CN117297612A - Magnetocardiogram three-dimensional measurement device and three-dimensional imaging method - Google Patents
Magnetocardiogram three-dimensional measurement device and three-dimensional imaging method Download PDFInfo
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- 238000003384 imaging method Methods 0.000 title claims abstract description 15
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- 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
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- A61B2576/023—Medical imaging apparatus involving image processing or analysis specially adapted for a particular organ or body part for the heart
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Abstract
The invention discloses a magnetocardiogram three-dimensional measuring device and a three-dimensional imaging method, wherein a plurality of three-dimensional SERF atomic magnetometers (z, x, y directions) are arranged at positions (x, y) parallel to the chest surface of a human body, z-direction magnetic field components perpendicular to the xy plane of a heart magnetic field, x-direction magnetic field components parallel to the xy plane of the heart magnetic field and y-direction magnetic field components are measured, signals output by the magnetometers are calculated, and calculation results are displayed. The result is projected onto a three-dimensional heart model reconstructed from a two-dimensional image of the heart by calculating the current distribution and the magnitude of the current distribution. Compared with the existing method, the method can obtain more detailed current distribution and a display result of the current distribution which is easier to understand visually, and improves the understanding degree of a user on a Magnetocardiogram (MCG).
Description
Technical Field
The invention relates to the field of magnetocardiogram three-dimensional measurement for measuring weak magnetic fields generated by human heart electric activity by using a SERF (spin exchange relaxation free) atomic magnetometer, in particular to a magnetocardiogram three-dimensional measurement device and a three-dimensional imaging method.
Background
The current distribution in the myocardium can be visualized by estimating the current distribution of a magnetic field source from cardiac magnetic field data by measuring a weak magnetic field (hereinafter, simply referred to as a cardiac magnetic field) generated by an electrical activity of a human heart using a magnetocardiogram three-dimensional measuring device and a three-dimensional imaging method, which is also referred to as a magnetocardiogram inverse problem. Research on its analytical methods has been ongoing. The main analysis methods include wiener filters, least squares methods and the like, and the characteristics and the effectiveness of the analysis methods are displayed through numerical simulation.
Methods for projecting current distributions solved by the magnetocardiogram inverse problem onto a three-dimensional heart model reconstructed from a two-dimensional image (MR or CT) of the subject's heart have been developed. However, in this method of displaying the current distribution, since measurement such as MRI or CT is required for each subject to be analyzed, it is very complicated and takes time before the display result is obtained.
Therefore, there is a need for a magnetocardiographic three-dimensional measurement device and three-dimensional imaging method that directly obtain a visually easily understood current distribution without performing MRI or CT measurement of a subject as required in the prior art.
Disclosure of Invention
In order to overcome the defects in the prior art, the invention provides a magnetocardiogram three-dimensional measuring device and a three-dimensional imaging method, wherein a plurality of three-dimensional SERF atomic magnetometers (z, x, y directions) are arranged at positions (x, y) parallel to the chest surface of a human body to measure a z-direction magnetic field component perpendicular to the xy plane of a heart magnetic field, and an x-direction magnetic field component and a y-direction magnetic field component parallel to the xy plane of the heart magnetic field; the problems of time and effort consumption in the existing imaging method are solved by establishing a standard heart model and an alignment technology thereof.
In order to achieve the above purpose, the invention adopts the following technical scheme:
a magnetocardiogram three-dimensional measuring device comprises a SERF atom magnetometer, a sensor bracket, a movable platform, a bed for lying a subject, a driving circuit for driving the SERF atom magnetometer, an amplifying and filtering unit for amplifying and filtering an output signal from the driving circuit, and a computer for processing digital signals of the output signal of the amplifying and filtering unit and controlling all parts of the device; a plurality of three-dimensional SERF atom magnetometers are arranged at the positions parallel to the chest surface of the human body, z-direction magnetic field components perpendicular to the xy plane of the heart magnetic field, x-direction magnetic field components and y-direction magnetic field components parallel to the xy plane of the heart magnetic field are measured, the output signals of the SERF atom magnetometers are calculated, and the calculation results are displayed; the digital signal processing of the computer includes projecting the results onto a three-dimensional heart model reconstructed from a two-dimensional image of the heart by calculating the current distribution and the magnitude of the current distribution.
The invention also provides a three-dimensional imaging method of the magnetocardiogram three-dimensional measuring device, which uses the MRI device to carry out heart detection, and the MRI measuring area is arranged in an area 300mm multiplied by 300mm right above the chest of the subject; moving along the z-axis at 5mm intervals in the MRI measurement region, sequentially acquiring MR images of the chest with a slice thickness of 1mm, and acquiring coordinates of the xiphoid process of the chest in the MRI measurement coordinate system; reconstructing a three-dimensional heart model, and performing a transformation (x) between coordinates of the three-dimensional heart model and coordinates of cardiac magnetic field measurement using coordinates of xiphoid process of chest n ，y n ，z n ) The method comprises the steps of carrying out a first treatment on the surface of the The position of the three-dimensional heart model is determined using the dipole presumption site of the P-wave and coordinates of the sinus node set on the three-dimensional heart model.
Compared with the prior art, the invention has the beneficial effects that:
according to the present invention, the position of a three-dimensional heart model can be obtained from P-wave heart magnetic field data for a subject or healthy subject suffering from heart disease. In addition, by projecting the current distribution obtained by solving the magnetocardiogram inverse problem onto the three-dimensional heart model to be constructed, the current distribution corresponding to each part of the heart can be displayed in a simple manner without measuring such as MRI or CT, a visually more easily understood current distribution display result can be obtained, and the understanding degree of the MCG by the user can be improved, so that the method becomes a new heart imaging method.
Drawings
Fig. 1 is a block diagram of a magnetocardiogram measuring apparatus according to the present invention.
Figure 2 shows an arrangement of the SERF atomic magnetometers and a setup diagram with respect to a subject.
Fig. 3 shows a schematic diagram of a heart detection using an MRI apparatus.
Fig. 4 shows a three-dimensional heart model generated from MR images and a sinus node on the three-dimensional heart model.
Fig. 5 shows a dipole estimation site of the P wave.
Fig. 6 shows the position of a three-dimensional heart model derived from the dipole estimation site of the P-wave.
Fig. 7 is a flowchart showing a position determination method of the three-dimensional heart model.
Fig. 8 shows a cardiac magnetic field measurement region and an extended measurement region.
Fig. 9 shows a display screen.
Fig. 10 shows an explanatory diagram of angles α and β of the viewpoint direction.
Detailed Description
The present invention will be described in further detail with reference to the drawings and examples, in order to make the objects, technical solutions and advantages of the present invention more apparent. It should be understood that the specific embodiments described herein are for purposes of illustration only and are not intended to limit the scope of the invention. In addition, the technical features of the embodiments of the present invention described below may be combined with each other as long as they do not collide with each other.
As shown in fig. 1, the magnetocardiogram measuring apparatus of the present invention includes a SERF atomic magnetometer 1, a sensor holder 2, a movable platform 3, and a bed 4 on which a subject (not shown) lies. The movable stage 3 is movable in the short axis direction (a direction, x direction), in the long axis direction (C direction, y direction), and in the up-down direction (B direction, z direction). The magnetocardiogram measuring device of the present invention further comprises a driving circuit 5 for driving the SERF atom magnetometer 1, an amplifier filtering unit 6 for amplifying and filtering the output signal from the driving circuit 5, and a computer 7 for performing digital signal processing on the output signal of the amplifier filtering unit 6 and controlling each part of the device.
As shown in fig. 2, the SERF atom magnetometers 1 are arranged in an 8×8 grid pattern, and the distance between adjacent SERF atom magnetometers 1 is 35mm. The cardiac magnetic field measurement region 9 composed of 64 SERF atom magnetometers 1 is arranged parallel to the chest 8 of the subject, and the cardiac magnetic field measurement region 9 is aligned such that 7 rows and 3 columns of SERF atom magnetometers 1 are positioned directly above the xiphoid process 11 of the chest. The coordinate system of the cardiac magnetic field measurement region 9 takes the position of the SERF atom magnetometer 1 of 8 rows and 1 columns as an origin. The component of the magnetic field measurement data of the heart measured By each SERF atom magnetometer 1 perpendicular to the magnetic field measurement region 9 is Bz (normal direction component), and the parallel component is Bx, by (tangential direction component).
To construct a standard heart model for all subjects possible, MR image data of adult male a without a history of heart disease was used. Hereinafter, the standard heart model will be simply referred to as heart model.
As shown in fig. 3, a nuclear magnetic resonance imaging apparatus (hereinafter, abbreviated as MRI apparatus) is used for heart detection. The MRI measurement region 12 is a region 300mm×300mm directly above the chest 8 of the subject. For imaging the three-dimensional structure of the heart, MR images of the chest with a slice thickness of 1mm are acquired sequentially, moving along the z-axis at 5mm intervals in the MRI measurement region 12. In order to convert the coordinates of the heart model generated from the MR image into the coordinates of the cardiac magnetic field measurement, the coordinates of the xiphoid process 11 of the chest are first acquired in the coordinate system of the MRI measurement. The coordinates of the cardiac model and the coordinates of the cardiac magnetic field measurement (x) are then performed using the coordinates of the xiphoid process 11 of the chest n ，y n ，z n ) And a transformation between them.
The position of the heart model is determined by focusing on the P-wave generated by the pacing excitation of the sinoatrial node to the atrial excitation induced by the atrium, using the dipole presumption site of the P-wave and the coordinates of the sinoatrial node set on the heart model.
The dipole estimation method is to represent the electrophysiological activity in a living body by a current dipole, and estimate the position coordinates (x d ，y d ，z d ) The inverse problem method of the direction θ and the electric dipole moment Q is attributed to the optimization problem that minimizes the objective function F in the equation (1).
F(x d ，y d ，z d ，θ，Q)＝Σ(B t，i －QL i (x d ，y d ，z d ，θ)) 2 /Σ(B t，i ) 2
(1)
Wherein B is t，i (i=1, 2, …, 64) represents the magnetic induction intensity at a certain time t measured by the SERF atomic magnetometer, L i Represents coefficients derived from the Law of Biot-Savart Law (Biot-Savart Law). i=1,2, …,64; the sum of i=1 to 64 is represented by the sum of the numerator and denominator.
As shown in fig. 4, is a heart model generated from MR images and the sinus node on the heart model. First, coordinates (x s ，y s ，z s ). Next, dipole estimation is performed using the cardiac magnetic field measurement data at the initial time of the P-wave. Here, the Simplex Method (Simplex Method) is applied to the optimization problem that minimizes the objective function F of the equation (1).
As shown in fig. 5, the dipole estimation portion of the P wave is shown. The coordinates of the dipole 15 derived by the dipole estimation method are (x d ，y d ，z d ). The coordinates (x d ，y d ，z d ) Coordinates (x) of the sinus node 14 of the heart model s ，y s ，z s ) The difference (Deltax, deltay, deltaz) is determined from equation (2).
Finally, the position (x, y, z) of the heart model is derived from equation (3) using equation (2).
As shown in fig. 6, the result of aligning the heart model based on the dipole-estimated site of P-wave was obtained for adult male B without history of heart disease. In fig. 6, the region 16 surrounded by a solid line represents the outline of the heart of the subject B constructed from the actual MR image. The hatched area 17 surrounded by the solid line indicates the position of the heart model in which the alignment is performed. As can be seen from fig. 6, for a subject based on a sinus rhythm (normal rhythm) normal, the method places the heart model in a position shifted to the left from the actual heart position.
As shown in fig. 7, the above-described processing flow includes the following steps:
step 1, starting a processing flow;
step 2, measuring a heart magnetic field by using a 64-channel SERF atomic magnetometer;
step 3, performing magnetocardiogram signal processing for measuring a magnetic field;
step 4, deriving the current distribution and the magnitude of the current distribution;
step 5, setting coordinates of a sinus node on the heart model;
step 6, estimating the dipole position of the P wave;
step 7, aligning the heart model by using the coordinates of the sinus node and the dipole position;
step 8, deriving an expanded magnetocardiogram measurement region;
step 9, deriving the current distribution in the expanded magnetocardiogram measurement region in step 8 and the magnitude of the current distribution;
step 10, projecting the current distribution and the magnitude of the current distribution which are derived in the step 4 and the step 9 on a heart model, and displaying the projection result on a picture of a computer 7;
step 11, ending the flow of the processing.
As shown in fig. 8, the above-described steps 8 and 9 are explained. Fig. 8 shows a magnetocardiographic measurement region and an expanded region. When using this method to determine the position of the heart model, it is possible that the heart model is not necessarily included in the magnetocardiographic measurement region 18. At this time, it is difficult to obtain a current distribution corresponding to a heart model site deviated from the magnetocardiographic measurement region 18 from the measured value of the magnetic field of the heart. Therefore, the magnetocardiogram measurement region 18 is expanded, and the current distribution corresponding to the expanded first region 19-1 and the expanded second region 19-2 is derived using spline interpolation. The current distribution corresponding to the extended first region 19-1, the extended second region 19-2 is projected onto a heart model not comprised in the magnetocardiographic measurement region 18.
Fig. 9 shows a current distribution and a screen display of the magnitude of the current distribution on the computer 7. A display screen 20 of a magnetic field waveform measured by the single SERF atom magnetometer 1, a display screen 21 of a current distribution projected on a heart model and a magnitude of the current distribution, and a selection button 22 are displayed on a screen of the computer 7.
The selection button 22 is provided with a magnetocardiogram waveform representation button 23, an MR heart image selection button 24, a three-dimensional heart model construction button 25, a magnetocardiogram inverse problem calculation button 26, and a current distribution representation button 27.
On the display screen 20 of the magnetic field waveform, a current distribution display time slot 28 is arranged. By matching the current distribution display time line 28 with an arbitrary timing on the magnetic field waveform, a display screen 21 of the current distribution projected on the heart model and the magnitude of the current distribution corresponding to the timing can be obtained.
In the display screen of fig. 9, a pull-down menu 29 for performing angle adjustment of the viewpoint direction of the display screen 21 of the current distribution projected on the heart model and the magnitude of the current distribution is arranged. By changing the angles α and β of the viewpoint direction of the pull-down menu 29, the viewpoint direction of the display screen 21 of the current distribution projected on the heart model and the magnitude of the current distribution can be arbitrarily selected.
There are a pull-down menu 30 for selecting the intensity display range of the magnetic field waveform on the display screen 20 of the magnetic field waveform, and an input field 31 for displaying the current distribution display time corresponding to the current distribution display time line 28.
The angles α and β of the viewpoint direction will be described with reference to fig. 10. Fig. 10 is a view showing the current distribution projected on the heart model and the angles α and β of the viewpoint direction of the display screen 21 of the magnitude of the current distribution. Including a coordinate system 32 of the viewpoint and a coordinate system 33 of the heart model 13. Here, the point at which the center point 34 of the heart model 13 is projected onto the xy plane along the z' axis is set to o ". Further, a straight line passing through the o "point and parallel to the x axis is referred to as x". At this time, an angle formed by a straight line connecting the viewpoint position o and the center point 34 of the heart model 13 and the xy plane is set to β. Further, an angle formed by a straight line connecting the center point 34 of the heart model 13 and the point o "and x" is set to α.
It will be readily appreciated by those skilled in the art that the foregoing description is merely a preferred embodiment of the invention and is not intended to limit the invention, but any modifications, equivalents, improvements or alternatives falling within the spirit and principles of the invention are intended to be included within the scope of the invention.
Claims (8)
1. The magnetocardiogram three-dimensional measuring device is characterized by comprising a SERF atom magnetometer, a sensor bracket, a movable platform, a bed for lying a subject, a driving circuit for driving the SERF atom magnetometer, an amplifying and filtering unit for amplifying and filtering an output signal from the driving circuit, and a computer for performing digital signal processing on the output signal of the amplifying and filtering unit and controlling all parts of the device; a plurality of three-dimensional SERF atom magnetometers are arranged at the positions parallel to the chest surface of the human body, z-direction magnetic field components perpendicular to the xy plane of the heart magnetic field, x-direction magnetic field components and y-direction magnetic field components parallel to the xy plane of the heart magnetic field are measured, the output signals of the SERF atom magnetometers are calculated, and the calculation results are displayed; the digital signal processing of the computer includes projecting the results onto a three-dimensional heart model reconstructed from a two-dimensional image of the heart by calculating the current distribution and the magnitude of the current distribution.
2. The magnetocardiogram three-dimensional measuring apparatus according to claim 1, wherein the magnitude, direction and position of a current source are estimated at the start time of the P-wave based on the magnetocardiogram signal in the digital signal processing.
3. The magnetocardiogram three-dimensional measurement device according to claim 1, wherein in the digital signal processing, three-dimensional heart model data is generated based on heart two-dimensional image data.
4. The magnetocardiogram three-dimensional measurement device according to claim 1, wherein the digital signal processing is performed to minimize a deviation between the position of the sinus node and the estimated position of the current source.
5. Three-dimensional imaging of a magnetocardiographic three-dimensional measuring device according to any of claims 1-4The method is characterized in that an MRI device is used for heart detection, and an MRI measurement area is arranged in an area 300mm multiplied by 300mm right above the chest of a subject; moving along the z-axis at 5mm intervals in the MRI measurement region, sequentially acquiring MR images of the chest with a slice thickness of 1mm, and acquiring coordinates of the xiphoid process of the chest in the MRI measurement coordinate system; reconstructing a three-dimensional heart model, and using coordinates of the xiphoid process of the chest, performing a three-dimensional heart model coordinate and a heart magnetic field measurement coordinate (x n ，y n ，z n ) A transformation between; the position of the three-dimensional heart model is determined using the dipole presumption site of the P-wave and coordinates of the sinus node set on the three-dimensional heart model.
6. The three-dimensional imaging method according to claim 5, wherein determining the position of the three-dimensional heart model using the dipole presumption site of the P-wave and coordinates of the sinus node set on the three-dimensional heart model comprises:
the dipole estimation site of the P wave is realized by a dipole estimation method, which is attributed to an optimization problem that minimizes the objective function F in the equation (1):
F(x d ，y d ，z d ，θ，Q)＝Σ(B t，i －QL i (x d ，y d ，z d ，θ)) 2 /Σ(B t，i ) 2 (1)
wherein B is t，i Representing the magnetic induction intensity of a moment t measured by a SERF atomic magnetometer (x) d ，y d ，z d ) θ and Q represent the position coordinates, direction and electric dipole moment, L, respectively, of the current dipole i Representing coefficients derived from the law of biot-savart, i=1, 2, …,64; the sum of the numerator and denominator represents i=1 to 64;
then, coordinates (x s ，y s ，z s ) The method comprises the steps of carrying out a first treatment on the surface of the Next, dipole estimation is performed using the cardiac magnetic field measurement data at the initial time of the P-wave; the coordinates of the dipole derived by the dipole estimation method are (x d ，y d ，z d ) The method comprises the steps of carrying out a first treatment on the surface of the The coordinates (x d ，y d ，z d ) Coordinates (x) of sinus node with three-dimensional heart model s ，y s ，z s ) The difference (Δx, Δy, Δz) is determined from formula (2):
finally, the position (x, y, z) of the three-dimensional heart model is derived from equation (3) using equation (2):
7. the three-dimensional imaging method according to claim 6, wherein determining the position of the three-dimensional heart model using the dipole presumption site of the P-wave and coordinates of the sinus node set on the three-dimensional heart model further comprises: the three-dimensional heart model is aligned based on the dipole estimation site of the P-wave.
8. The three-dimensional imaging method of claim 7, wherein said aligning comprises the steps of:
step 1, starting a processing flow;
step 2, measuring a heart magnetic field by using a 64-channel SERF atomic magnetometer;
step 3, performing magnetocardiogram signal processing for measuring a magnetic field;
step 4, deriving the current distribution and the magnitude of the current distribution;
step 5, setting coordinates of a sinus node on the three-dimensional heart model;
step 6, estimating the dipole position of the P wave;
step 7, aligning the three-dimensional heart model by using the coordinates of the sinus node and the dipole position;
step 8, deriving an expanded magnetocardiogram measurement region;
step 9, deriving the current distribution in the expanded magnetocardiogram measurement region in step 8 and the magnitude of the current distribution;
step 10, projecting the current distribution and the magnitude of the current distribution which are derived in the step 4 and the step 9 on a three-dimensional heart model, and displaying a projection result on a picture of a computer;
step 11, ending the flow of the processing.
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