating gaussmeter generation on layer of compensation is multiplied by a coefficient matrix, then deducts described 36 The second field signal that on superconducting quantum interference device array layer, each gaussmeter produces, gets output difference；
Count the quadratic sum of this output difference, obtain a least square and corresponding coefficient matrix；
The second field signal that on described 36 superconducting quantum interference device array layers, each gaussmeter produces deducts minimum flat The product compensating the first field signal that gaussmeter produces on square and corresponding coefficient matrix and described layer of compensation, obtains and compensates The 3rd field signal afterwards.
The compensation gaussmeter that the acquisition module 22 being connected with described compensating module 21 is used for gathering on described layer of compensation produces The first field signal, each gaussmeter produces on described 36 superconducting quantum interference device array layers the second field signal, benefit The 3rd field signal after repaying.
The optimization module 22 being connected with described compensating module 21 is used for calculating the assessment ginseng of the 3rd field signal after compensating Number, and described 3rd field signal is assessed according to described assessment parametric synthesis, to optimize described layer of compensation, it is formed on optimal Compensate passage.Described assessment parameter includes: the 3rd field signal and after compensation is in order to replace the pumping signal of mcg-signalses Time domain correlation coefficient and frequency domain correlation coefficient；The characteristic wave crest value of the 3rd field signal after compensation is believed than with described excitation Number characteristic wave crest value ratio standard deviation；And/or the distortion grade of the isomagnetic chart of the 3rd field signal after compensating.
In the present embodiment, the 3rd field signal and after described optimization module 22 is used for calculating described compensation is in order to generation Time domain correlation coefficient for the pumping signal of mcg-signalses.
Specifically, described optimization module 22 to obtain compensation after the 3rd field signal carry out 50hz bandreject filtering and 100hz low-pass filtering treatment, forms the 3rd field signal after processed compensation；
According to preset correlation calculations mode, calculate the 3rd field signal after processed compensation and described pumping signal Time domain correlation coefficient.In the present embodiment, described preset correlation calculations mode is
Wherein, xiFor the 3rd field signal after the processed compensation of sampled point serial number i,Average for n sampled point The 3rd field signal after processed compensation, yiFor the pumping signal of sampled point sequence number i,For the average excitation letter of n sampled point Number.
Described optimization module 22 is used for calculating the 3rd field signal and after compensating in order to replace the excitation of mcg-signalses The frequency domain correlation coefficient of signal.
Specifically, the 3rd field signal after processed compensation and described pumping signal are carried out Fu by described optimization module 22 In leaf transformation, the 3rd field signal after the processed compensation of Fourier transformation and described pumping signal are substituted into preset dependency Calculation,
I.e.
Calculate the frequency domain correlation coefficient of the 3rd field signal after processed compensation and described pumping signal.
Described optimization module 22 be used for calculate described compensate after the 3rd field signal characteristic wave crest value than with described The standard deviation of the characteristic wave crest value ratio of pumping signal.
Specifically, the characteristic wave in the 3rd field signal after described optimization module 22 identifies processed compensation.Yu Benshi Apply in example, characteristic wave refers to q ripple, s ripple, t ripple, r ripple.The specifically characteristic wave in the 3rd field signal after the processed compensation of identification Refer to: differential, nonlinear transformation, again differential are carried out to the 3rd field signal after processed compensation, obtains what result was not zero Point, by the sharpness of definition, you can judge qrs waveform.Subsequently, the st ripple to the 3rd field signal after processed compensation Spacing carries out statistical average, the position of s ripple add average after st wave space get the position of t ripple, thus realizing qrst ripple Identification.
The crest value of statistical nature ripple, and the crest value according to characteristic wave, calculate the 3rd magnetic field letter after processed compensation The peak ratio of the characteristic wave in number, that is, calculate q/r in the 3rd field signal after processed compensation, s/r, t/r.
Calculate the peak ratio of characteristic wave in the 3rd field signal after processed compensation and the feature in pumping signal Standard deviation between the peak ratio of ripple, with the deviation of the 3rd field signal after relatively more processed compensation and pumping signal.? In the present embodiment, the computing formula of standard deviation is
σ = 1 n σ i = 1 n ( x i - x )
Wherein, n is the number of the gaussmeter on array layer, i.e. 36, x in the present embodimentiThe ripple of each characteristic wave of statistics Peakedness ratio, the crest value ratio of each characteristic wave of x pumping signal.Refer to Fig. 4, be shown as compensating gaussmeter 111b, 111g, 111l Qrst crest value compare schematic diagram.As shown in figure 4, the qrst peakedness ratio deviation standard value compensating gaussmeter 111b is the most serious, Therefore distortion is the most serious；The qrst peakedness ratio and the standard value deviation that compensate gaussmeter 111g are very little, and distortion level is low.
Qrst crest value is than the important parameter being assessment distortion level at characteristic point for the mcg-signalses, ratio time domain phase relation Number and frequency domain correlation coefficient more can assessment signal in detail concordance.
Described optimization module 22 is additionally operable to obtain the distortion grade of the processed isomagnetic chart of the 3rd field signal after compensating. In the present embodiment, difference process is carried out to the 3rd field signal after processed compensation, then inversion imaging, obtain processed benefit The isomagnetic chart of the 3rd field signal after repaying, that is, obtain and compensate gaussmeter 111a, the processed compensation that 111b ..., 111l produce The isomagnetic chart of the 3rd field signal afterwards, and be compared with the isomagnetic chart of pumping signal, and locate according to distortion degree arrangement The isomagnetic chart of the 3rd field signal after reason compensation, chooses distortion degree little.111g and 111l is as compensation passage post-compensation Effect is the most clear.
Based on concordance highest and the undistorted principle of signal, determine and compensate on 36 superconducting quantum interference device array layers most preferably Compensate passage i.e., the compensation passage that 111g and 111l is formed.
The compensation optimizing system based on magnetocardiograph described in the present embodiment utilizes the compensation configuration in magnetocardiograph, effectively Remnant field in suppression shielding room environmental, makes 36 squid signal permutation output high s/n ratios, Hi-Fi heart magnetic letters Number.
The present embodiment also provides a kind of server 3, refers to Fig. 6, is shown as principle knot in an embodiment for the server Structure schematic diagram.As shown in fig. 6, described server 3 includes the compensation optimizing system 2 based on magnetocardiograph described above.
In sum, magnetocardiograph of the present invention, the compensation optimizing method based on it, system and the server by utilizing heart Remnant field in compensation configuration in magnetic chart instrument, effectively suppression shielding room environmental, makes 36 squid signal permutation output height letters Make an uproar ratio, Hi-Fi mcg-signalses.So, the present invention effectively overcomes various shortcoming of the prior art and has high industrial Value.
Above-described embodiment only principle of the illustrative present invention and its effect, not for the restriction present invention.Any ripe The personage knowing this technology all can carry out modifications and changes without prejudice under the spirit and the scope of the present invention to above-described embodiment.Cause This, those of ordinary skill in the art is complete with institute under technological thought without departing from disclosed spirit such as All equivalent modifications becoming or change, must be covered by the claim of the present invention.

Claims (11)

1. a kind of magnetocardiograph is it is characterised in that described magnetocardiograph includes:
Layer of compensation, is arranged above the superconducting quantum interference device array layer of described magnetocardiograph；
It is provided with least one in order to compensate the magnetic field letter that described superconducting quantum interference device array layer produces on described layer of compensation Number compensation gaussmeter.
2. magnetocardiograph according to claim 1 it is characterised in that: described layer of compensation is arranged at described superconductive quantum interference At predeterminable range above device array layer；And the compensation gaussmeter of setting and superconducting quantum interference device battle array on described layer of compensation Gaussmeter in row layer corresponds.
3. passage magnetocardiograph according to claim 1 it is characterised in that: described compensation gaussmeter be fixed to by contact pin Described layer of compensation, described layer of compensation is arranged on the printed circuit board (PCB) being electrically connected with the main body of described magnetocardiograph；The described heart Magnetic chart instrument need to be applied in magnetic shield environment.
4. a kind of compensation optimizing method based on the magnetocardiograph any one of claim 1-3 is it is characterised in that described Compensation optimizing method comprises the following steps:
The first field signal compensating gaussmeter generation on described layer of compensation is utilized to compensate by predesigned compensation mode described super Lead the second field signal that on quantum interference device array layer, each gaussmeter produces, to form the 3rd magnetic field letter after compensation Number；
Calculate the assessment parameter of the 3rd field signal after compensating, and described 3rd magnetic field is assessed according to described assessment parametric synthesis Signal, to optimize described layer of compensation, determines the optimal compensation passage thereon.
5. compensation optimizing method according to claim 4 it is characterised in that: described predesigned compensation mode is:
The first field signal compensating gaussmeter generation on layer of compensation is multiplied by a coefficient matrix, then deducts described superconduction amount The second field signal that on sub- interfered device array layer, each gaussmeter produces, gets output difference；
Count the quadratic sum of this output difference, obtain a least square and corresponding coefficient matrix；
The second field signal that on described superconducting quantum interference device array layer, each gaussmeter produces deducts least square and right The product compensating the first field signal that gaussmeter produces on the coefficient matrix answered and described layer of compensation, obtains the after compensating Three field signals.
6. compensation optimizing method according to claim 4 it is characterised in that: described assessment parameter include:
The 3rd field signal after compensation is with one in order to replace the time domain correlation coefficient of pumping signal and the frequency domain phase of mcg-signalses Close coefficient；
The characteristic wave crest value of the 3rd field signal after compensation is than the standard with the characteristic wave crest value ratio of described pumping signal Deviation；And/or
The distortion grade of the isomagnetic chart of the 3rd field signal after compensation.
7. compensation optimizing method according to claim 6 it is characterised in that:
Described pumping signal is produced by a circular excitation coil, and described circle excitation coil is located at the Dewar in described magnetocardiograph Bottom part down；Described circle excitation coil, after loading the mcg-signalses by the transmitting of connected mcg-signalses emitter, produces Raw described pumping signal；
The size of the magnetic field intensity of described pumping signal calculates according to Biot's Safa law；Described Biot's Safa law is:
b z = μ 0 i 4 π &integral; 0 2 π ( r - x c o s θ - y s i n θ ) r d θ [ ( x - r cos θ ) 2 + ( y - sin θ ) 2 + h 2 ] 3 2 ;
Wherein, μ0Represent permeability of vacuum, μ0=4 × 10-7t·m/a；R represents the radius of circular excitation coil；X represents described super Lead the abscissa of each gaussmeter and circular excitation coil distance on quantum interference device array layer；Y represents described Superconducting Quantum The vertical coordinate of the abscissa of each gaussmeter and circular excitation coil distance on interfered device array layer；H is circular excitation coil Vertical dimension with described superconducting quantum interference device array layer；I is the size of current through described circle excitation coil.
8. compensation optimizing method according to claim 6 it is characterised in that: described compensate after the 3rd field signal and The time domain correlation coefficient of pumping signal and the calculating process of frequency domain correlation coefficient in order to replace mcg-signalses include:
50hz bandreject filtering and 100hz low-pass filtering treatment are carried out to the 3rd field signal after the compensation obtaining, is formed and locate The 3rd field signal after reason compensation；
According to preset correlation calculations mode, calculate the time domain of the 3rd field signal after processed compensation and described pumping signal Correlation coefficient；
The 3rd field signal after processed compensation and described pumping signal are carried out Fourier transformation, according to described preset simultaneously Correlation calculations mode, calculates the frequency domain correlation coefficient of the 3rd field signal after processed compensation and described pumping signal.
9. compensation optimizing method according to claim 8 it is characterised in that: described compensate after the 3rd field signal spy Levy ripple crest value to include than the calculating process with the standard deviation of the characteristic wave crest value ratio of described pumping signal:
The characteristic wave in the 3rd field signal after the processed compensation of identification；
The crest value of statistical nature ripple, and the crest value according to characteristic wave, calculate in the 3rd field signal after processed compensation Characteristic wave peak ratio；
Calculate characteristic wave in the peak ratio of characteristic wave and the pumping signal in the 3rd field signal after processed compensation Standard deviation between peak ratio.
10. a kind of compensation optimizing system based on the magnetocardiograph any one of claim 1-3 is it is characterised in that institute State compensation optimizing system to include:
Compensating module, for utilizing the first magnetic field letter compensating gaussmeter generation on described layer of compensation by predesigned compensation mode Number compensate the second field signal that on described superconducting quantum interference device array layer, each gaussmeter produces, to be formed after compensation 3rd field signal；
Optimization module, for calculating the assessment parameter of the 3rd field signal after compensating, and comments according to described assessment parametric synthesis Estimate described 3rd field signal, to optimize described layer of compensation, determine the optimal compensation passage thereon.
A kind of 11. servers are it is characterised in that include being based on as claimed in claim 10 any one of claim 1-3 institute The magnetocardiograph compensation optimizing system stated.
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Cited By (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN106901717A (en) * 2017-03-01 2017-06-30 中国科学院上海微***与信息技术研究所 Three-dimensional heart source localization method, system and server
CN108514413A (en) * 2018-04-04 2018-09-11 漫迪医疗仪器（上海）有限公司 Dewar biology Magnetic Detection System and its design method/system, readable storage medium storing program for executing
CN110687491A (en) * 2018-07-04 2020-01-14 漫迪医疗仪器（上海）有限公司 Detection performance evaluation device/method, medium, and processing device for magnetocardiogram system
CN112179343A (en) * 2019-07-01 2021-01-05 新加坡国立大学 Magnet positioning system and method

Families Citing this family (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE102022209444A1 (en) * 2022-09-09 2024-03-14 Robert Bosch Gesellschaft mit beschränkter Haftung Method for determining a magnetocardiogram signal of a living being

Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20020158631A1 (en) * 2001-04-27 2002-10-31 Akihiko Kandori Biomagnetic field measuring apparatus
CN102988038A (en) * 2012-12-14 2013-03-27 中国科学院上海微***与信息技术研究所 First-order gradient compensation module and method for unmask magnetocardiography
CN104427931A (en) * 2012-07-02 2015-03-18 利兹大学 Magnetometer for medical use
CN104545913A (en) * 2013-10-18 2015-04-29 中国科学院上海微***与信息技术研究所 Adaptive compensation method and system for environmental magnetic field suppression
CN105022005A (en) * 2014-04-23 2015-11-04 中国科学院上海微***与信息技术研究所 SQUID magnetic sensor measuring sensitivity enhancement method, device and system

Patent Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20020158631A1 (en) * 2001-04-27 2002-10-31 Akihiko Kandori Biomagnetic field measuring apparatus
CN104427931A (en) * 2012-07-02 2015-03-18 利兹大学 Magnetometer for medical use
CN102988038A (en) * 2012-12-14 2013-03-27 中国科学院上海微***与信息技术研究所 First-order gradient compensation module and method for unmask magnetocardiography
CN104545913A (en) * 2013-10-18 2015-04-29 中国科学院上海微***与信息技术研究所 Adaptive compensation method and system for environmental magnetic field suppression
CN105022005A (en) * 2014-04-23 2015-11-04 中国科学院上海微***与信息技术研究所 SQUID magnetic sensor measuring sensitivity enhancement method, device and system

Cited By (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN106901717A (en) * 2017-03-01 2017-06-30 中国科学院上海微***与信息技术研究所 Three-dimensional heart source localization method, system and server
CN108514413A (en) * 2018-04-04 2018-09-11 漫迪医疗仪器（上海）有限公司 Dewar biology Magnetic Detection System and its design method/system, readable storage medium storing program for executing
CN108514413B (en) * 2018-04-04 2023-09-22 漫迪医疗仪器（上海）有限公司 Dewar biological magnetic detection system, design method/system thereof and readable storage medium
CN110687491A (en) * 2018-07-04 2020-01-14 漫迪医疗仪器（上海）有限公司 Detection performance evaluation device/method, medium, and processing device for magnetocardiogram system
CN110687491B (en) * 2018-07-04 2021-11-16 漫迪医疗仪器（上海）有限公司 Detection performance evaluation device/method, medium, and processing device for magnetocardiogram system
CN112179343A (en) * 2019-07-01 2021-01-05 新加坡国立大学 Magnet positioning system and method

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