CN113384259B - A monitoring electrode setting method for parietal and temporal lobe lesions - Google Patents
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- 210000003478 temporal lobe Anatomy 0.000 title claims abstract description 17
- 230000001936 parietal effect Effects 0.000 title claims abstract description 15
- 210000001152 parietal lobe Anatomy 0.000 title claims abstract description 15
- 238000012544 monitoring process Methods 0.000 title claims abstract description 14
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- 208000028867 ischemia Diseases 0.000 description 5
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Abstract
本发明公开了一种针对顶叶及颞叶病变的监测电极设置方法，该方法利用物体内部阻抗变化会呈现在电极的电位变化上这一特性，对出现在顶叶及颞叶的病变情况进行了相应的监测电极优化；采用相对激励模式，采集边界电压，进行基础成像；根据基础成像判断当前病变位置，再根据病变所处区域不同设定主电极与副电极，并将其余电极紧密排布在主电极两侧，最大化目标区域相对灵敏度；然后依次选定电极对，将电极对向副电极移动，根据RS、BR、PE判断成像质量来筛选最优电极对位置，固定电极对到最优电极对位置。本发明优化了脑病变高概率位置的成像结果，并提供了高质量的头部内部电导率可视化分布。
The present invention discloses a monitoring electrode setting method for parietal and temporal lobe lesions. The method utilizes the characteristic that the change of internal impedance of an object will be presented in the change of electrode potential, and optimizes the corresponding monitoring electrodes for the lesions occurring in the parietal and temporal lobes; adopts a relative excitation mode, collects boundary voltage, and performs basic imaging; determines the current lesion position according to basic imaging, and then sets the main electrode and the auxiliary electrode according to the different areas where the lesions are located, and closely arranges the remaining electrodes on both sides of the main electrode to maximize the relative sensitivity of the target area; then selects the electrode pair in turn, moves the electrode pair to the auxiliary electrode, and screens the optimal electrode pair position according to the imaging quality based on RS, BR, and PE, and fixes the electrode pair to the optimal electrode pair position. The present invention optimizes the imaging results of high-probability locations of brain lesions and provides high-quality visualization distribution of internal conductivity of the head.
Description
Technical Field
The invention belongs to the technical field of brain lesion detection application of electrical tomography, and particularly relates to a method for setting monitoring electrodes for parietal and temporal lobe lesions.
Background
The electrical tomography (ELECTRICAL TOMOGRAPHY, ET) is a soft field imaging technique, and the principle is that electrodes arranged on the surface of an object are utilized to regularly apply excitation to the electrodes, if certain impedance changes exist in the object, certain potential changes are caused on the measurement electrodes, and the internal impedance changes can be reversely deduced through certain mathematical operations on the potential changes, so that the interior of the object is visualized. Capacitance Tomography (ECT) ELETRICAL CAPACITANCE, resistance Tomography (ERT) ELECTRICAL RESISTANCE and electromagnetic Tomography (Eletromagnetic Tomography, EMT) are three fundamental imaging modalities of electrical Tomography, on the basis of which Electrical Impedance Tomography (EIT) techniques are derived. The EIT technology has very attractive prospect in medical detection, and has good application prospect in lung lesion detection, brain lesion detection, breast cancer detection and abdominal organ function imaging because of the characteristics of non-invasiveness, no radiation, low cost and the like. T Dowrick et al 2016 published in physiological measurements (Physiological Measurement) volume 37, volumes 765-784, entitled' in vivo bioimpedance changes in mouse hemorrhage and ischemic stroke three-dimensional brain stroke imaging by impedance tomography '(In vivo bioimpedance changes during haemorrhagic and ischaemic stroke in rats:towards 3D stroke imaging using electrical impedance tomography), article using EIT differential imaging, truly experimental and image reconstruction of mouse hemorrhage and ischemia models, which confirmed the feasibility and accuracy of EIT in brain experiments. The article "living body detection and imaging of newborn piglets for intracerebral hemorrhage '(In vivo Detection and Imaging of Intraventricular Hemorrhage in Neonatal Piglets Using Electrical Impedance Tomography), using electrical impedance tomography," published by Y D Li et al 2018, volume 27, no. 2, journal of biomedical engineering (english edition) of china (Chinese Journal of Biomedical Engineering), likewise uses differential imaging, employs a relative excitation adjacent measurement mode, and because the head is irregularly shaped and the skull has a high degree of non-conductive properties, it is difficult to let current penetrate to reach the central region of the brain if a conventional adjacent excitation mode is employed. The experiment adopts electrode arrangement with 16 electrodes uniformly arranged, and the result of the electrode arrangement can detect bleeding and ischemia parts, but the size and shape of lesions cannot be accurately judged due to more artifacts. Experiments show that 14% of patients with cerebral hemorrhage are in frontal lobe, 7% of patients with cerebral hemorrhage are in parietal lobe, 48% of patients with cerebral hemorrhage are in temporal lobe, and 31% of patients with cerebral hemorrhage are in occipital lobe. Therefore, the probability of cerebral hemorrhage at the temporal lobe and the top lobe is up to 55%, however, the probability is influenced by the relative excitation mode and the uniform electrode arrangement, the imaging result is poor when lesions are positioned at the two parts, and certain optimization is needed to ensure the image quality, so that EIT has more advantages in brain lesion detection.
Disclosure of Invention
The invention solves the technical problem of providing a method for setting monitoring electrodes aiming at the pathological changes of the parietal lobe and the temporal lobe, which utilizes the fact that the internal impedance change of an object can be presented on the potential change of the electrodes, and by changing the arrangement mode of the electrodes, the potential change information comes from the area surrounded by the parietal lobe and the temporal lobe, namely, the temple on two sides and the ear behind two sides, and irrelevant signals are reduced, so that the imaging quality is improved.
The invention adopts the following technical proposal to solve the technical problems, and is a method for setting monitoring electrodes aiming at parietal and temporal lesions, which is characterized by comprising the following specific steps:
Under the conditions that a human body stands and the head is vertically upwards, respectively making a plane I and a plane II which are vertical to the ground, connecting temple on two sides of the cranium on the plane I, connecting the back of the left ear with the back of the right ear on the plane II, setting the area of the cranium between the plane I and the plane II as an area to be optimized, making a plane III which is vertical to the connecting line of the left ear and the right ear, and moving from the left ear to the right ear The intersection of the area swept during the movement and the area to be optimized is an alpha 1 area, and the plane three-right ear is continuously movedThe intersection of the area swept during the movement and the area to be optimized is an alpha 2 area, and the plane three-right ear is moved continuouslyThe intersection of the area swept in the moving process and the area to be optimized is an alpha 3 area, wherein c is the length of a line segment of a left ear-to-right ear connecting line;
Respectively placing one electrode as a reference electrode to be fixed on the position, which is 6cm away from the front position, of the right ear and the front position of the left ear of the patient, and placing the rest electrodes at intervals on a horizontal plane parallel to the ground where the reference electrode is positioned Placed around the patient's head, where D is the patient's head circumference and n is the number of electrodes;
step three, adopting a relative excitation mode, collecting boundary voltage, and performing basic imaging;
Wherein the relative excitation mode is specifically to select any one electrode as excitation electrode to inject excitation current, and simultaneously select counter-clockwise interval with the excitation electrode The electrode of each electrode is grounded as a grounding electrode, after the point position information of the electrode except the exciting electrode and the grounding electrode is obtained, the next electrode is selected anticlockwise as the exciting electrode, and the grounding electrode still keeps anticlockwise interval with the new exciting electrodeThe electrodes are used for finishing excitation until all the electrodes are selected as excitation electrodes and potential information on the rest electrodes is obtained;
Judging the current lesion position according to basic imaging, and calculating and reserving relative sensitivity RS, position offset PE and blur radius BR;
Wherein S αi represents the pixel sensitivity value in the alpha i region, S represents the pixel sensitivity value of the whole brain region, and the value range of i is 1 or 3;
X t、Yt represents the X-axis coordinate and Y-axis coordinate of the pixel points with the conductivity greater than or equal to 50% of the maximum conductivity in all the pixel points of the reconstructed image, and P represents the number of the pixel points with the conductivity greater than or equal to 50% of the maximum conductivity in all the pixel points of the reconstructed image;
X, Y denote the X-axis coordinate and Y-axis coordinate of the geometric center of the lesion on the base imaging image, respectively;
R t represents the radius of a lesion part, A t represents the area of the lesion part, R represents the radius of the whole imaging area, A represents the area of the whole imaging area, BR value represents the accuracy of the reconstructed image, and BR value is smaller, the more accurate the imaging target is, and the fewer artifacts are;
Step five, judging whether the pathological change position of the image is in an alpha 2 area, namely in the geometric center position of the brain, if so, ensuring enough current penetration effect, and if not, entering step six, wherein the electrode position is not adjusted and all the steps are finished;
Step six, two reference electrodes are fixed, the reference electrode closest to the lesion area is defined as a main electrode, the other reference electrode is an auxiliary electrode, all electrodes except the main electrode and the auxiliary electrode are equally divided into two groups, one group is started by the main electrode, the adjacent electrode edge interval e is placed on the outer side of the scalp which is equal to the level of the main electrode in a anticlockwise manner, the other group of electrodes is started by the main electrode, the adjacent electrode edge interval e is placed on the outer side of the scalp which is equal to the level of the main electrode in a clockwise manner, and the RS, PE and BR values are calculated and stored, wherein e is the length of a single electrode;
step seven, selecting a pair of symmetrical electrodes taking the main electrode and the auxiliary electrode as symmetry axes, and sequentially selecting the electrode pairs closest to the main electrode from the electrode pairs closest to the auxiliary electrode in a selection sequence;
Step eight, moving the selected electrode to the auxiliary electrode, wherein the moving step length is 2mm, calculating and reserving RS, PE and BR values after each movement, judging whether the RS values stored each time are larger than the RS values of basic imaging, if so, not performing other operations, and if not, deleting the position data of the movement and the RS, PE and BR values, then continuing to move, wherein the moving constraint condition is that the distance between the adjacent edges of any electrode cannot be smaller than e;
Step nine, screening the minimum value position among all the stored BR values, judging whether the PE value is the minimum value or less than 0.5mm when the current position is judged, if so, selecting the position as the current optimal electrode pair position, otherwise, deleting the position data, repeating the step, and screening the new BR minimum value position until the optimal electrode pair position is obtained;
And step ten, fixing the selected electrode pair to an optimal position, deleting the data stored when the electrode pair moves, repeating the steps seven to nine, selecting the electrode pair again and fixing the electrode pair to the optimal position until all the electrode pairs are fixed, and ending optimization.
Further defined, the number of electrodes n can range from 8, 10, 12, 14, 16 or 18.
The imaging is specifically defined by using measured potential information and known normal intra-brain conductivity distribution to obtain sensitivity of each part in the object to potential information change, namely Ag=b, wherein A is sensitivity, b is potential information, g is conductivity, using the sensitivity and the potential information obtained after internal conductivity change to obtain conductivity information, namely g=A -1 b, and coloring the obtained conductivity according to the value size to obtain the imaging.
Further defined, the pixel point is specifically to perform subdivision modeling on the brain region by using a finite element method, namely dividing the brain region into a finite number of small grids, solving the grid information for a Maxwell equation set corresponding to each small grid column, wherein each grid is a pixel point, and the more the pixel points are, the higher the resolution is, and the more accurate the solving is.
Aiming at the pathological changes of the parietal lobe and the temporal lobe, the invention has the advantages that non-reference electrodes are all arranged on the reference electrode side closest to the pathological change part so as to maximize the relative sensitivity of the pathological change area, and then the electrodes are respectively moved to the other reference electrode so as to meet the imaging requirement, and the imaging result is judged by using the fuzzy radius and the position deviation to determine the optimal electrode position. The method covers all possible positions of the electrode, provides conditions for high-precision imaging, optimizes imaging results of the high-probability position of the encephalopathy, can better judge the current illness state and visualizes the illness state.
Drawings
FIG. 1 is a schematic top view of the excitation mode, measurement mode, α1, α2, α3 partitions, and final electrode distribution optimized for the α1 region of the present invention.
Fig. 2 is a flow chart of the method of the present invention for monitoring electrode placement for parietal and temporal lesions.
FIG. 3 is a graph showing the comparison of the maximum relative sensitivity of the present invention to uniformly arranged electrodes in the α1, α2, and α3 zones.
Fig. 4 is an imaging comparison of the invention with uniformly arranged electrodes in six different lesions of the α1 region.
Fig. 5 is a bar graph comparing the blur radius of the present invention with that of uniformly arranged electrodes in six different lesions of the α1 region.
Detailed Description
The method for setting the monitoring electrode for the parietal and temporal lobe lesions is described in detail with reference to the accompanying drawings and examples.
The invention relates to a method for setting monitoring electrodes for parietal and temporal lesions, which aims to further optimize images of parietal and temporal lesions, since the top and temporal lobes are located in the middle of the head from the temple on both sides to the ear on both sides, the sensitivity of the uniform electrode arrangement is already high at this point, and the method is generally difficult to optimize. The invention utilizes the characteristic that the impedance change in the object can be displayed on the potential change of the electrode, and the sensitivity of a target area is maximized by compactly placing the electrode, and then the position of the electrode is changed according to the imaging quality. The adjacent measurement mode is excited relatively as shown in fig. 1, allowing the current to penetrate the skull. The right side of fig. 1 is the results of electrode optimization for the α1, α2, α3 partitions of the parietal and temporal lobe sites, and when lesions are in the α1 region. Wherein 1 is excitation current, 2 is measurement voltage, 3 is electrode, 4 is head forehead direction, 5 is head back pillow direction, 6 is left ear direction, 7 is right ear direction, 8 is plane one, and 9 is plane two.
The specific optimization steps are shown in the flow chart of fig. 2, and are divided into the following steps:
Under the conditions that a human body stands and the head is vertically upwards, respectively making a plane I and a plane II which are vertical to the ground, connecting temple on two sides of the cranium on the plane I, connecting the back of the left ear with the back of the right ear on the plane II, setting the area of the cranium between the plane I and the plane II as an area to be optimized, making a plane III which is vertical to the connecting line of the left ear and the right ear, and moving from the left ear to the right ear The intersection of the area swept during the movement and the area to be optimized is an alpha 1 area, and the plane three-right ear is continuously movedThe intersection of the area swept during the movement and the area to be optimized is an alpha 2 area, and the plane three-right ear is moved continuouslyThe intersection of the area swept in the moving process and the area to be optimized is an alpha 3 area, wherein c is the length of a line segment of a left ear-to-right ear connecting line;
Respectively placing one electrode as a reference electrode to be fixed on the position, which is 6cm away from the front position, of the right ear and the front position of the left ear of the patient, and placing the rest electrodes at intervals on a horizontal plane parallel to the ground where the reference electrode is positioned Is placed around the head of the patient. Where D is the circumference of the patient's head and n is the number of electrodes, which number n ranges from 8, 10, 12, 14, 16 or 18.
Step three, adopting a relative excitation mode, collecting boundary voltage, and performing basic imaging;
The relative excitation mode is to select any electrode as excitation electrode to inject excitation current, and select counter-clockwise interval with the excitation electrode The electrode of each electrode is grounded as a grounding electrode, after potential information on the electrode except the exciting electrode and the grounding electrode is obtained, the next electrode is selected anticlockwise as the exciting electrode, and the grounding electrode still keeps anticlockwise interval with the new exciting electrodeThe electrodes are used for finishing excitation until all the electrodes are selected as excitation electrodes and potential information on the rest electrodes is obtained;
the imaging specifically comprises the steps of obtaining sensitivity of each part in the object to potential information change, namely Ag=b, by utilizing measured potential information and known normal brain conductivity distribution, wherein A is sensitivity, b is potential information, g is conductivity, obtaining conductivity information, namely g=A -1 b by utilizing the sensitivity and the potential information obtained after the internal conductivity change, and coloring the obtained conductivity according to the value size to obtain the imaging;
Judging the current lesion position according to basic imaging, and calculating and reserving relative sensitivity RS, position offset PE and blur radius BR;
Wherein S αi represents the pixel sensitivity value in the alpha i region, S represents the pixel sensitivity value of the whole brain region, and the value range of i is 1 or 3;
x t、Yt represents the X-axis coordinate and Y-axis coordinate of the pixel point with the conductivity greater than or equal to 50% of the maximum conductivity in all the pixel points of the reconstructed image, P represents the number of the pixel points with the conductivity greater than or equal to 50% of the maximum conductivity in all the pixel points of the reconstructed image, and X, Y represents the X-axis coordinate and Y-axis coordinate of the geometric center of the lesion on the basic imaging image;
R t represents the radius of a lesion part, A t represents the area of the lesion part, R represents the radius of the whole imaging area, A represents the area of the whole imaging area, BR value represents the accuracy of the reconstructed image, and BR value is smaller, the more accurate the imaging target is, and the fewer artifacts are;
The pixel points are specifically formed by carrying out subdivision modeling on the brain region by utilizing a finite element method, namely dividing the brain region into a finite number of small grids, solving the grid information for a Maxwell equation set corresponding to each small grid column, wherein each grid is a pixel point, and the more the pixel points are, the higher the resolution is, and the more accurate the solving is;
Step five, judging whether the pathological change position of the image is in an alpha 2 area, namely in the geometric center position of the brain, if so, ensuring enough current penetration effect, and if not, entering step six, wherein the electrode position is not adjusted and all the steps are finished;
Step six, two reference electrodes are fixed, the reference electrode closest to the lesion area is defined as a main electrode, the other reference electrode is an auxiliary electrode, all electrodes except the main electrode and the auxiliary electrode are equally divided into two groups, one group is started by the main electrode, the adjacent electrode edge interval e is placed on the outer side of the scalp which is equal to the level of the main electrode in a anticlockwise manner, the other group of electrodes is started by the main electrode, the adjacent electrode edge interval e is placed on the outer side of the scalp which is equal to the level of the main electrode in a clockwise manner, and the RS, PE and BR values are calculated and stored, wherein e is the length of a single electrode;
step seven, selecting a pair of symmetrical electrodes taking the main electrode and the auxiliary electrode as symmetry axes, and sequentially selecting the electrode pairs closest to the main electrode from the electrode pairs closest to the auxiliary electrode in a selection sequence;
Step eight, moving the selected electrode to the auxiliary electrode, wherein the moving step length is 2mm, calculating and reserving RS, PE and BR values after each movement, judging whether the RS values stored each time are larger than the RS values of basic imaging, if so, not performing other operations, and if not, deleting the position data of the movement and the RS, PE and BR values, then continuing to move, wherein the moving constraint condition is that the distance between the adjacent edges of any electrode cannot be smaller than e;
Step nine, screening the minimum value position among all the stored BR values, judging whether the PE value is the minimum value or less than 0.5mm when the current position is judged, if so, selecting the position as the current optimal electrode pair position, otherwise, deleting the position data, repeating the step, and screening the new BR minimum value position until the optimal electrode pair position is obtained;
And step ten, fixing the selected electrode pair to an optimal position, deleting the data stored when the electrode pair moves, repeating the steps seven to nine, selecting the electrode pair again and fixing the electrode pair to the optimal position until all the electrode pairs are fixed, and ending optimization.
As shown in FIG. 3, for the optimal relative sensitivity of the invention and the uniformly arranged electrodes in the alpha 1, alpha 2 and alpha 3 regions, the invention has obvious numerical advantages in the alpha 1 and alpha 3 regions, and the electrodes arranged by the method can be proved to be capable of effectively improving the relative sensitivity.
The imaging effect of six different lesions in the α1 region is shown in fig. 4, which includes three bleeding sites, and three bleeding sites with secondary ischemia, with reference to the actual human tissue parameters, the brain background conductivity is 0.15S/m for human cerebral cerebrospinal fluid conductivity. The bleeding conductivity was set to 0.8S/m (all on the left), and the ischemia conductivity was set to 0.06S/m (all on the right), it can be seen that imaging of the second row of uniform electrode arrangements in this region had better imaging quality, but there was some deformation and bias of the imaging near the edge and with secondary ischemia. The third line of the invention can form images with better imaging quality at all positions without obvious deformation, and has better guiding effect on the judgment and treatment of the illness state.
The BR values for the six different lesions are compared as shown in fig. 5. The BR values of the invention under the condition of different lesions at each position are smaller and stable, only have a certain increase in F, but still are smaller than the BR values of the uniformly arranged electrodes, so that the optimized electrode arrangement can well improve the relative sensitivity of the region to be optimized, thereby improving the imaging quality and better judging the current lesion condition.
The foregoing description of the preferred embodiments of the invention is not intended to be limiting, but rather to enable any modification, equivalent replacement, improvement or the like to be made within the spirit and principles of the invention.
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| CN111616708A (en) * | 2020-05-25 | 2020-09-04 | 中国人民解放军第四军医大学 | An image reconstruction method for accurate identification of intracranial lesions in stroke |
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