Device for suppressing power-frequency noise effect on electric cardiosignal

FIELD: medicine.

SUBSTANCE: invention refers to medical equipment. A device for suppressing a power-frequency noise effect on an electric cardiosignal comprises a TR-segment time domain selection unit (2), a key element (8), a filter (14), an amplifier (15), a delay unit (16) and a subtract unit (17). An input of the device is connected to the first input of the key element and an input of the delay unit; an output of the device is an output of the subtract unit. The device comprises an electric cardiosignal second derivative forming unit (1), a comparator (3), an RS-trigger (4), an AND circuit (5), a binary counter (6), a decoder (7), second (9), third (10), fourth (11) and fifth (12) key elements and a scaling amplifier (13).

EFFECT: using the invention enables the higher noise resistance of the analysed electric cardiosignal without misrepresenting information components.

8 dwg

 

The invention relates to medicine, in particular to electrocardiography, and can be used when processing electrocardiogram.

The most common and dangerous additive disturbance acting on electrocardiogram (EX), is focusing on the industrial network of 50 Hz. Frequency band spectral components EX interest for practical cases analysis electrocardiograma extends up to 100 Hz [1]. Thus, the additive disturbance from industrial supply is located in the frequency band occupied by electrocardiogram.

For removing additive noise from industrial power used by various filters.

Use as a device for the elimination of additive noise low-pass filters (LPF) with a cutoff frequency of about 25-35 Hz [2, S. 96-97; 3, S. 154] leads to the fact that together with additive disturbance from industrial supply from a mix of FORMER and interference removes part of the spectral components of electrocardiograma. Suppression components in the high frequency part of the spectrum FORMER leads, in turn, to a distortion of the shape of the FORMER on the output of the LPF, which can affect the results of the analysis of the FORMER.

To reduce distortion of shape EX at elimination of additive noise from industrial power using band-stop (notch) filters with Central the frequency, equal to the signal frequency industrial network 50 Hz [3, S. 154-158]. However, this device for suppressing additive noise from industrial power has drawbacks. Because through the filter pass all elements of electrocardiograma when using analog filters, or all discrete samples of all elements of electrocardiograma in the case of the use of discrete filters, the distortion of the spectral components EX, falling within the band of suppression notch filter, that is, together with the interference from the industrial network is suppressed, and the useful components of the FORMER.

In addition, the real band-stop filter cannot have an infinitely narrow band suppression, so together with a complete suppression component EX at a frequency of industrial network when passing through such a filter distorted (decrease in amplitude) closely spaced frequency components of the left and right of the center frequency of the boom.

Thus, as in the case of applying a low-pass filter, the distortion is of the form EX at the output of the band-stop filter, which is the same as when using a low-pass filter can affect the results of the analysis of the FORMER.

Closest to the proposed method (prototype) is a device for suppressing the influence of additive noise on electrocardiogram [4]. The device comprises a block allocation in each t is cle heart rate readings EX, the corresponding TP-segment having a duration τ is a multiple of the oscillation period of the signal network interference. The output of this block is formed by a sequence of packets of pulses, filled with network signal interference. In the spectrum of this sequence contains the frequency of the signal fill rectangular pulses, i.e., the frequency of additive noise 50 Hz, and lateral components formed of the spectral components of the baseband rectangular pulses of duration τ and a repetition period equal to the duration of one cycle of the heartbeat. In the spectrum of the missing components EX, because the TP segment corresponds to the electrical diastole of the heart and in the absence of noise has a zero value. The generated sequence of counts FORMER fed to bandpass filter with a center frequency equal to the frequency of additive noise (50 Hz for noise from industrial network), the output of the filter will select only the signal interference. The output signal from the band pass filter is fed to an amplifier and then to one of the inputs of the subtraction unit, to the other input of which receives the delayed in the delay block, the original EX with an obstacle. In block subtraction is the subtraction of the selected network signal interference from the original EX. At the output of the subtraction is "cleaned" from network interference electrocardiogram.

p> This device has the following disadvantages.

1. Duration counts electrocardiograma on the TP segment is fixed. Consequently, when the frequency deviation of network interference from the nominal value of the phase of the interference signal at the beginning of the countdown and at the end of the countdown will not match that will lead to the appearance of discontinuities in the signal interference and distortion of its spectral components.

This case is illustrated in Fig.1. In Fig.1 shows the spectrum envelopes of the amplitudes of a sequence of samples TP-segment, filled with jamming signal frequency. Duration samples (40 MS) is equal to two periods of the signal network interference at a nominal value of its frequency - 50 Hz. The repetition period (1) corresponds to the heart rate 60 beats/min Figure 1 shows the envelope of the spectrum at a nominal frequency industrial noise, the digit 2 is reduced, and the number 3 is at high frequency network interference. Figure 4 the designated level (0.04 In), which is the spectral component of network interference (denoted by a dot) at a nominal value of its frequency and the above time parameters of the samples if the amplitude of the interference is equal to 1 V. When the deviation of the frequency from the nominal value of the amplitude of its spectral component will be different from the nominal value: decreasing h is the frequency of the interference it will increase, higher decreases (shown by crosses in Fig.1).

2. When changing frequency network signal bandwidth bandpass filter (amplitude-frequency characteristic of the bandpass filter shown by the dashed line 1 in Fig.2) get the lateral components of the spectrum (shown as vertical solid lines in Fig.2) sequence allocated to the TP segment burst, filled with network signal interference, which will lead to the distortion of the interference signal at the output of the filter in terms of its amplitude modulation (Fig.3).

The essence of the invention consists in the following. In the device containing the block allocation of a time interval corresponding to the TP segment of the FORMER, a key element, a filter, an amplifier, a delay unit and a subtraction unit, and the first (information) input the key element and the input of the delay unit are connected together, forming the input device, the output device is an output of the subtraction unit, put the unit forming the second derivative of the FORMER, the comparator RS-trigger circuit And a binary pulse counter, decoder, second, third, fourth and fifth key elements and scaling amplifier, the input processing unit to the second derivative of EX is connected to the input device, with the input of the delay unit and the first (information) inputs of the second, third, fourth and pathologic elements, the output of the processing unit of the second derivative of EX is connected to the input of the block allocation of a time interval corresponding to the TP segment of the FORMER, and to the first comparator input, a second input connected to the "zero" wire, the output of block allocation of a time interval corresponding to the TP segment of the FORMER connected to the first input (setting "1") RS-flip-flop, the output of which is connected to the first input circuit And a second input which is connected to the output of the comparator, the output of the circuit And connected to the first (counting) input binary pulse counter, the bit outputs of a binary pulse counter connected to respective the inputs of the decoder, the first, second, third, fourth and fifth outputs of the decoder are connected respectively with the second (control) inputs of the first, second, third, fourth and fifth key elements whose outputs are connected respectively to the first, second, third, fourth and fifth inputs of the scaling amplifier, the sixth output of the decoder is connected to a second input (setting "0") RS-flip-flop and a second input (setting "0"binary pulse counter, the output of the scaling amplifier is connected to the input of the filter, which is made on the basis of a bandpass filter with a center frequency, equal to the frequency of network interference, the output of the filter connected to the amplifier input, the amplifier output is connected to the first input of the subtraction unit, the second input is connected to the output of the delay unit, the output unit subtracting an output device.

The proposed device allows to eliminate the disadvantages of the known device, namely, to weaken the influence of additive noise on electrocardiogram without distorting components of the signal itself.

The essence of the invention and an embodiment of the device illustrated in the following graphics:

Fig.4 is a structural diagram of the device;

Fig.5 and Fig.6 is a time chart illustrating the process of forming samples EX on the TP-segment;

Fig.7 is a spectrum of samples TP-segment;

Fig.8 - signal interference remaining after subtracting from the original EX with the interference signal selected network interference.

The technical result of the proposed device is achieved as follows. The selection signal interference from the electrical network is based on the filtration processing times of the FORMER, taken on the TP segment. The TP segment corresponds to the electrical diastole of the heart, therefore, these samples do not carry information about the electrical activity of the heart, and only contain the components of the noise acting on the EX. In this regard, the restoration of the noise signal by filtering samples TP-segment does not distort the EX. With the aim of taking into account the changes in the frequency of network interference and reduction due to this error of the recovered signal interference counts TP segment is synchronized with the signal network interference. The beginning of each sample coincides with the moment of transition of the signal network interference zero line (for example, from the negative to the positive half-wave), and the end of the countdown is formed at the end of two periods of the signal network interference, regardless of its frequency. Use five times the TP segment, the amplitude of which is determined scale factors calculated according to certain rules for a given distance between samples allows to suppress the spectrum of samples TP-segment, filled with network signal interference, two spectral zones to the left of the spectral component at frequency interference and two spectral zones on the right. This eliminates the ingress bandwidth bandpass filter spectral components of zones adjacent to the component at the frequency of network interference, even when changing its frequency.

Diagram of the device shown in Fig.4.

The device comprises a block 1 forming the second derivative of EX, unit 2 the allocation of a time interval corresponding to the TP segment of the FORMER in each cycle of pulse, a comparator 3, RS-trigger 4, scheme 5, a binary pulse counter 6, a decoder 7, the first 8, second 9, the third 10, 11 fourth and fifth 12 key elements of the scaling amplifier 13, a filter 14, is made on the basis of a bandpass filter with a center frequency equal to the frequency at which EHI frequency, the amplifier 15, the delay block 16 and block 17 subtraction signal network interference.

The input unit 1 forming the second derivative of EX is connected to the input device to the input of the delay block 16 and the first (information) inputs of the first 8, second 9, the third 10, 11 fourth and fifth 12 key elements, the output of block 1 forming the second derivative of EX is connected to the input unit 2 the allocation of a time interval corresponding to the TP segment of the FORMER, and to the first input of the comparator 3, the second input is connected with the zero wire of the output unit 2 the allocation of a time interval corresponding to the TP segment EX, is connected to the first input setting "1") RS-flip-flop 4, the output of which is connected to the first input circuit And 5, the second input of which is connected to the output of the comparator, the output of the circuit 5 is connected to the first (counting) input binary pulse counter 6, the bit outputs of a binary pulse counter 6 is connected to the corresponding inputs of the decoder 7, the first, second, third, fourth and fifth outputs of the decoder 7 is connected respectively with the second (control) inputs of the first 8, second 9, the third 10, 11 fourth and fifth 12 key elements, the outputs of which are connected respectively to the first, second the third, fourth and fifth inputs of the scaling amplifier 13, the sixth output of the decoder 7 is connected with the second input (the mouth of the transportation "0") RS-flip-flop 4 and the second input setting "0"binary pulse counter 6, the output of the scaling amplifier 13 is connected to the input of the filter 14, which is made on the basis of a bandpass filter with a center frequency equal to the frequency of the interference frequency, the output of the filter 14 is connected to the input of the amplifier 15, the output of the amplifier 15 is connected to the first input unit 17 subtraction, the second input is connected to the output of the delay block 16, block 17 subtracting an output device.

The operation of the proposed device is illustrated by the graphs in Fig.5, 6, 7 and 8.

The device operates as follows. The signal EX, including interference from the electrical outlet (Fig.5), is fed to the input device and, respectively, to the input unit 1 forming the second derivative of EX and the first (information) inputs of the first 8, second 9, the third 10, 11 fourth and fifth 12 key elements, and also to the input of the delay unit 16. In block 1 forming the second derivative is the weakening of the additive low-frequency interference type drift contour lines, if any are present in the input signal, as compared with the interference from the mains frequency. This ensures a more reliable selection unit 2 a time interval corresponding to the TP segment. The output unit 1 to the input of the unit 2 selection of the time interval corresponding to the TP segment of the FORMER, and the first input components is the EOS 3. Unit 2 the allocation of a time interval corresponding to the TP segment EX may be made in the form of the device [5] or [6]. The output signal of the block 2 is a sequence of rectangular pulses coinciding in time with the initial plot TP-segment in each cycle of cardiac contractions. This sequence served as a control signal to the first input setting "1") RS-flip-flop 4. RS-flip-flop 4 is set to the state of the logical unit, and the signal from its output when the first input circuit And 5, permit the passage at its output a rectangular pulse from the output of the comparator 3, formed by the comparison signal from the output of block 1 with zero potential. The repetition period of the rectangular pulse at the output of the comparator is equal to the repetition period of the interference from the mains frequency. The sequence of rectangular pulses from the output of the comparator 3 is supplied to the second input circuit 5, and when the first input of the enabling output signal from RS-flip-flop 4 is held at the output of the circuit 5 and the first (counting) input binary pulse counter 6, which carries these impulses. Thus, the switching of the binary counter is only at times that coincide with the moments of the zero-crossing signal network interference. The signals from the bit outputs of the binary counter impulse the 6 go to corresponding inputs of a decoder 7, which converts the binary code at its inputs in the position code at its outputs. While the beginning and end of the pulses on each of the outputs of the decoder matches the moments of the zero-crossing signal network interference. Thus, the phase of the interference signal at the beginning of the countdown and at the end of the countdown will be the same, which eliminates the appearance of discontinuities in the signal and, accordingly, the distortion of its spectral components of the Pulse from the first, second, third, fourth and fifth outputs of the decoder 7, spaced in time, proceed to the second (control) inputs, respectively, of the first 8, second 9, the third 10, 11 fourth and fifth 12 key elements, allowing in turn pass on the outputs of these key elements of the plots TP-segment electrocardiograma present on the first (information) inputs of all key elements. The signals from outputs of the key elements of the act respectively on the first, second, third, fourth and fifth inputs of the scaling amplifier 13 and amplified or attenuated (scaled) in a specified number of times. Thus the sign of the signal at the output of the amplifier 13 may coincide with the sign of the corresponding input or to be opposite him.

In Fig.6 shows in a larger time scale of a fragment of the TP-segment electrocardiograph shown in Fig.5. POM the ha from the network frequency (sin50(t)) is shown by the dashed line. Plots TP-segment (UTP(t)), past the exit key devices and then passed through a scaling amplifier 13, have the form of a pulse packet filled with jamming signal frequency (shown in Fig.6 by solid lines). The pulses in the stack are arranged symmetrically relative to the Central pulse.

By appropriate choice of the time shift of each pair of pulses relative to the Central pulse and the values of scaling factors for each pair of pulses it is possible to provide suppression in the spectrum of the sequence of such burst spectral zones with predetermined numbers [7]. The values of the shifts of the pulses of the inner pair τ1 and the outer pair of τ2 (Fig.6) the values of scaling factors K1 and K2 are solution of the system of equations [7]

1+2[K1cos(2πjt1T)+K2cos(2πjt2T)]=01+2[K1cos(2πkt1T) +K2cos(2πkt2T)]=0,

where j, k are non suppressed spectral zones, T is the repetition period of the pulse packet defined by the heart rate.

In the example shown in Fig.6, the pulse duration τ is equal to two periods of signal interference frequency, τ1=5τ, τ2=7τ, T=1, which corresponds to a heart rate of 60 beats/min, j=1, k=2. With such initial data, the solutions of the system of equations obtained values of scaling factors: K1=-0,846 and K2=1,274. Thus, the sign of the inner pair of pulses of opposite sign of the original signal, and the sign of the outer pair of pulses coincides with the sign of the original signal.

This will be depressed first and the second spectral zone, if the reference point to take zero spectral zone. In addition, in accordance with theorem on the spectrum shift of the low-frequency signal in the high frequency region when it is multiplied by the higher frequency oscillation, will be suppressed two spectral zones located to the left of the spectral component corresponding to the actual frequency fCindustrial network(fC/msub> -1T,fC-2T)and two spectral zones located to the right of(fC+1T,fC+2T).

The spectrum of the signal taken from the output of the scaling amplifier 13 shown in Fig.7. In this example, the frequency of industrial network has been taken equal to 50.1 Hz. Accordingly, in the spectrum of the signal (Fig.6) with the adopted higher repetition period T=1 with no components at frequencies 48.1 Hz, 49.1 Hz, 51.1 Hz and 52.1 Hz (Fig.7).

Once formed, the entire stack of five pulses of the signal from the sixth output of the decoder 7 is supplied to the second input (setting "0") RS-flip-flop 4 and sets the RS-flip-flop 4 in the zero state, the output signal of the trigger becomes equal to a logical zero and prohibits the passage through the scheme And 5 pulses from the output of the comparator 3, the first (counting) input binary pulse counter 6. Also the signal from the sixth output of the decoder 7 is supplied to the second input (setting "0"binary pulse counter 6 and sets the latter in the initial zero state.

The following is ikle heartbeat described process is repeated.

The sequence of packets of pulses from the output of the scaling amplifier 13 (Fig.6) is fed to the input of filter 14, which is made on the basis of a bandpass filter with a center frequency equal to the nominal frequency interference industrial network and the attenuation of the amplitude-frequency characteristics of the order of -40...80 dB at frequencies (50 Hz (±2 Hz). At the output of filter 14 is allocated signal interference from industrial network. The amplitude of this signal is smaller than the amplitude of the original signal (Fig.5 and 6) τ(1+2K1+2K2)/T time [8]. Therefore, the output signal from the filter 14 is fed to the input of the amplifier 15 with a gain Kus=T/[τ(1+2K1+2K2)].

The output signal from the amplifier 15 is supplied to the first input unit 17 of the subtraction, to the second input of which is supplied from the output of the delay unit 16. Electrocardiogram with interference, delayed for the time required to obtain at the output of the amplifier 15 of the interference signal frequency in accordance with the described process. In block 17 deduction is a subtraction from the original electrocardiograma with interference from the industrial network of the selected signal of the obstacle. At the output of the subtractor 17 is "cleaned" from interference electrocardiogram.

Naturally, the imperfection of the characteristics of real blocks involved in the allocation of network signal interference, do not allow to completely eliminate this disadvantage. In Fig.8 presents residual interference Δs(t). When the amplitude of the interference source 1 (see Fig.6) the amplitude of the residual interference does not exceed 15 mV, that is, the influence of interference is weakened more than 60 times.

Technical and economic effect of the proposed device is to provide high noise immunity investigated electrocardiograma without producing distortion in his informative components. This provides, in turn, increase the information content of the FORMER and, as a consequence, the General level of quality electrocardiographic diagnosis that facilitates timely and informed to take necessary measures for dealing with abnormalities of the cardiovascular system of the patient.

Literature

1. Bakalov B. N. fundamentals of biotelemetry. M.: Radio and communication, 2001. C. 27.

2. Rangayan P. M. Analysis of biomedical signals. M.: Fizmatlit, 2007. S. 96-97.

3. The heart monitor. Equipment for continuous monitoring of ECG / A. L. Baranovski, A. N. Kalinichenko, L. A. Attracted etc.: edited by A. L. Baranovsky and A. P. Nemirko. M.: Radio and communication. 1993. S. 153-159.

4. RF patent №2428107, A61B 5/04, A61B 5/0402. The method of suppressing the influence of additive noise on electrocardiogram and device for its implementation / O. C. Miller, A. A. Mikheev, N. With. Strukova. 2011. No. 25.

5. RF patent №2237432, A61B 5/02. Device to select the beginning of the cardiac cycle / O. A. Zuikova, A. A. Mikheev // Opening. Of the invention. 2004. No. 28.

6. RF patent 287367, MKI7A61B 5/02, A61B 5/0452. The way to identify cardiocomplex and device for its implementation / P. A. Blinov, A. A. Mikheev // Opening. Of the invention. 2010, No. 12.

7. Karasev centuries, Mikheev, A. A., Nechaev, I. Measuring system for rotating assemblies and mechanisms. M.: Energoatomizdat, 1996. S. 81-87.

8. Melnik, O. C., A. Mikheev A. Methods of processing and analysis of electrocardiogram in real-time / Under the General editorship of O. C. Miller. Ryazan: "Service", 2010. S. 59-61.

The device suppress the influence of interference of industrial frequency on electrocardiogram containing block allocation time interval corresponding to TR-segment electrocardiograma, a key element, a filter, an amplifier, a delay unit and a subtraction unit, and the first input key element and the input of the delay unit are connected together, forming the input device, the output device is an output of the subtraction unit, characterized in that it introduced the forming unit of the second derivative of electrocardiograma, the comparator RS-trigger circuit And a binary pulse counter, decoder, second, third, fourth and fifth key elements and scaling amplifier, the input unit the formation of the second derivative of electrocardiograph connected to the input device, with the input of the delay unit and to the first inputs of the first, second, third, fourth and fifth key elements : the processing unit of the second derivative of electrocardiograph connected to the input of block allocation time interval, the corresponding TR-segment electrocardiograma, and to the first comparator input, a second input connected to the "zero" wire, the output of block allocation of a time interval corresponding to TR-segment electrocardiograph connected to the first input of the RS-flip-flop, the output of which is connected to the first input circuit And a second input which is connected to the output of the comparator, the output of the circuit And connected to the first input of a binary pulse counter, the bit outputs of a binary pulse counter connected to respective inputs of the decoder, the first, second, third, fourth and fifth outputs of the decoder are connected respectively with the second inputs of the first, second, third, fourth and fifth key elements whose outputs are connected respectively to the first, second, third, fourth and fifth inputs of the scaling amplifier, the sixth output of the decoder is connected to the second input of the RS flip-flop and a second input binary pulse counter, the output of the scaling amplifier is connected to the input of the filter, which is made on the basis of a bandpass filter with a center frequency equal to the frequency of the interference frequency, the output of the filter connected to the amplifier input, the amplifier output is connected to the first input of the subtraction unit, the second input is connected to the output of the delay unit, the output unit subtracting the beach on the output device.



 

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2 cl, 3 ex

FIELD: medicine.

SUBSTANCE: continuous electric cardiac signal (ECS) is filtered and presented in the form of discrete readouts. Then it is smoothed by amplitude averaging of adjacent readouts of the electric cardiac signal. That is followed by isolating R-R interval and a cardiac cycle, limiting a search area of the beginning of the ventricular repolarisation to the left and right in relation to R wave, specifying two numbers of the ECS readouts X1={xa÷xb} and X2={xc÷xd}in the search area, calculating arithmetical mean amplitudes M1 and M2 of the readouts from the numbers X1 and X2, calculating an absolute difference of mean ECS amplitudes D=|M1-M2|, and unless D gets more than the ECS limit, calculating M1, M2 and D is repeated for the numbers X1 and X2 displaced one element to the right until reaching the right limit of the search area, isolating the readout Jj,i=xa in each j-th deflection for which D falls below the ECS limit. Thereafter the latest Jj,i value is determined; the determined value represents the beginning of ventricular repolarisation in the i-th cardiocycle.

EFFECT: method provides higher reliability of isolating R-wave and stating the beginning of ventricular repolarisation.

13 dwg

FIELD: medicine.

SUBSTANCE: auricular extrasystole recorded in the patient is analysed by calculating a relative coupling interval (RCI). The value is calculated by dividing a cardiac contraction interval immediately preceding the auricular extrasystole by the coupling interval. The derived RCI is assessed. If the value exceeds the value of 1.7, a high risk of developing paroxysmal atrial fibrillation is diagnosed in the patient.

EFFECT: method enables predicting a high probability of developing paroxysmal atrial fibrillation within the next hour.

2 ex, 2 dwg, 3 tbl

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

FIELD: medicine; medical engineering.

SUBSTANCE: method involves selecting reference point in every cardiac cycle on TP-segment. Values of neighboring N=2n+1 reference points also belonging to TP-segment are recorded, n=1,2,…, beginning from the first reference point. Other reference points are set to zero. The central reference point value is left without changes in a group of 2n+1 member. Reference point values of each of n pairs of reference points symmetrically arranged relative to the central reference point are scaled relative to condition Uj=U0Kj, where U0 is the central reference point amplitude, Uj is amplitude of j-th reference point pair, j=1,2,…,n is the number of each reference point pair relative to the central reference point, Kj is the scaling coefficients determined from received signal suppression condition of the first n spectral zones in spectrum. The so formed electrocardiogram signal reference point groups sequence is let pass through lower frequency filter with isoline drift signal being obtained being produced on output. The signal is amplified and subtracted from the initial electrocardiogram signal that is preliminarily delayed for lower frequency filter delay time. Device has the first lower frequency filter, discretization unit and unit for selecting anchor reference points connected in series, as well as subtraction unit, unit for saving N reference points, scaling unit, the second lower frequency filter, amplifier and delay unit. Output of the unit for selecting anchor reference points is connected to the first input of memory unit the second input of which is connected to discretization unit output. Each of N memory unit outputs is connected to one of N inputs of scaling units. Scaling unit output is connected to the second lower frequency filter input which output is connected to amplifier input. Amplifier output is connected to the first input of subtraction unit, the second output of subtraction unit is connected to delay unit output. Its input is connected to output of the first lower frequency filter. Subtraction unit output is the device output.

EFFECT: reliable removal of isoline drift.

2 cl, 8 dwg

FIELD: medicine; cardiology.

SUBSTANCE: device has amplifier, analog-to-digital converter provided with multiplexer, arithmetic unit, memory unit, digital modem, increment code analyzer, increment codes number counter, switching unit and control unit as well as second memory unit, digital filtration unit and decimation unit. Electrocardiogram signal is registered within frequency-time area. Increase in volume of diagnostic data is provided due to time localization of spectral components of electrocardiogram signal.

EFFECT: widened operational capabilities; improved precision of diagnosing; higher efficiency of treatment.

6 dwg

FIELD: medicine; radio electronics.

SUBSTANCE: device for taking cardiogram has set of electrodes, cardiologic unit, analog-to-digital converter, cardio signal preliminary treatment unit, computer, lower frequency filter, differentiator, functional converter and controlled filter. Power function calculation units are not included. Preliminary continuous filtering of cardio signal entering the computer is provided.

EFFECT: simplified design; improved precision of measurement.

1 dwg

FIELD: medical engineering.

SUBSTANCE: device has electrodes, input amplifier, unit for protecting against error influence when applying medical electric instruments, low frequency filter, signal analysis unit, unit for eliminating isoline drift and electric power supply units.

EFFECT: high accuracy in plotting rhythmograms; improved instruments manipulation safety.

1 dwg

FIELD: medicine.

SUBSTANCE: method involves modeling real three-dimensional patient heart image based on electrocardiogram and photoroentgenogram data and determining basic functional values of its myohemodynamics.

EFFECT: high accuracy and reliability of the method.

2 cl, 5 dwg

FIELD: medicine.

SUBSTANCE: method involves recording cardiac biopotentials with vector electrocardiograph, processing and visualizing signal with graphical plane integral cardiac electric vector projections (vector electrocardiograms) being built and analyzed. Shape, QRS-loop value and vector orientation-recording process are determined. Analysis is based on planar vector electrocardiograms in horizontal, frontal and sagittal planes and in spatial 3-D-form. Vector loop direction is studied in X-,Y-,Z-axis projections, values, dynamics and localization are evaluated in resulting integral cardiac electric vector delta-vector space. To do it, QRS-loop is divided into four segments, one of which characterizes excitation in middle part of axial partition surface, the second one is related to excitation in lower ventricular septum one-third with cardiac apex being involved and the third and the fourth one is related to excitation in basal parts of the left and right heart ventricles. Delta-vector existence and its magnitude are determined from changes in loop segment localization when compared to reference values.

EFFECT: improved data quality usable in planning surgical treatment.

4 dwg

FIELD: medical radio electronics.

SUBSTANCE: device can be used for testing cardio-vascular system of patient. Differential vector-cardiograph has high frequency oscillator, common electrode, unit for reading electrocardiogram and radio cardiogram provided with amplification channels and filtration channels, multiplexer, microprocessor unit with common bus, analog-to-digital converter, keyboard, mouse and indication unit. Device provides higher precision of measurements due to usage of electric component heart activity and truth of diagnostics due to ability of representation of results of testing in form of variety of vector-cardiograms in real time-scale.

EFFECT: improved precision.

1 dwg

FIELD: medicine, cardiology, arhythmology, functional diagnostics.

SUBSTANCE: one should register electrocardiogram in esophagus, apply an electrode in a site where the maximum signal amplitude is registered, increase the signal 5-fold, not less to be filtered in the range of 0.5-40 Hz to be registered at the rate of 100 mm/sec, not less. The time for intra-atrial process should be measured from the beginning of ascending part of the first positive wave of pre-P-tooth up to the top of the second adhesion of P-tooth; the time for inter-atrial process should be measured from the site of crossing a descending part of the first positive wave and the onset of obliquely ascending pre-P-interval up to crossing this interval with the point of abrupt increase of the first phase of P-tooth. The innovation provides more means for noninvasive evaluation of intra- and inter-atrial stimulation process.

EFFECT: higher accuracy of evaluation.

3 dwg

FIELD: medicine, cardiology.

SUBSTANCE: one should register a standard electrocardiogram (ECG) and measure the duration of a "P"-wave. Moreover, it is necessary to conduct daily ECG monitoring to calculate single, paired and group atrial extrasystoles. Then one should calculate diagnostic coefficient DC by the following formula: DC=DC1+DC2+DC3+DC4, DC1 =-8.8 at duration of "P"-wave below 106 msec, 9.3 at duration of "P"-wave above 116 msec, -3.5 at duration of "P"-wave ranged 106-116 msec. DC2=-1.9 at the absence of group atrial extrasystoles during a day, 8.3 -at daily quantity of group atrial extrasystoles being above 4, 2.5 - at daily quantity of group atrial extrasystoles ranged 1-4. DC3=-2.9 at daily quantity of paired atrial extrasystoles being below 3, 8.1 - at daily quantity of paired extrasystoles being above 35, -1.4 - at daily quantity of paired atrial extrasystoles ranged 3-35. DC4=-5.1 at daily quantity of single atrial extrasystoles being below 15, 4.3 - at daily quantity of single atrial extrasystoles being above 150, -1.0 - at daily quantity of single atrial extrasystoles ranged 15-150, if DC is above or equal to 13 one should diagnose high risk for the development of paroxysmal atrial fibrillation, in case if DC is below or equal -13 it is possible to diagnose no risk for the development of paroxysmal atrial fibrillation, and if DC is above -13 and below 13 - the diagnosis is not established.

EFFECT: higher sensitivity of diagnostics.

5 ex

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