SU1209152A1 - Method and apparatus for analysis of cardic rhytm - Google Patents

Abstract

1. A method for analyzing the rhythm of the heartbeat, which simultaneously removes the electrocardiogram and respiration signals from the patient and converts the duration of the current cardiocycle into a voltage that is different in order to assess the relationship between the rhythm of the cardiac contractions and the respiratory parameters. the previous cardiac cycle into a voltage, is formed by a voltage proportional to dl and -. of the current cardiac cycle, and by the respiration signal, the image control signal, then both signals are fed to the inputs of the two-coordinate indicator and by the distribution of graphic symbols on the screen of the indicator, the relationship between the heart rate rhythm and the respiration parameters is evaluated. (L S about CD SP yu Fb / g .;

Description

2. A device for analyzing heart rate, containing a series-connected electrocardiogram sensor, Wuxi, R-wave detector, a cardiointerval into voltage transducer, and a recorder and a breath sensor, characterized in that, in order to evaluate the relationship of the heart rhythm with the respiratory parameters ,

A signal synthesis unit is inserted into it, to the first input of which a respiration sensor is connected, and the cardiointerval to voltage conversion unit is designed as a converter of two adjacent cardiointervals to voltages, the second output of which is connected to the second input of the signal synthesis unit indicator, the second input of which is connected to the output of the signal synthesis unit.

3, The device according to Po2, characterized in that in it the cardiointerval-to-voltage converting unit is designed as a pulse shaper, the input of which is connected to the output of the R-wave detector,

The invention relates to medicine, 5 namely, methods for monitoring and diagnosing the functional state of the cardiovascular system 1 .1 of the organism.

The purpose of the invention is to assess the relationship between the rhythm of heart contractions and respiration parameters.

Figure 1 shows the structural electrical circuit of the device for analyzing the rhythm of the heartbeat; Fig. 2 is a schematic implementation of a breath sensor; FIG. 3 shows a structural electrical circuit of the pulse former, the first and second accumulators, and the switch; FIG. 4 is a timing diagram of the passage of signals along the circuits of the device while implementing the proposed method} FIG. 3 image on the screen of a cathode ray tube (CRT) - distribution

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the first drive, the inputs of which are connected respectively to the first and second outputs of the pulse former, the second drive, whose inputs are connected respectively to the third and fourth outputs of the pulse former, and the switch, the first and second inputs of which are connected respectively to the outputs of the first and second drives, the third and fourth inputs, respectively, with the fifth and sixth outputs of the pulse former, the first code with the first input of the two-coordinate indicator, and the second output with the second input of the block with nteza signals.

4. The device according to claim 2, characterized in that it contains a signal synthesis unit in the form of a summing amplifier, and the respiration sensor contains a series-connected variable resistor and a trimming resistor connected to an alternating voltage source with a grounded midpoint, and the point of connection is variable and trimmer resistors connected to the first input of the signal synthesis unit.

graphic characters obtained by implementing the proposed method.

The device contains a series of electrocardiogram sensor 1 (ex), amplifier 2, detector 3R-rammer EX, cardio-voltage conversion unit 4 and recorder 5, serially connected breath sensor 6 and signal synthesis unit 7, the cardio-voltage converting unit 4 made as a converter of two adjacent cardiointervals into voltages, the second output of which is connected to the second input of the signal synthesis unit 7. And the recorder 5 is designed as a two-coordinate indicator, the second input to expensively connected to the output of block 7 signal synthesis.

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In this case, the conversion unit of the radiointerval into voltage contains (FIG. 1) a pulse shaper 8, the input of which is connected to the output of the R-wave detector 3, the first drive 9, the inputs of which are connected respectively to the first and second outputs of the pulse shaper 8, the second drive 10 The inputs of which are connected respectively to the third and fourth outputs of the driver 8 pulses, and the switch 11, the first and second inputs of which are connected respectively to the outputs of the first storage device 9 and the second storage device 10, the third and fourth input - respectively to the fifth and sixth output pulse shaper 8, the first output - to the first input two coordinate warning indicator, and the second output - to a second input of the synthesis of signals 7.

The signal synthesis unit 7 can be made in the form of a summing amplifier, and the two-coordinate indicator in the form of an oscilloscope with a CRT, the inputs of which are the inputs of the beam sweep along the horizontal (X) and vertical (Y) axis of the CRT.

In addition, the respiration sensor contains (Fig.2) series-connected AC 12 and trimmer 13 resistors connected to a variable voltage source 14 with a grounded midpoint, and the connection point of the AC 12 and trimmer 13 resistors is connected to the first input of synthesis unit 7 signals. In this case, the alternating voltage source 14 can be performed, for example, on a transformer, the secondary windings of which are connected in series and their connection point is grounded, and the primary winding is connected to the primary alternating voltage source. Variable resistor 12 constructively can be made in the form of a rubber tube filled with graphite and fixed on a corset that encloses the patient's chest.

The pulse shaper 8 (FIG. 3 contains first connected first 15 and second 16 one-shot and counting trigger 17, first 18 and second 19 elements And, the first inputs. Which are connected to the output of the first single-vibrator 15, and the outputs are connected respectively to

15

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25

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the third and fourth inputs of the 1G switch, the third element AND 20, and the fourth element AND 21, the first inputs of which are connected to the output of the second one-oscillator 16, and the outputs are connected respectively to the first input of the first drive 9 and the first input of the second drive 10 The second inputs of the first element 9 and 21 and the fourth element 21 are connected to the first output of the counting trigger 17 and to the second input of the first accumulator 9, the second inputs of the second element 19 and the third element 20 to the second output of the counting trigger 17 and to the second in the second drive 10, and the input of the first one-shot 15 is connected to the output of the detector R-wave 3.

The first drive 9 (FIG. 3) contains the first capacitor 22 connected to the first input of the switch 11 through the first switch 23 to the DC source 24 and through the second switch 25 to the zero bus, the control inputs of the first 23 and second switches 25 are connected respectively, with the first output of the counting trigger 17 and with the output of the third element I 20, and the second lining of the first capacitor 22 is connected to the zero bus. The second accumulator 10 (FIG. 3) contains the second capacitor 26 connected to the second input of the switch 11 through the third switch 27 to the DC source 24 and through the fourth switch 28 to the zero bus, the control inputs of the third and fourth switches 27 and 28 connected respectively with the second output of the counting trigger 17 and the output of the fourth element And 21, and the second lining of the second capacitor 26 is connected to the zero bus.

The switch 11 (FIG. 3) contains keys connected in series between its first X and second Y output buses, serially connected fifth and sixth 30 keys and serially connected seventh 31 and eighth 32 keys, with the control inputs of the sixth 30 and seventh 31 keys connected to the output the first element And 18, and the control inputs of p 29 29 55 and the eighth 32 keys are connected to the output of the second element And 19.

The method is carried out as follows.

thirty

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SC, by applying the EX-1 sensors and the respiration sensor 6 superimposed on the patient, simultaneously remove the EX-breath signal. The EX signal (Fig. 4a) is fed through the amplifier 2 to the R-wave detector 3, which, for each R-wave, the EX generates a sync pulse, the sequence of which is fed to the input of the cardiointervoltage-to-voltage unit 4. This block 4, at its outputs X and Y, forms, respectively, a signal proportional to; the duration of the previous cardio cycle (RR interval) is proportional to the signal proportional to the duration of the current cardiocycle.

The respiration signal (fig. 4t) is fed to the first input of the signal synthesis unit 7, to the second input of which a signal is output from the output of the block 4, which converts the cardiointerv to voltage. At the time of each successive heartbeat, the signal synthesis unit 7 generates an image control signal that carries information both about the duration of the current cardiocycle and about the depth and / or respiration phase of the patient (figure 4U which is fed to the input V vertical deviation of the two-coordinate indicator 5, To the input X of the horizontal deviation of which a signal is received that is proportional to the duration of the previous cardiac cycle (Fig. 4X). Thus, on the screen of the two-coordinate indicator 5, a symbol is formed whose position is The origin of the screen characterizes the duration of the current and pre-cardiac cardio, and its dimensions, shape, or color indicate the depth and / or phase of breathing. In one embodiment of the device, in which the design of the breath sensor 6 is given in FIG. 2, the cardiointer conversion unit 4 - the shaft in voltage has a design shown in FIG. 3, and a summing amplifier and an oscilloscope with a CRT are used, the symbol formed on the screen of a CRT (Fig „5) has the form of a vertical line, the length (3 of which is proportional to the inspiratory depth, and inati X and Y, which on the CRT screen is proportional to the duration of the previous respectively (RR |) and the current (RR ,,) kardio1Schk- fishing. When this device operates as follows.

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For each sync pulse generated by the R-wave 3 detector when an ECS arrives at its input, the first single vibrator 15 produces a pulse of several milliseconds in duration. This pulse opens through the corresponding first 18 (fig.4a) or second 19 elements AND (fig.4c), determined by the state of the counting trigger 17 (figDe and fig.4d), or the sixth 30 and seventh 31 keys, or fifth 5 and the eighth 32 keys. At the same time, the voltages on the first and second capacitors 22 and 26 are proportional to the duration of the last two adjacent cardiointerests. are fed to the outputs X and Y of the switch 11 so that the output Y is given a signal proportional to the duration of the RR- card just completed, and the output .X is a signal proportional to the duration of the previous cardiocycle RRj (Fig. 4, X). Then the signals from the outputs of the switch 11 are fed to the corresponding scan inputs of the oscilloscope 5, on the screen of which the point is lit (in the absence of a breathing signal) with the corresponding coordinates.

The second one-shot 16, launched on the falling edge of the pulse of the first one-shot 15, also produces a pulse of several milliseconds, which, if there is a logical 1 on the first output of the counting trigger 17 (FIG. 4e), opens the fourth key through AND 21 (FIG. 4B) 28 and discharges the second capacitor 26 (Figure 4b). The falling edge of this pulse transfers the counting trigger 17 to another stable state, in which the logical O closes the first switch 23 at its first output (FIG. 4e) and a voltage proportional to the duration of the previous cardio-interval is fixed to the first capacitor 22 (Fig.4 ), and the logical 1 at the second output of the counting trigger 17 (fig.4g) opens the third key 27J through which the linear charge of the second capacitor 26 starts up to a voltage proportional to the length of the current cardiointerval (fig.4b). With the arrival of the next clock pulse, the voltages are transmitted again from the first and second capacitors 22 and 26 (via the fifth and eighth keys 29 and 32) to

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the corresponding outputs X and Y of the switch 11, the signals on which determine the position on the CRT screen of the oscilloscope 5 of the next point, etc.

The breathing sensor 6 (Fig. 2) is initially adjusted by the trimming resistor 13 so that with the maximum exhalation of the patient, the voltage at the output of the breathing sensor 6 is zero. Then, with each breath, the rubber tube filled with graphite, which is a variable resistor 12, expands, increasing its resistance, and a variable voltage appears on the output of breath sensor 6 (figure 4t), the amplitude of which is proportional to the change in resistance of the variable resistor 12, therefore proportional to the depth of inhalation. This voltage is applied to the first input of the summing amplifier, the second input is supplied with a voltage proportional to the duration of the previous cardiocycle and determines the vertical deviation of the corresponding point on the oscilloscope's CRT screen. AC voltage.

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i, the frequency of which is chosen so that several oscillations of this voltage fit over the time of the pulse deviation of the beam, 5 summing up with the deviation pulse along the axis Y (FIG. 4 y) when illuminated on a CRT screen and the vertical line, the length d of which is proportional to the depth of inhalation, and the position on the screen displays the duration of the corresponding cardiocycles (figure 5).

Formed during a given period of observation, a two-dimensional distribution of symbols (for example, vertical lines) reflects the dynamics of the heartbeat rhythm taking into account the depth and phase of respiration, the Ta-20 IMM, the method of analyzing the heart rate and the proposed device for its implementation the ability to control the functional relationship of respiration and rhythm of heart contractions, which ensures the prompt and reliable diagnosis of this connection and the types of cardiac arrhythmias.

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Compiled by E. Baluev Editor M.Blanar Tehred T.Tulik Corrector I.Muska

Order 336/6 Circulation. 659 Subscription VNIIPI USSR State Committee

for inventions and discoveries, 113035, Moscow, Zh-35, Raugaska nab. 4/5

Branch PPP Patent, Uzhgorod, Proektna St., 4

Fi, if

IS sec

Claims (4)

METHOD FOR ANALYSIS OF THE RHYTHM OF CARDIAC REDUCTION AND THE DEVICE FOR ITS IMPLEMENTATION. (57) 1. The method of analyzing the heart rate, which consists in the fact that the electrocardiogram and respiration signals are simultaneously taken from the patient and the duration of the current cardiocycle is converted to voltage, characterized in that, in order to assess the relationship of the heart rate with respiration parameters, they are also converted the duration of the previous cardiocycle in tension, is formed by a voltage proportional to the length--. function of the current cardiocycle, and an image control signal from the breathing signal, then both signals are fed to the inputs of the two-coordinate _Q indicator and the relationship of the heart rate with the respiration parameters is estimated by the distribution on the graphic display of the indicator of graphic symbols. SU „„ 1209152 FIG. /> 2. A device for analyzing a heartbeat rhythm, comprising a series-connected electrocardiogram signal sensor, an amplifier, an R-wave detector, a cardio-interval to voltage conversion unit, and a recorder and a breathing sensor, which, in order to assess the relationship of heart rhythm of abbreviations with respiration parameters, a signal synthesis block is introduced into it, the respiration sensor is connected to its first input, and the cardio-interval to voltage conversion unit is made in the form of a converter of two adjacent cardio-intervals to n conjugation, the second output of which is connected to the second input of the synthesis of signals, the recorder is configured as a two-coordinate display, a second input coupled to the output of the synthesis signals. 3. The device according to claim 2, characterized in that in it the cardio-interval to voltage conversion unit is made in the form of a pulse shaper, the input of which is connected to the output of the R-wave detector, the first drive, the inputs of which are connected respectively to the first and second outputs of the pulse shaper, the second drive, the inputs of which are connected respectively to the third and fourth outputs of the pulse shaper, and the switch, the first and second inputs of which are connected * respectively with the outputs of the first and second drives, the third and fourth inputs, respectively, with the fifth and sixth outputs of the pulse former, the first output with the first input of the two-coordinate indicator, and the second output with the second input of the signal synthesis unit, 4. The device according to claim 2, characterized in that the signal synthesis unit is made in the form of a summing amplifier, and the respiratory sensor contains a series-connected variable resistor and a tuning resistor connected to an AC voltage source with a grounded midpoint, and the connection point of the AC and tuning resistors connected to the first input of the signal synthesis block.