KR102498057B1 - Weight scale type reactance cardiac output monitoring apparatus and method - Google Patents

Abstract

A weight scale-type reactance cardiac output monitoring device and method capable of simultaneously measuring a user's body weight and cardiac output. A weight scale-type reactance cardiac output monitoring device includes a main body having a plurality of load cells and electrodes; a measurement unit for measuring a weight of a user positioned on the main body using the load cell and measuring a biosignal of the user positioned on the main body using the electrode; a signal processor configured to obtain a cardiac output (CO) of the user by using a reactance signal included in the bio-signal; and an application unit outputting the weight and the cardiac output, wherein the signal processing unit calculates the position of the center of position (COP) of the user based on the pressure applied to each load cell, A warning signal may be output when the center of gravity COP is out of a predetermined area.

Description

Weight scale type reactance cardiac output monitoring apparatus and method {Weight scale type reactance cardiac output monitoring apparatus and method}

The present invention relates to a weight scale-type reactance cardiac output monitoring apparatus and method capable of simultaneously measuring a user's body weight and cardiac output, and more particularly, after detecting the user's center of position (COP), the center of gravity A weight scale-type reactance cardiac output monitoring device and method, which are easy to use and have improved reliability of measurement results, by guiding the location within a desired measurement region.

In general, cardiac output is the amount of blood per minute that goes out to the whole body through heartbeats, and is an index that reflects not only cardiac function but also the state of the entire circulatory system, and is controlled through autonomous regulation of whole body tissues. Therefore, in treating a patient, the direction and method of treatment are determined by considering blood pressure, left ventricular filling pressure, cardiac output, and systemic vascular resistance. The measurement of cardiac output can yield many indicators that reflect overall circulatory system function, and systemic vascular resistance can be found using stroke volume, central venous pressure, and blood pressure.

Methods for measuring cardiac output can be largely divided into invasive methods and non-invasive methods. The invasive method uses a catheter to measure the amount of blood that is actually ejected into the heart. This method not only requires skilled skills from the operator, but also increases thoracic resistance to the patient if the operator makes a mistake during the procedure. There is a problem that causes a change in electrical bioimpedance.

In order to solve this problem, a non-invasive method using a spot ECG electrode or a band type electrode has been developed. For example, after attaching 4 pairs of electrodes to the xiphoid process on the neck and chest, constant current is injected from the outer 2 pairs of electrodes, and the differential voltage between them is measured through the 2 inner pairs of electrodes. to measure the impedance change. Here, the measured impedance change is due to the change in blood volume according to the contraction and relaxation of the heart in the aorta for each cardiac cycle.

However, despite these advantages, the non-invasive cardiac output measurement method has a problem in that self-measurement is difficult because there is no alternative that can be measured in a non-hospital setting. In order to solve this problem, a scale-type cardiac output monitoring device capable of self-measuring has been developed, but the conventional weight scale-type cardiac output monitoring device has a problem in that the measured value varies depending on the measurement position of the foot. That is, since the contact resistance varies depending on the area of the electrode in contact with the body, even if the measurement is performed with the same electrode, the measurement value is different due to the change in the contact area between the foot and the electrode when the electrode is out of the measurement position or standing with one leg. there was.

Registered Patent Publication No. 10-1950555 (announced on February 20, 2019)

An object of the present invention is to detect the center of position (COP) of a user located on a weight scale using a plurality of load cells, and then guide the center of gravity to be located within a desired measurement area, so that it is easy to use and the measurement result is It is an object of the present invention to provide a scale-type reactance cardiac output monitoring device and method having improved reliability.

In order to achieve the above object, a body scale-type reactance cardiac output monitoring device according to the present invention includes a main body having a plurality of load cells and electrodes; a measurement unit for measuring a weight of a user positioned on the main body using the load cell and measuring a biosignal of the user positioned on the main body using the electrode; a signal processor configured to obtain a cardiac output (CO) of the user by using a reactance signal included in the bio-signal; and an application unit outputting the weight and the cardiac output, wherein the signal processing unit calculates the position of the center of position (COP) of the user based on the pressure applied to each load cell, A warning signal may be output when the center of gravity (COP) is out of a predetermined area.

In addition, the body portion may be formed in a rectangular plate shape, and four load cells may be provided at corners of the body portion, respectively.

The weight scale-type reactance cardiac output monitoring device of claim 1 , wherein a portion of the electrode is exposed to the outside of the main body unit, and the measuring unit measures a biosignal using contact resistance when both feet of the user come into contact with the electrode.

In addition, the signal processor may detect the user's motion by measuring the distribution of the center of gravity (COP) during the measurement time, and output a warning signal when the distribution of the center of gravity (COP) exceeds a preset range. there is.

In addition, the signal processing unit may extract the impedance signal using a low pass filter (LPF) and extract the reactance signal using a high pass filter (HPF).

In addition, the signal processing unit may further obtain a heart rate (HR) and a heart rate variability (HRV) of the user by using the reactance signal.

In addition, the biosignal may further include at least one of an impedance signal, an electrocardiography (ECG) signal, a ballistocardiography (BCG) signal, and an impedance plethysmography (IPG) signal.

In addition, the signal processing unit calculates a pulse arrival time (PAT), a pulse transit time (PTT), and a pre-ejection period (PEP) using the electrocardiogram signal and the reactance signal. can obtain more.

In addition, the application unit calculates systemic vascular resistance (SVR), central venous pressure (CVP), mean arterial pressure (MAP), and systolic blood pressure calculated using the cardiac output and the pulse wave transit time. At least one of systolic blood pressure (SBP) and diastolic blood pressure (DBP) may be output.

The application unit may further include an input unit capable of inputting the user's body information, and the application unit analyzes body composition using the user's body information, the weight, and an impedance signal included in the bio-signals. and can be output.

In addition, the measurement unit may further include a temperature and humidity sensor for measuring ambient temperature and humidity.

A weight scale-type reactance cardiac output monitoring method according to the present invention includes the steps of measuring a user's weight using a plurality of load cells provided in a main body; Calculating a position of a center of position (COP) of the user based on the pressure applied to each load cell; determining whether the center of gravity is within a predetermined area, and outputting a warning signal when the center of gravity is out of the predetermined area; measuring a biosignal of the user located on the main body by using an electrode provided in the main body; obtaining a cardiac output (CO) of the user by using a reactance signal included in the bio-signal; and outputting the measured weight and cardiac output.

In addition, in the step of measuring the user's bio-signal, the weight scale detects the user's motion by measuring the distribution of the center of gravity during the measurement time, and outputs a warning signal when the distribution of the center of gravity exceeds a preset range. Type reactance cardiac output monitoring method.

In addition, the biosignal may further include at least one of an impedance signal, an electrocardiography (ECG) signal, a ballistocardiography (BCG) signal, and an impedance plethysmography (IPG) signal.

In addition, using at least one of the electrocardiogram signal and the reactance signal, the user's heart rate (HR: Heartrate), heart rate variability (HRV), pulse arrival time (PAT), pulse wave transit time ( A pulse transit time (PTT) and a pre-ejection period (PEP) may be further obtained.
In addition, a body portion provided with a plurality of load cells and electrodes; a measurement unit for measuring a weight of a user positioned on the main body using the load cell and measuring a biosignal of the user positioned on the main body using the electrode; a signal processor configured to obtain a cardiac output (CO) of the user by using a reactance signal included in the bio-signal; and an application unit outputting the weight and the cardiac output, wherein the signal processing unit calculates the position of the center of position (COP) of the user based on the pressure applied to each load cell, When the center of gravity deviates from a predetermined area, a warning signal is output to guide the user's foot to be located in the measurement area, and the signal processing unit measures the distribution of the center of gravity (COP) during the measurement time to measure the user's movement. It is characterized in that it detects and induces re-measurement by outputting a warning signal when the distribution of the center of gravity (COP) exceeds a preset range.

According to the present invention, it is provided as a weight scale type including a load cell and electrodes, and has an advantage in that weight and cardiac output can be simultaneously measured when the user climbs on the main body.

In addition, when the user's weight and cardiac output are continuously monitored through the cardiac output monitoring device, cardiovascular diseases can be self-managed and prevented.

In addition, by calculating the position of the user's center of position (COP) using a plurality of load cells provided in the main body, and outputting a warning signal when the center of gravity (COP) is out of a preset area, Reliability of the measurement result can be improved by guiding the user to place both feet in the correct measurement area.

In addition, since cardiac output as well as heart rate, heart rate variability, pulse wave arrival time, pulse wave transit time, stroke electricity, and the like can be simultaneously measured using the measured biosignal, cardiovascular diseases can be more effectively managed.

1 is a perspective view of a scale-type reactance cardiac output monitoring device according to an embodiment of the present invention.
FIG. 2 is a block diagram of the scale-type reactance cardiac output monitoring device shown in FIG. 1 .
FIG. 3 is a block diagram schematically illustrating a processing procedure of the scale-type reactance cardiac output monitoring device shown in FIG. 1 .
FIG. 4 is a graph showing results obtained by first- and second-order derivatives of reactance values that have passed through a high pass filter (HPF) in FIG. 3 .
FIG. 5 is a graph showing peak values over time of the first order differential signal of reactance in FIG. 3 .
6 is a view for explaining a process of calculating the position of the center of gravity using the load cell of FIG. 1;
7(a) is a diagram showing a case in which the center of gravity is located within a preset area, and FIGS. 7(b) to 7(d) are diagrams showing a case in which the center of gravity is located outside the preset area.
8(a) is a diagram showing a case in which the distribution of the center of gravity is located within a preset range, and FIG. 8(b) is a diagram showing a case in which the distribution of the center of gravity is located outside the preset range.
9 is a diagram illustrating a body composition table output through an application unit.
10 is a flow chart of a weight scale-type reactance cardiac output monitoring method according to an embodiment of the present invention.

Hereinafter, a weight scale-type reactance cardiac output monitoring device and method according to a preferred embodiment will be described in detail with reference to the accompanying drawings. Here, the same reference numerals are used for the same components, and repeated descriptions and detailed descriptions of known functions and configurations that may unnecessarily obscure the subject matter of the invention are omitted. Embodiments of the invention are provided to more completely explain the present invention to those skilled in the art. Accordingly, the shapes and sizes of elements in the drawings may be exaggerated for clarity.

1 is a perspective view of a weight scale-type reactance cardiac output monitoring device according to an embodiment of the present invention, FIG. 2 is a configuration diagram of the weight scale-type reactance cardiac output monitoring device shown in FIG. 1, and FIG. It is a block diagram schematically showing a processing procedure of the scale-type reactance cardiac output monitoring device. And, FIG. 4 is a graph showing the result of first and second order differentiation of the reactance value that has passed through the high pass filter (HPF) in FIG. 3, and FIG. 5 is the time of the first order differential signal of the reactance in FIG. It is a graph showing the peak value according to

1 to 5 , the scale-type reactance cardiac output monitoring device 100 may include a body unit 110, a measuring unit 120, a signal processing unit 130, and an application unit 140. there is.

The main body 110 forms the outer shape of the weight scale, and may include a plurality of load cells 10 and electrodes 20 . For example, the main body 110 may include an upper plate 111 made of a flat square plate so that both feet of a user may be positioned, and a lower plate 112 coupled to a lower portion of the upper plate 111. Due to the combination of the upper plate 111 and the lower plate 112, a storage space capable of accommodating various parts may be provided inside the main body 110.

The measurement unit 120 measures the weight of the user located on the main body 110 using the load cell 10 and measures the bio-signal of the user located on the main body 110 using the electrode 20. can For example, the load cell 10 is installed between the upper plate 111 and the lower plate 112 of the body part 110 to measure the weight of the user, and four load cells are provided at the corners of the body part 110. each can be provided. Although illustrated and described as having four load cells 10 in this embodiment, it is also possible that three load cells 10 are provided and circularly arranged at 120° intervals.

The electrode 20 is for measuring a biosignal by using contact resistance when both feet of the user come into contact with the electrode 20, and a part of the electrode 20 may be formed to be exposed to the outside of the top plate 111 of the main body 110. there is. For example, four electrodes 20 may be provided and spaced apart from each other in the front, rear, left, and right directions.

Meanwhile, the measurement unit 120 may include a temperature and humidity sensor 121 that measures ambient temperature and humidity. In this way, as the temperature and humidity of the surroundings can be further measured using the temperature and humidity sensor 121, there is no need to separately prepare a thermometer or a hygrometer, so there is an effect of increasing versatility.

The signal processing unit 130 may obtain a cardiac output (CO) of the user by using a reactance signal included in the biosignal. The signal processing unit 130 may send current to one foot and measure the time it takes for the current to reach the opposite foot, and then detect the cardiac output using a change in phase caused by a change in blood flow over the measured time.

For example, when a constant current is applied to the user's body using the electrode 20, an electrical signal that is changed to body fat, muscle, water content, basal metabolic rate, BMI, protein, bone density, blood flow, cardiac output, etc. is in the form of a voltage. can be output as The output voltage may be provided to a low pass filter (LPF) and a high pass filter (HPF) by passing through an IQ demodulator for analyzing the resistance of the human body. Then, the impedance signal may be extracted using the low pass filter (LPF) and the reactance signal may be extracted using the high pass filter (HPF). That is, a DC component is obtained using a low pass filter (LPF) and an AC component is obtained using a high pass filter (HPF). Here, if the signal passing through the low pass filter (LPF) is I _DC /Q _DC and the signal passing through the high pass filter (HPF) is I _AC /Q _AC , The final signal can be obtained by the following equation. Here, G is an amplification factor, which was set to 1,000 in this embodiment.

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[rad])을 구현할 수 있다. Using the IQ value measured in this way, the impedance phase signal conversion (Z [Ω]) and the reactance phase signal conversion (

[rad]) can be implemented.

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Cardiac Output (CO), an important index of cardiovascular disease, can be obtained by first and second differentiation of the converted time-series reactance value and then analyzing the waveform of the second differential signal. In addition, the heart rate (HR: Heartrate) is detected by detecting the peak value per minute of the time-series reactance first-order differential signal, and the heart rate variability (HRV: Heart Rate variability) is obtained through the deviation of the peak value per minute of the time-series reactance first-order differential signal. can do.

The application unit 140 may output the user's weight and cardiac output measured using the load cell 10 and the electrode 20 . For example, the body unit 110 may be provided with a display unit 150 for displaying the user's weight and cardiac output output from the application unit 140, and the user may display the weight output to the display unit 150. Cardiovascular disease can be self-managed by monitoring heart rate and cardiac output. In addition, a speaker 160 may be further provided in the main body 110 to output the measured weight or cardiac output as a voice, and a warning signal may be output when the cardiac output exceeds a standard range and is determined to be a risk factor. there is.

According to the present invention, the signal processing unit 130 calculates the position of the center of position (COP) of the user based on the pressure applied to each load cell 10, and the center of gravity (COP) is a predetermined area If it is out of range, a warning signal can be output. That is, by guiding the user to position both feet in an accurate measurement area, the reliability of the measurement result is improved.

This is because, since the cardiac output monitoring device 100 is provided in the form of a weight scale, the contact area of the electrode 20 may vary depending on the position where the user stands. In this case, when the contact area is different, even if the measurement is performed with the same electrode 20, the resistance may change according to the contact area with the electrode 20, which may affect the measured value. Therefore, since measurement is possible only when the position of the user's feet located on the main body 110 is placed in an accurate measurement area, it is possible to obtain an accurate measurement value for cardiac output, and it is possible to use it without the help of an expert, allowing self-reliance. It has a measurable effect.

6 is a view for explaining a process of calculating the position of the center of gravity using the load cell of FIG. 1; Further, FIG. 7(a) is a diagram showing a case in which the center of gravity is located within a preset area, and FIGS. 7(b) to (d) are diagrams showing a case in which the center of gravity is located outside the preset area.

Referring to FIG. 6 , the measurement of the center of gravity (COP) using four load cells 10 may be obtained by the following equation. Here, Fz is the total sum of the load cells 10 measured at four corners, COP _x is the center of gravity in the X axis, and COP _y is the center of gravity in the Y axis.

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After obtaining the position of the center of gravity (COP _xy ) using this calculation formula, the cardiac output may be induced to be measured only when the center of gravity (COP _xy ) is located within the predetermined area (A). For example, as shown in FIG. 7(a), when the user's center of gravity (COP) is located within the existing region (A), the measurement of cardiac output starts, and FIGS. 7(b) to 7(d) As shown in ), when the user's center of gravity (COP) is located outside the preset area (A), a warning signal may be output to guide the user's foot position to an accurate measurement area.

8(a) is a diagram showing a case in which the distribution of the center of gravity is located within a preset range, and FIG. 8(b) is a diagram showing a case in which the distribution of the center of gravity is located outside the preset range.

As shown in FIG. 8 , when the user moves on the main body 110, the position of the center of gravity COP may change. If the distribution of the center of gravity (COP) is large, since there is a possibility that the user lifted and moved his foot from the body part 110 during measurement, even if the user's foot is within the preset area (A), the distribution of the center of gravity (COP) There is a need for a plan to request a re-measurement accordingly.

To this end, the signal processing unit 130 may detect the user's movement by measuring the distribution of the center of gravity (COP) during the measurement time, and output a warning signal when the distribution of the center of gravity (COP) exceeds a preset range. there is. For example, if the distribution of the user's center of gravity (COP) is within a preset range (B) as shown in FIG. When the distribution of the center of gravity (COP) is outside the predetermined range (B), measurement of the biosignal is stopped and a warning signal is output to induce remeasurement. This warning signal may be output to the outside through the display unit 150 or the speaker 160, and the preset range (B) may vary depending on the size of the body unit 110, the size and spacing of the electrodes 20, and the like. can

The biosignal measured by the scale-type reactance cardiac output monitoring device 100 is at least one of an impedance signal, an electrocardiography (ECG) signal, a ballistocardiography (BCG) signal, and an impedance plethysmography (IPG) signal. may further include. At this time, in the case of an electrocardiogram (ECG), since the electrical activity of the heart is measured at the feet, the muscles are relaxed when the user is sitting, but when the user is standing, the muscles are contracted, so the EMG signal is introduced as noise. Accurate measurements can be difficult. In order to solve this problem, the signal processing unit 130 takes samples of a certain section from the front and back based on the peak measured in the first-order differentiated reactance conversion signal, sums them up, and takes the average to reduce noise caused by EMG. and an ensemble ECG signal, which is a periodic signal, can be obtained.

According to the present invention, the signal processing unit 130 uses an electrocardiogram signal and a reactance signal to determine a pulse arrival time (PAT), a pulse transit time (PTT), and a pre- ejection period) can be obtained more. For example, the pulse wave arrival time (PAT) can be detected using the time difference between the signals measured at the forefoot and heel of the sole, and the pulse wave transit time (PAT) using the difference in time measured from one sole to the other sole. PTT) can be detected, and PEP can be detected using the peak point of the time-series reactance signal and the peak point of the electrocardiogram.

In addition, the application unit 140 calculates systemic vascular resistance (SVR), central venous pressure (CVP), mean arterial pressure (MAP), At least one of systolic blood pressure (SBP) and diastolic blood pressure (DBP) may be output. For example, systemic vascular resistance (SVR) can be detected using the pulse wave transit time, and central blood pressure (CVP) and mean blood pressure (MAP) can be detected using a formula of cardiac output x vascular resistance. In addition, the systolic blood pressure (SBP) and the diastolic blood pressure (DBP) may be detected using cardiac output signals that change in real time.

9 is a diagram illustrating a body composition table output through an application unit.

Referring to FIG. 9 , the scale-type reactance cardiac output monitoring apparatus 100 may analyze and output body composition using body information, weight, and impedance signals of the user. To this end, the scale-type reactance cardiac output monitoring apparatus 100 may further include an input unit capable of inputting user's body information. For example, the input unit may be provided as a button type on one side of the body unit 110 or as a remote control type capable of transmitting data to the cardiac output monitoring device 100 side.

Accordingly, when body information including the user's height and age is input through the input unit, the application unit 140 uses the user's body information, weight, and an impedance signal included in the biosignal to determine body composition ( body composition) can be analyzed and output.

As described above, the scale-type reactance cardiac output monitoring device 100 is provided as a weight scale type including a load cell 10 and an electrode 20, and measures weight and cardiac output when a user climbs on the main body 110. It has the advantage of being able to measure simultaneously.

In addition, when the user's weight and cardiac output are continuously monitored through the cardiac output monitoring device 100, cardiovascular diseases can be self-managed and prevented.

In addition, the position of the user's center of position (COP) is calculated using a plurality of load cells 10 provided in the body unit 110, and a warning signal is issued when the center of gravity (COP) is out of a preset area. By being provided to output, it is possible to improve the reliability of the measurement result by guiding the user to place both feet in the accurate measurement area.

In addition, since cardiac output, heart rate, heart rate variability, pulse wave arrival time, pulse wave transit time, and stroke electrical power can be simultaneously measured using the measured biosignal, cardiovascular diseases can be managed more effectively.

10 is a flow chart of a weight scale-type reactance cardiac output monitoring method according to an embodiment of the present invention. In this embodiment, a description will be made focusing on differences from the previous embodiment.

Referring to FIG. 10 , the scale-type reactance cardiac output monitoring method (S100) includes measuring a user's weight (S110), calculating the position of the user's center of gravity (COP) (S120), and Outputting a warning signal when out of the preset area (S130), measuring the user's bio-signal (S140), acquiring the user's cardiac output (CO: Cardiac Output) (S150), and weight and outputting cardiac output (S160).

In the step of measuring the user's weight (S110), the user's weight may be measured using a plurality of load cells 10 provided in the main body 110. For example, the user's weight can be measured by the total sum of the four load cells 10 provided at the corners of the main body 110 .

In the step of calculating the position of the user's center of gravity (COP) (S120), the position of the user's center of position (COP) may be calculated based on the pressure applied to each load cell 10. For example, the COP _xy value can be obtained by the following equation.

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In the step of outputting a warning signal when the center of gravity is out of the preset area (S130), it is determined whether the center of gravity (COP) is within the preset area, and a warning signal is output when the center of gravity (COP) is out of the preset area. can do. When the warning signal is output in this way, the user can move the position of both feet so that both feet are located in the accurate measurement area.

In the step of measuring the user's bio-signal ( S140 ), the user's bio-signal located on the main body 110 may be measured using the electrode 20 provided on the main body 110 . For example, at least one of a reactance signal, an impedance signal, an electrocardiography (ECG) signal, a ballistocardiography (BCG) signal, and an impedacne plethysmography (IPG) signal using the electrode 20 vital signs can be measured. At this time, the user's movement is detected by measuring the distribution of the center of gravity (COP) during the measurement time, and when the distribution of the center of gravity (COP) exceeds a preset range, a warning signal for re-measurement may be output.

In the step of acquiring the user's cardiac output (CO) (S150), the user's cardiac output (CO) may be obtained using a reactance signal included in the biosignal. In addition, by using at least one of the electrocardiogram signal and the reactance signal, the user's heart rate (HR: Heartrate), heart rate variability (HRV: Heart Rate variability), PAT: Pulse arrival time, PTT: Pulse Transit Time), and pre-ejection period (PEP) may be further acquired.

In the step of outputting the weight and cardiac output ( S160 ), the user's weight and cardiac output measured by the load cell 10 and the electrode 20 may be externally output. Accordingly, the user can self-manage and prevent cardiovascular diseases by continuously monitoring the output weight and cardiac output.

The present invention has been described with reference to an embodiment shown in the accompanying drawings, but this is only exemplary, and those skilled in the art will understand that various modifications and equivalent other embodiments are possible therefrom. You will be able to. Therefore, the true protection scope of the present invention should be defined only by the appended claims.

10: load cell
20: electrode
110: body part
120: measuring unit
130: signal processing unit
140: application unit
150: display unit
160: speaker

Claims (15)

A body portion provided with a plurality of load cells and electrodes;
a measurement unit for measuring a weight of a user positioned on the main body using the load cell and measuring a biosignal of the user positioned on the main body using the electrode;
a signal processor configured to obtain a cardiac output (CO) of the user by using a reactance signal included in the bio-signal; and
An application unit outputting the weight and the cardiac output;
The signal processing unit calculates the position of the center of position (COP) of the user based on the pressure applied to each load cell, and outputs a warning signal when the center of gravity is out of a preset area, so that the user Guide the feet to be located in the measurement area,
The signal processor detects the user's movement by measuring the distribution of the center of gravity (COP) during the measurement time, and outputs a warning signal when the distribution of the center of gravity (COP) exceeds a preset range to perform re-measurement. A scale-type reactance cardiac output monitoring device that induces
According to claim 1,
The weight scale-type reactance cardiac output monitoring device of claim 1 , wherein the body portion is formed in a rectangular plate shape, and four load cells are provided and provided at corners of the body portion, respectively.
According to claim 1,
The weight scale-type reactance cardiac output monitoring device of claim 1 , wherein a portion of the electrode is exposed to the outside of the main body unit, and the measurement unit measures a biosignal using contact resistance when both feet of the user come into contact with the electrode.
delete According to claim 1,
The signal processing unit extracts an impedance signal using a low pass filter (LPF) and extracts the reactance signal using a high pass filter (HPF).
According to claim 1,
The weight scale-type reactance cardiac output monitoring device of claim 1 , wherein the signal processing unit further acquires a heart rate (HR) and a heart rate variability (HRV) of the user using the reactance signal.
According to claim 1,
The biosignal further comprises at least one of an impedance signal, an electrocardiography (ECG) signal, a ballistocardiography (BCG) signal, and an impedance plethysmography (IPG) signal.
According to claim 7,
The signal processing unit further calculates a pulse arrival time (PAT), a pulse transit time (PTT), and a pre-ejection period (PEP) using the electrocardiogram signal and the reactance signal. A scale-type reactance cardiac output monitoring device to obtain.
According to claim 8,
The application unit calculates systemic vascular resistance (SVR), central venous pressure (CVP), mean arterial pressure (MAP), and systolic blood pressure (calculated using the cardiac output and the pulse wave transit time). A scale-type reactance cardiac output monitoring device that outputs at least one of Systolic Blood Pressure (SBP) and Diastolic Blood Pressure (DBP).
According to claim 1,
An input unit capable of inputting the user's body information is further included, and the application unit analyzes and outputs body composition using the user's body information, the weight, and an impedance signal included in the bio-signal. Weight scale-type reactance cardiac output monitoring device.
According to claim 1,
The weight scale-type reactance cardiac output monitoring device further comprising a temperature and humidity sensor for measuring ambient temperature and humidity.
A weight scale-type reactance cardiac output monitoring method comprising the weight scale-type reactance cardiac output monitoring device of claim 1,
Measuring the user's weight using a plurality of load cells provided in the main body in the measuring unit;
Calculating a position of a center of position (COP) of the user based on a pressure applied to each load cell by a signal processing unit;
determining whether the center of gravity is within a predetermined area in a signal processing unit and outputting a warning signal when the center of gravity is out of the predetermined area;
measuring a biosignal of the user located on the main body by using an electrode provided in the main body by a measuring unit;
acquiring a cardiac output (CO) of the user by using a reactance signal included in the bio-signal in a signal processing unit; and
outputting the measured weight and cardiac output in an application unit;
Weight scale reactance cardiac output monitoring method comprising a.
According to claim 12,
The step of measuring the user's bio-signal,
A weight scale-type reactance cardiac output monitoring method for detecting motion of the user by measuring the distribution of the center of gravity for a measurement time, and outputting a warning signal when the distribution of the center of gravity exceeds a predetermined range.
According to claim 12,
The biosignal further comprises at least one of an impedance signal, an electrocardiography (ECG) signal, a ballistocardiography (BCG) signal, and an impedacne plethysmography (IPG) signal. Method for monitoring cardiac output.
According to claim 14,
Using at least one of the electrocardiogram signal and the reactance signal, the user's heart rate (HR: Heartrate), heart rate variability (HRV), pulse arrival time (PAT), pulse wave transit time (PTT: A weight scale-type reactance cardiac output monitoring method further acquiring a pulse transit time (PEP) and a pre-ejection period (PEP).

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