Method to calibrate diagnostic measurement device

FIELD: measurement equipment.

SUBSTANCE: invention relates to facilities of calibration of measurement devices of biological signals. The method of processing of measured values of the diagnostic measurement device consists in the fact that the measurement device generates some measured values, which may be represented as n-dimensional vectors, where n takes the value at least equal to 2. During realisation of the method they set a search area for a rest interval contained in this area, at the same time the search area is the area, where there is the area of insignificant physiological or biological activity that is justified from the physiological point of view, besides, the rest interval and the medium vector arranged in this interval are determined by vectors of measured values produced in the search area, at the same time the medium vector is determined as the basis vector for calibration of the measurement device. The device for measurement of biological signals has facilities for realisation of the method.

EFFECT: usage of the invention makes it possible to increase validity of measurements.

13 cl, 2 dwg.

 

This invention relates to a method of calibrating a diagnostic measuring device for biological signals, which can be represented as n-dimensional vectors. In medical diagnostics such measuring devices are known, for example, in electroencephalography and in all areas cardiography, vector cardiography and cardiopoietic.

Such measuring tools and their diagnostic value based on, for example, on measuring the electrical activity of the body, and the activity in healthy and unhealthy condition differs. In the case of heart cardiography based on the electric field generated by flowing through the cell membrane of cardiac muscle. (Total) vector that is created by the heart of the field varies in time as the largest, and its spatial orientation. Cardiac cycle, i.e. passing an electric process with each heart beat can be divided into different parts. Classic electrocardiogram wave R corresponds to the excitation of the Atria, the R-wave - ventricular depolarization and spike T - repolarization of the ventricles.

If cardiopoietic described in patent document EP 0086429 to measure the magnitude of the potentials and their spatial orientation using four located near the heart of thoracic e is ctrada, registered cardiac currents in four mutually perpendicular projections. In the patent document EP 1'048'000 disclosed further development of this idea, which leads to carried out with the help of computer mathematical analysis with the aim of better understanding and interpretation of measurement results.

For example, if the spatial representation of the vector cardiography or cardiopoietic above the teeth of the P, R and T are in the form of vector loops P, R, and So These vector loops represent the path, which takes place during the heart beat of the end of the vector created by the heart electric field. Over time the total vector created by the heart electric field takes place in three-dimensional space in three loops. The beginning of the resultant vector can be thought of as the beginning of the coordinate system for this space. This is the origin of coordinates must be defined as depending on the choice of origin yield different measurements.

On the one hand, the origin of coordinates should correspond to physiologically reasonable zero, on the other hand, it should be possible to reliably identify it, despite the variability in the activity of cardiac muscle due to individual differences, the degree of load, health is so In addition, should be filtered out various noises, for example, bias voltage. Given the above, it is clear that to find in such physiological system reliable origin as a reference point for calibration of the measuring device is difficult.

In this regard, the objective of the invention is to provide such a method of calibrating a diagnostic measuring device for the representation of biological signals, in particular biological potentials, in the form of n-dimensional vectors, due to which these problems in finding reliable and reasonable from the biological point of view the origin, can be overcome. This problem is solved by the method defined in the independent claim. Dependent claims define preferred embodiments of the invention.

The method suggested diagnostic measuring device relates to measuring devices, generating a number of measured values that can be represented as n-dimensional vectors, where n takes a value at least equal to 2. Define the scope of the search is contained in this interval of rest. The search area is defined as the area in which the search interval of rest. The interval of rest - this is the interval, in which the vector is changed slightly. This interval of rest and placed in it the average vector is determined by the measurement data obtained in the search area. The average vector in the interval of rest is defined as a vector basis for calibration of the measuring device.

In this description, the term "diagnostic measuring device" includes not only the measuring device for the diagnosis, but measuring device for all fields of medicine and veterinary medicine, in particular including measuring devices used in therapeutic and surgical applications.

The basic idea of the invention is to determine the initial vector or point of reference (basis vector) for calibration of the measuring device as the average vector, which is located preferably in the center of the time interval, called the "rest interval" in which the module of the vector is changed slightly. This interval of peace may lie in biologically based resting phase, for example in the resting phase recurring physiological cycle, as in the case of the above heartbeat. However, the interval of rest can also correspond to the resting phase of the signal, set purely empirically; to know when this causal relationships related to this rest phase, not necessarily. In the case of empirical what about the definition of the rest phase define the temporal scope of the search interval of peace, which contains empirically determined and/or physiologically based resting phase for the output signal. Although in order to find the interval of rest, you can view and the whole time interval measurement.

As a measure of signal changes, for example, is the change of the measured value per unit of time. In the most General case, determine the measure of how much of the measured values deviate from the average value in a relatively short time interval. As such measures can be used, for example, the arithmetic mean values, variances, and the variance or standard deviation, or other appropriate mathematical measure of the average deviation. In the following text, the term "change in the measured values generally used for any appropriate measure of the average deviation from the mean.

Empirical determination of the rest phase change of the measured values in the time interval Delta is compared with the change in the measured values in other time intervals and the time interval with a minimum change in the measured values is defined as the interval of rest. Time intervals Delta can choose as a "sliding window" or as overlapping or separate time intervals Delta around the selected points of measurement over time is serenia. Depending on the application to perform the criterion of "rest interval" to changes in the measured values over a time interval Delta have different requirements. Such criteria, for example, are the following criteria: average deviation (arithmetic mean values, variance, standard deviation, variance, and so on) from the mean in the comparison time interval for the measured values in the interval of peace is one third, preferably not more than half of the average deviation in the comparative periods of time out of the rest phase and very preferably at least an order of magnitude smaller than the average variation in the comparative periods of time out of the rest phase.

Of course, specialist meaningfully ask comparative intervals or sliding Windows so that they approximately match the expected value of the rest phase, in order not to average each other the rest phase and the active phase. The duration of the comparison interval of time is usually chosen so that they contain several periods characteristic fluctuations of the signal, but was a maximum of a small portion (for example, not more than 1/10 or 1/20) of the total cycle. For example, in the case of cardiochiles comparative intervals of time preferably ranges from 5 to 100 MS, preferably about is 10 to 50 MS, particularly preferably from 15 to 30 MS, for example 20 MS. In the General case (i.e. not only on cardiochiles) periods characteristic fluctuations of the signal can determine, for example, using the Fourier transform (the required period corresponds to the reciprocal of the frequency at which the frequency Fourier spectrum has a maximum), often the expert is able to determine the comparative length of the time intervals on the eye better than is possible using a mathematical algorithm.

The search scope can cover the entire period of measurement, that is, for example, the values measured for at least one full cycle of the signal, or only a portion of the measuring period. In addition, this method can make for finding a interval of peace, first in longer time intervals, and then to repeat it in the identified interval of peace, with increasing refinement of this method allows the identification of the point of rest.

Thus, in accordance with the preferred embodiment of the invention, the interval of peace can be found in any search containing the resting phase. It applies to the case when the search includes the entire period of measurement, and the occasion when it embodies only a part of the measuring period.

According to another preferred variant implementation is tvline the scope of the search interval of rest does not cover all the measurement time, and limited time interval, which is located within the entire measurement time and reasonable from the biological point of view. Biologically-based search can determine, for example, by empirical data showing the phase of physiological rest, and/or on the basis of knowledge about the flow of the investigated physiological process, especially those phases, when physiological activity is absent or minimal. This restriction of the search area indicates the interval of rest with a minimum change in the measured signal and the average vector in the center of the interval of rest in the phase of physiological rest.

A great advantage of this method of calibration of the measuring instrument is that it is applicable for all records of biological signals that can be represented as n-dimensional vectors, for example in the form of two - or three-dimensional vectors or multi-tuples of n elements representing the measured value at a specific point in time. As an example, multi-channel application here can be called a 12-channel electrocardiograph. In vector cardiography total vector of the electric field created by cardiac muscle, present in the form of three-dimensional vector.

The following example cardiography, in particular, vector cardiography, detail op is described a method of calibrating the measuring device, but this does not mean that the invention is limited to use in cardiography.

The origin of coordinates, which physiologically justified and therefore ideal as a reference point for calibration of the device for measuring electrical activity of the heart, is located at the point with the lowest possible electrical potential, after all the excitement has died down and the new one began. Accordingly origin, which satisfies this condition and is the reference point for calibration is defined as the isoelectric zero point. If this is the origin of coordinates coincides with the isoelectric zero point, then theoretically the dimension of the vector created by the heart of the electric field in the resting phase would give a potential of 0 volts in all leads. Of course, as mentioned above, measured in leads potentials distorted noise in the measuring system, so that exactly 0 volts all the leads do not measure never, even at the time of measurement, when there is absolutely isoelectric potential. Using the proposed method the origin as the reference point for calibration can be defined so that it better corresponds to the isoelectric point. This means that every time a potential of 0 V in the measurement data with the best approximation is shown when the phone is actually there is the resting potential.

During the cardiac cycle, the vector created by the heart of the electric field in each case approaches theoretically defined isoelectric point during a few short resting phases, in particular during the phases after excitation of the Atria (the prong P) and before the depolarization of the ventricles (R-wave), that is, shortly before the so-called point Z, and after depolarization and before repolarization of the ventricles (the T wave) in the so-called point J and again after repolarization of the ventricles and before excitation of the Atria when the next blow. The most important factor for determining the isoelectric zero point is the resting phase before the depolarization of the ventricles (R-wave), because at this time the spread of electrical activity in the AV node does not occur, and therefore, the point Z is not yet reached, the action potentials of the cells of the ventricles of the heart while not occur, and repolarization in the cells of the Atria is not yet started.

In addition, at the heart of this invention lies in the observation that was made during the examination of records alone for approximately 1,000 patients: almost all records changes of potential patients there is a significant time interval between the excitation of the Atria (the prong P loop P) and depolarization of the ventricles (the R-wave loop R), during which the measured vecto created heart electric field does not change almost. So, a few measurement points in all derivations give each other constant values, which in this time interval fluctuant around an imaginary center. Thus, this time interval with isoelectric potential corresponds to the resting phase with minimal change vector, depending on the patient usually lasts from 20 to 80 MS or even more.

Furthermore, since in accordance with the foregoing, the physiology of the heart determines such a resting phase before depolarization, in preferred variants of the proposed method the search area is chosen so that it included this resting phase, but was not extended for the duration of the heart beat. For example, this area extends from the maximum potential for excitation of the Atria to the maximum depolarization of the ventricles. However, you can choose a smaller search area, provided that it is guaranteed to include the resting phase. So, within a certain search area based on the source data by the numerical method determines the interval of peace and located in the center of the average vector as the initial or base vector. This approach ensures that the origin as the reference point for calibration enters the phase of physiological rest before depolarization of the ventricles (the R-wave loop R) and max is the maximum possible approximation corresponds to the isoelectric point.

Another advantage of this method when used in cardiology is that reasonable from a physiological point of view the origin as the reference point for calibration can determine even if, as occurs in some patients, the resting phase before the depolarization of the ventricles does not last long. Using a numerical method such as the method described for example below, determine the origin of coordinates, in which the change vector in time is the lowest rate, that is the most calm. Therefore, this method is a little error prone. Should only be performed a minimum requirement: the R-wave of the kick is clearly localized, with sufficient even approximate, yet inaccurate localization.

Another advantage of the proposed method is used in the calculation of the origin as a point of reference, in addition, invariant to rotation and transfer of measured values. This calculation can be applied directly to the measured raw counts, and filtered or smoothed, or averaged measurements, in all cases it gives equally good results.

The proposed method is also suitable for the calibration of measuring devices used in cardiology, for example, in electroencephalography, Claiborne electrical activity of the brain, moreover, in accordance with the foregoing, the scope of the search origin as the reference point, respectively, should choose so that it could expect in the physiological ratio of the interval of rest. Additional applications of the proposed method are related to the calibration of measuring devices for other biological processes, such as hormonal or other chemical or physical processes, which collect data measurements made during a certain time interval, and correlate them with the reference point.

Another aspect of the invention relates to a measuring device that measures a biological signal, such as potentials, and has means for implementing the above method. The measuring device in the preferred embodiment, using electrodes to measure changes in potential of the body of man or animal, such as the heart or brain, for example, on the surface of the body, and the signals assign and register, process and record the data quality measurements using instruments or components of instruments, known from the existing art. These devices or components of devices have means for applying the proposed method of calibration of the measuring instrument. This means that before the final performance is the pressure measurement data to correct them on the absolute value of a proposed method of the base vector. Means for applying the proposed method, for example, may be a programming device or component of a device or software component.

Below using the following drawings are described in more detail embodiments of the proposed method.

Fig.1. An enlarged fragment of the spatial recording of the heart beat, which shows the vector loop and fixed beams of vectors in a vector cardiogram.

Fig.2. A block diagram of an exemplary method for determining the origin as the reference point for calibration in accordance with isoelectric zero point as the geometric centre of the fixed beam vectors.

Fig.1 refers to the application of the method in the measuring device for the vector cardiography. This drawing shows an enlarged fragment of spatial representation of the potentials resulting from cardiac activity, and for each time t was defined as the vector created by the heart electric field. Vector cardiogram shows a connecting line between the ends of these vectors, from one measurement to the next measurement. With each cardiac cycle creates several distinctive loops, which are interrupted by phases in which the vector (i.e. the intensity and spatial orientation elektricheska the field) remains relatively constant. In Fig.1 this resting phase is displayed in the form of a bundle of short lines (that is, the connecting lines from vector to vector), which is almost omnidirectional moving around the centre On (indicated by the long arrow) or only fluctuant in microvoltage range. Before discussed here resting phase before the loop R the vector moves, moving from loop P (indicated by eight short arrows) in this "fixed beam", and after this rest phase he comes out of the beam and leaves the origin very quickly and at a great distance, to a high speed pass loop R (reference sign R1marked emanating from the origin part of the hinge R). This drawing also shows the end of the loop R (R2and the next loop T (indicated by dots). Isoelectric zero point O is located at the geometric center of the beam before the loop R, the origin is set at the isoelectric point. Three orthogonal axes a, a' and a” determining three-dimensional space, in accordance with the definition intersect at the origin. Along the dotted loops spear arrow Z shows how the vector field is developing in this space in time.

The proposed method of calibration of a diagnostic device for measuring biological potentials can be applied all the way to the x recording potentials of cardiac activity, for example, including electrocardiography, shown in this drawing, the embodiment of the three-dimensional records, he is not limited.

In Fig.2 shows a block diagram of an exemplary method of calibrating a measurement device for vector cardiography, in which the origin as the reference point for calibration is defined as the geometric center of the fixed beam vectors.

For calibration cardiographic measuring device first from the original data of the cardiac cycle define the temporal scope of the search, in which you must find the interval of rest. The search area should be wide enough so that it contains the phase of physiological rest and stretched to the maximum of the maximum potential excitation of the Atria (peak loop P) up to a maximum potential of ventricular depolarization (peak loop R). However, you can choose a smaller area of search, because it is guaranteed that it covers the interval of rest.

Then in the search area selects multiple points in time txwhere x=1 ... n. Time intervals Delta around these moments of time txaccording to the measurements vector signal by the numerical method to determine the initial vector and use it for calibration as the base vector.

A possible variant of such a numerical definition can about motivate, for example, steps a)-d).

a) Determine the time at Delta around each of the selected points in time txwhere x=1 ... n, with multiple points of measurement in the time interval Delta (from time tx-delta/2 until tx+delta/2, etc), and for each of these time points define the module of the vector, which describes the created heart muscle field. Calculate the average module of the vector in the time interval from tx-delta/2 to tx+delta/2 by adding modules of all vectors and subsequent division by the number of vectors. The result is the average module of the vector in the time interval Delta around time tx. This module is the mean vector is determined in the search area for each time interval Delta around each point in time txwhere x=1 ... n.

b) Calculate the average deviation of all modules of the vectors in the time interval from tx-delta/2 to tx+delta/2 no calculated during step a) the average vector, the latter is subtracted from each of the individual vectors that are defined for all points of measurement, and in each case determine the module resulting difference vector. Then these modules are again summed and divided by the number of summed modules. The result represents the average deviation of these vectors from the mean is the sector, calculated in process step a). This average deviation is a measure of the average speed with which the selected vectors are moved in the time interval from tx-delta/2 to tx+delta/2. This is the average deviation and the speed is calculated for each time interval Delta around each point in time txin the search pane.

c) In all search scopes compare the average velocity vectors (calculated in process step b)) at each measurement point and determine the time interval Delta with the lowest average speed vectors. This time interval Delta is the desired interval of peace located in the center measuring point tx.

d) For this measurement point is in the center of the time interval of calm define calculated in process step a) the mean vector located around this point of the time interval from t-delta/2 to t+delta/2. This vector represents the initial vector, which displays the resting potential in the measurement and is used as the base vector for calibration of the measuring device.

By the way, in which use is described in this example, the numerical definition, the invention is not limited. Depending on the application in mind can take, for example, the following options are - by themselves or, if possible, in combination.

- Failure on the select search scope, averaging instead of the whole area.

- Determination of the dispersion or standard deviation at each time interval instead of the formation of the arithmetic mean of the differences.

Weighted averaging, for example, due to the fact that the points located farther from the point of time tx, are taken into account to a greater or lesser extent.

In process step d) selecting another characteristic vector, for example, by selecting instead of the average values of a certain measured value (assuming that, with some minor changes of the measured value in the interval of peace representative is even a separate measured value).

- Select the interval rest interval of time that is not identical to the time interval tx. For example, you can choose the time interval that contains only the Central part of a time interval, and to calculate it mean, especially if you choose a relatively large time intervals. On the other hand, can also choose a large area, fully containing the time interval, for example, if the interval of peace, as expected, lies in the large relatively quiet time interval.

The initial module of the vector defined in this method as the mean vector of fixed beam vectors, in practice, according to which there is a difference between the measured potential in the resting phase and isoelectric zero point, therefore, when calibrating it can be applied as a correction of zero, appropriate and reasonable from a biological point of view.

As is known to the specialist, calibration or zero correction can be implemented in different ways. In one embodiment of the proposed method the initial or baseline vector is subtracted from the vector of all measured values of the cardiac cycle or the entire measurement period. In other embodiments, implementation of the first count initial vectors of several heartbeats, then average them, and the average initial vector is subtracted from each vector measured values. Of course, the zero can perform and represent graphically. For example, following one after the other starting vectors can connect direct or other suitable line, such as a spline curve or approximating curve specified by the numerical method.

Another preferred application of the definition of the zero point is the calculation of a point z Point Z in cardiology call time starts when the depolarization of the ventricles. In accordance with this definition, this point defines the beginning of the R-wave or loop R Point Z is not identical isoelectric point, it is located immediately after the last, and therefore, its potential should not correctiva the change to the potential of 0 volts. Time point set Z where the vector in the spatial relationship finally comes out of the beam, reflecting the resting phase to pass through the loop R. accordingly, this point usually lies near the isoelectric zero point, and it may lie inside or outside the interval of rest.

After finding the origin that best fits isoelectric point, similarly also can easily find the point Z. for this purpose, define the temporal scope of the search, in which you must find the point Z. the search Area should be wide enough so that it contains the point Z and stretched from the point in time with the lowest average speed vector to the point where the module of the vector away from the isoelectric zero point on the value of Epsilon and again does not fit it closer to the maximum of the R-wave Magnitude Epsilon can be defined microvolt, it should have a small value.

Of course, this method can also define any other point during the cardiac cycle, because they can represent the dependence of a point from the zero point. Of course, such an application of the proposed method can be applied to the measurement of other biological processes.

1. The method of processing measured values of the diagnostic measurement of the mouth of the STS, wherein the measuring device generates a number of measured values that can be represented as n-dimensional vectors, where n takes a value at least equal to 2, characterized in that the said method is used for calibration of the mentioned diagnostic measuring device, and in the way set the search scope to be contained in this interval of peace, at the same time as the search area select the area that contains reasonable from a physiological point of view, the area of minor physiological or biological activity, moreover, the interval of peace and located in this interval the mean vector is determined by the vectors obtained in the search area of the measured values, while this average vector is defined as a vector basis for calibration of the measuring device.

2. The method according to p. 1, wherein the search area corresponds to the average value of multiple repetitive sequences of measured values.

3. The method according to any of paragraphs.1-2, characterized in that in the search area determined time interval with a minimum change in the measured values and determine the interval of rest so that he, at least partially contains the time interval with a minimum change in the measured values.

4. The method according to l is the Bohm PP.1-2, characterized in that as a temporary area search plot of calm define a limited phase during the whole period of measurements.

5. The method according to any of paragraphs.1-2, characterized in that the measuring device provides the possibility of recording the electrical activity of the heart muscle.

6. The method according to p. 5, characterized in that the temporal scope of the search reasonable from a physiological point of view of the rest interval goes from maximum potential with the excitation of the Atria to the maximum potential during depolarization of the ventricles during the cardiac cycle.

7. The method according to any of paragraphs.1-2 or 6, which use a vector basis for calibration of the measuring device, and the basis vector is subtracted from the vectors mentioned measured values.

8. The method according to any of paragraphs.1-2 or 6, characterized in that the baseline vector for calibration using a numerical method, wherein in the search area containing a few selected moments of time, perform at least the following four steps:
a) calculating the average vector in the time interval Delta around each selected in the search area of the time;
b) calculate the mean deviation of all the vectors from the mean vector in the time interval Delta;
c) determination of the rest interval as a time interval of deltas the smallest average deviation of all the vectors from the average value;
d) determining an average vector in the time interval defined as the interval of rest, as the base vector.

9. The method according to p. 8, characterized in that from a number of measured values generated by the diagnostic measuring device, determine at least one characteristic point of measurement, and to determine a characteristic of the measurement point as a reference point, use the previously defined basic vector.

10. The method according to p. 9, characterized in that the characteristic measurement point represents a point Z, and the point Z is defined as the first located at the origin of coordinates measured value, the module is in the coordinate system with base vectors as the origin of coordinates corresponds to at least limit the value of Epsilon, below which it does not fall.

11. Device for measuring biological signals, characterized in that at least one component of the device has means for implementing the method according to any one of paragraphs. 1-10.

12. The device according to p. 11 for measuring biological signals, and the signals are the potentials, and the device has at least two electrodes and the device or components of the instrument for recording measured values in accordance with the signals from the electrodes and for processing the measured C is acini and presenting the processed measured values.

13. The device according to p. 12, characterized in that it is a device for cardiography or cardiopoietic.



 

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1 ex

FIELD: medicine.

SUBSTANCE: psychophysiological response is recorded in the course of executing attention and coordination motility tasks. The hands coordination motility is implemented by approaching similar poles of two permanent magnets at a specified distance as a part of a device, which comprises a passive part with a permanent magnet for the left hand, and an active part with a permanent magnet for the right hand. The permanent magnets in the passive and active parts are arranged with their similar poles to each other. The device also comprises a spring-loaded element for recording a distance of the parts. When performing the tasks, the person being tested overcomes magnetic resistance, approaches the active and passive parts of the device so that an electronic processing assembly forms a time interval in the process of which the person being tested positions the parts of the device accurately. When performing the task, the accurate positioning time to the total experiment time relation is derived.

EFFECT: method enables controlling the individual's psychophysiological state and assessing the reliability of the responses by operating the compact device.

2 dwg

FIELD: medicine.

SUBSTANCE: heart rate variability is assessed. The assessment procedure involves 24-hour Holter monitoring on the 21st day from the moment of the ischemic stroke occurred. And if observing brady-arrhythmias presented by degree 2-3 atrio-ventricular block or degree 2-3 sinoatrial block and sinus pauses of more than 2 sec long, a high risk of cardiovascular fatal complications following the ischemic stroke is predicted.

EFFECT: method provides the high informative and flexible prediction of the risk of cardiovascular fatal complications following the ischemic stroke in the patients with cerebrovascular, cardiac, endocrine comorbidities.

3 tbl, 3 ex

FIELD: medicine.

SUBSTANCE: invention refers to medicine and can be used in labour hygiene and occupational health problems. A digital camera is fixed on a driver's head in front of his eyes and a blinding light source. Crossing coordinates of a display plane and straight lines connecting an eye centre with each blinding source are determined. Blackout areas comparably sized with a head lamp light of the oncoming car are displayed. A maximum contrast negative image of the blinding light sources read out from the camera is presented on a transparent display.

EFFECT: method provides the more effective driver's eyes protection if blinded by the light of the oncoming car that is ensured by displaying the maximum contrast negative image of the segments corresponding to the blinding head lamp light.

4 cl, 2 dwg

FIELD: medicine.

SUBSTANCE: group of inventions refers to medicine and medical equipment. A distance of the upper to lower eyelids of at least one eye is measured over a period of time, Eye openness coefficients varying within the value of wide open eye, through the value of partially open eye to the value of completely closed eye are determined. The eye openness coefficients are graphed. The eye openness coefficients variations over the period of time are compared to a reference eye closure model indicating the microsleep cases. Besides, the method is implemented according to the version, which provides notifying an operator if the microsleep has been detected, by signalling. The method is also implemented by comparing the microsleep models with the eye openness coefficients variations as shown by EEG and EOG. That is ensured by using a device comprising an infrared emitter, which is connected to an image selector. A microprocessor with an electronic procedure of microsleep detection configured to detect face, eyes and eyelids images in a digital image and to calculate the eye openness coefficient with determining a microsleep-specific coefficient, and presenting the obtained information in the form of graphical presentation of the eye openness coefficients at the selected moments of time. A memory unit connected to the microprocess and comprising the reference eye closure models to be compared to the eye openness coefficients at the selected moments of time.

EFFECT: invention enables providing the more reliable assessment of microsleep that is ensured by microsleep detection at the early stages of falling asleep.

28 cl, 6 dwg

FIELD: medicine.

SUBSTANCE: group of inventions refers to medicine and medical equipment. A distance of the upper to lower eyelids of at least one eye is measured over a period of time, Eye openness coefficients varying within the value of wide open eye, through the value of partially open eye to the value of completely closed eye are determined. The eye openness coefficients are graphed. The eye openness coefficients variations over the period of time are compared to a reference eye closure model indicating the microsleep cases. Besides, the method is implemented according to the version, which provides notifying an operator if the microsleep has been detected, by signalling. The method is also implemented by comparing the microsleep models with the eye openness coefficients variations as shown by EEG and EOG. That is ensured by using a device comprising an infrared emitter, which is connected to an image selector. A microprocessor with an electronic procedure of microsleep detection configured to detect face, eyes and eyelids images in a digital image and to calculate the eye openness coefficient with determining a microsleep-specific coefficient, and presenting the obtained information in the form of graphical presentation of the eye openness coefficients at the selected moments of time. A memory unit connected to the microprocess and comprising the reference eye closure models to be compared to the eye openness coefficients at the selected moments of time.

EFFECT: invention enables providing the more reliable assessment of microsleep that is ensured by microsleep detection at the early stages of falling asleep.

28 cl, 6 dwg

FIELD: medicine.

SUBSTANCE: electric cardio signal recorder in free motion activity comprises an amplifier (1), an analogue-to-digital converter with a multiplex switch (2) and series decomposition unit (3), second arithmetical-logical unit (4), an arithmetic unit (5), an increment code analyser (6), a switchover unit (7) and a digital modem (8), as well as a control unit (9), first (12) and second (10) memory units, an increment code counter (11). A second output of the second arithmetical-logical unit (4) is connected to a first input of a decomposition unit (3); an output of the second memory unit (10) is connected to a second output of the second arithmetical-logical unit (4); a second output of the increment code analyser (6) is connected to a first input of the first memory unit (12), while a third output - to a first input of the increment code counter (11), an output of which is connected to a second input of the first memory unit (12) an output of which us connected to an second input of the switchover unit (7); first, second, third, fourth, fifth and sixth outputs of the control unit (9) are connected respectively to a first input of the analogue-to-digital converter with the multiplex switch (2), a second input of the decomposition unit (3), an input of the second memory unit (10), a third input of the second arithmetical-logical unit (4), a second input of the increment code counter (11) and a third input of the switchover unit (7). The device also comprises an electrode break detector (13) and a heart critical state detector (14). The amplifier (1), the electrode break detector (13), the analogue-to-digital converter with the multiplex switch (2), the heart critical state detector (14) and the decomposition unit (3) are series connected. A seventh output of the control unit (9) is connected to a fourth input of the switchover unit (7); a second output (17) of the electrode break detector (13) is connected to a first input of the control unit (9), a second input of which is connected to a second output (24) of the heart critical state detector (14), and a second output of the second memory unit (10) is connected to a second input (22) of the heart critical state detector (14).

EFFECT: using the invention enables enhancement by detecting the electrode break and the heart critical state in free motion activity.

3 cl, 12 dwg

FIELD: medicine.

SUBSTANCE: invention relates to medicine, namely to surgery and gastroenterology. Registration of sound effects from front abdominal wall is performed. Density of spectrum power in the range of low (D1) and high (D2) frequencies: 200-450 Hz and 450-700 Hz in children at the age of 7-9 years, 100-350 Hz and 350-600 Hz in 10-12 year old children, 100-350 Hz and 350-600 Hz in 13-15 year old children is determined. Ratio of density values (C), obtained at low frequencies to values at high frequencies is calculated. In evaluation of results coefficients depending on child's age (Cav) are applied: 7-9 years Cav - 1.11, 10-12 years Cav - 1.00, 13-15 years Cav - 1.01. Obtained values C larger than Cav testify to predominance of large intestine sounds; C less than Cav - about predominance of small intestine sounds.

EFFECT: method extends arsenal of means for evaluation of motor-evacuation function of intestine, which is reached due to spectral analysis of spectrum power density at low and high frequencies with taking into account child's age peculiarities.

4 dwg, 2 ex, 1 tbl

FIELD: medicine.

SUBSTANCE: invention relates to medicine, namely to paediatric cardiology and paediatric infectious diseases, and can be used for evaluation of indications for cardiometabolic therapy in case of infectious affection of myocardium in children. For this purpose quantitative evaluation of clinical, electrocardiographic, biochemical and echocardiographic indices is determined and realised. As clinical indices auscultative symptomatic: sonority of tones, presence of noises, parameters of arterial pressure are evaluated. As biochemical indices evaluated are: activity of cardiospeciphic enzymes: MB-fraction of creatine phosphokinase, α-hydroxybutyrate dehydrogenase, aspartic transaminase, alanine transaminase and cardiospecific troponin I protein. Echocardiographic examination is realised with application of Dopplerography for evaluation of diastolic ventricular function. Each of indices is evaluated by from 1 to 3 points. Points are summed up and obtained result is used to evaluate indications for cardiometabolic therapy. If the total sum is lower than 3 points, cardiometabolic therapy is not indicated. If the total sum is from 3 points to 7 point including, peroral introduction of cardiometabolic preparations is carried out. If the total sum is from 8 points and higher, parenteral introduction of cardiometabolic preparations is realised.

EFFECT: method provides possibility of determining presence of indications to administering cardiometabolic therapy objectively in minimal terms, including situations, when part of results of additional examination is absent because of some reasons, and of evaluating its efficiency in differential way.

1 tbl, 4 ex

FIELD: medicine.

SUBSTANCE: pulse electric activity of sensorimotor central neurons is recorded in experimental animals adapted to hypoxia. The recorded activity frequency is modulated by a multivibrator and an electroacoustic transducer; the signals are copied and transferred onto a carrier. The patient is exposed to distant acoustic signals with the use of the laser generator. The exposure is sequential and starts with sessions at frequency 5-8 Hz for 5-7 minutes and follows with sessions at frequency 10-15 Hz for 5-8 minutes. The sessions are daily, one session a day; the therapeutic course is 10-14 sessions.

EFFECT: method enables using the drug-free modalities and normalise the blood pressure that is ensured by providing the mode and sequence of acoustic signal flow.

2 tbl, 3 ex

FIELD: medicine.

SUBSTANCE: method involves carrying out pulsating Doppler echocardiographic examination. Mean pressure is determined in pulmonary artery. Mean pressure in pulmonary artery being less than 13 mm of mercury column, no cardiac rhythm disorders risk is considered to take place. The value being greater than 13 mm of mercury column, complex cardiac rhythm disorder occurrence risk is considered to be the case.

EFFECT: accelerated noninvasive method.

1 tbl

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