CN109199349B - Electrocardiogram pulse monitoring closestool and blood pressure acquisition method thereof - Google Patents
Electrocardiogram pulse monitoring closestool and blood pressure acquisition method thereof Download PDFInfo
- Publication number
- CN109199349B CN109199349B CN201811108041.7A CN201811108041A CN109199349B CN 109199349 B CN109199349 B CN 109199349B CN 201811108041 A CN201811108041 A CN 201811108041A CN 109199349 B CN109199349 B CN 109199349B
- Authority
- CN
- China
- Prior art keywords
- pulse
- curve
- effective peak
- ith
- blood pressure
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Active
Links
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/02—Detecting, measuring or recording pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure
- A61B5/0205—Simultaneously evaluating both cardiovascular conditions and different types of body conditions, e.g. heart and respiratory condition
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/0002—Remote monitoring of patients using telemetry, e.g. transmission of vital signals via a communication network
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/02—Detecting, measuring or recording pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/02—Detecting, measuring or recording pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure
- A61B5/021—Measuring pressure in heart or blood vessels
- A61B5/02108—Measuring pressure in heart or blood vessels from analysis of pulse wave characteristics
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/02—Detecting, measuring or recording pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure
- A61B5/024—Detecting, measuring or recording pulse rate or heart rate
- A61B5/0245—Detecting, measuring or recording pulse rate or heart rate by using sensing means generating electric signals, i.e. ECG signals
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
- A61B5/316—Modalities, i.e. specific diagnostic methods
- A61B5/318—Heart-related electrical modalities, e.g. electrocardiography [ECG]
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
- A61B5/6887—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient mounted on external non-worn devices, e.g. non-medical devices
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/74—Details of notification to user or communication with user or patient ; user input means
- A61B5/746—Alarms related to a physiological condition, e.g. details of setting alarm thresholds or avoiding false alarms
-
- Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y02—TECHNOLOGIES OR APPLICATIONS FOR MITIGATION OR ADAPTATION AGAINST CLIMATE CHANGE
- Y02A—TECHNOLOGIES FOR ADAPTATION TO CLIMATE CHANGE
- Y02A50/00—TECHNOLOGIES FOR ADAPTATION TO CLIMATE CHANGE in human health protection, e.g. against extreme weather
- Y02A50/30—Against vector-borne diseases, e.g. mosquito-borne, fly-borne, tick-borne or waterborne diseases whose impact is exacerbated by climate change
Landscapes
- Health & Medical Sciences (AREA)
- Life Sciences & Earth Sciences (AREA)
- Engineering & Computer Science (AREA)
- Heart & Thoracic Surgery (AREA)
- Public Health (AREA)
- Veterinary Medicine (AREA)
- Biophysics (AREA)
- Pathology (AREA)
- Physics & Mathematics (AREA)
- Biomedical Technology (AREA)
- Cardiology (AREA)
- Medical Informatics (AREA)
- Molecular Biology (AREA)
- Surgery (AREA)
- Animal Behavior & Ethology (AREA)
- General Health & Medical Sciences (AREA)
- Physiology (AREA)
- Pulmonology (AREA)
- Computer Networks & Wireless Communication (AREA)
- Signal Processing (AREA)
- Vascular Medicine (AREA)
- Measurement And Recording Of Electrical Phenomena And Electrical Characteristics Of The Living Body (AREA)
- Measuring Pulse, Heart Rate, Blood Pressure Or Blood Flow (AREA)
Abstract
The invention discloses an electrocardiograph pulse monitoring closestool and a blood pressure acquisition method thereof. Part of people with poor conditions are easy to raise blood pressure and expand arteries in the toilet, and serious vascular rupture and sudden death can be caused. The invention relates to an electrocardio pulse monitoring closestool which comprises a handle, a pulse sensor, a first electrode plate, a second electrode plate, a third electrode plate and an information processing circuit. The pulse sensor is arranged at the outer end of the handle. The first electrode plate is arranged in the middle of the handle. The second electrode plate and the third electrode plate are arranged on the toilet seat. The information processing circuit comprises a voltage stabilizing circuit, a pulse signal filtering circuit, an electrocardio acquisition circuit and a controller. The pulse signal filtering circuit filters the pulse signal and transmits the pulse signal to the controller; the electrocardio signal is converted into a digital signal by the electrocardio acquisition circuit and then is transmitted to the controller. The invention can realize real-time accurate detection of the electrocardio, pulse and blood pressure of the user and has good monitoring effect on the physical health of the user.
Description
Technical Field
The invention belongs to the technical field of physiological signal processing, and particularly relates to an electrocardiographic pulse monitoring closestool and a blood pressure acquisition method thereof.
Background
Along with the progress of science and technology, the toilets also change day and month, and various intelligent toilets are continuously emerging. Intelligent toilets incorporate various technologies such as electronics, integrated circuits, communication technologies, etc. in combination with human health detection are a trend in the development of modern intelligent toilets.
The physiological health monitoring system in the home environment can not only share the medical expense with high cost, but also further detect the sign of health abnormality through long-term continuous health monitoring data, become the first line of defense for health and medical treatment, and medical services become more active preventive medical treatment from passive treatment and first aid. Many scholars have proposed combining the functionality of physiological monitoring with living goods or the surrounding environment to record changes in physiological parameters over a long period of time with non-perceptible measurement methods.
In life, the phenomenon that people are heard and stated to die suddenly in the process of going to a toilet is common, and the phenomenon is more common among the old. The sudden death is caused by the fact that some heart patients exert too much force when using the toilet, so that the blood pressure is increased, arteries are expanded, and finally blood vessels are ruptured to sudden death. Therefore, in the toilet process, the blood pressure of a person who uses the toilet is monitored in real time, and when the blood pressure of the person is at risk, the person can be reminded and warned in time, so that the heart disease patient can be prevented and cured in time.
The existing human body continuous blood pressure measuring method can be divided into an invasive measuring method and a non-invasive measuring method. Arterial catheterization is considered to be a "gold standard" for invasive continuous blood pressure acquisition, which involves inserting a catheter connected to a pressure sensor into the aorta or heart to monitor blood pressure signals, thereby achieving continuous blood pressure measurement, but is a limitation. The noninvasive continuous blood pressure acquisition method comprises an arterial tension method, a volume compensation method, a pulse wave conduction time measurement method and the like. The pulse wave conduction time method is convenient to measure, high in comfort level and ideal in effect. In recent years, scholars at home and abroad have made a great deal of researches on pulse wave transit time measurement methods, aiming at improving measurement accuracy so as to achieve clinical effects.
Disclosure of Invention
The invention aims to provide an electrocardiographic pulse monitoring closestool and a blood pressure acquisition method thereof.
The invention relates to an electrocardio pulse monitoring closestool which comprises a handle, a pulse sensor, a first electrode plate, a second electrode plate, a third electrode plate and an information processing circuit. The handle is arranged on one side of the closestool. The pulse sensor is arranged at the outer end of the handle. The first electrode plate is arranged in the middle of the handle. The second electrode plate and the third electrode plate are arranged on the toilet seat.
The information processing circuit comprises a voltage stabilizing circuit, a pulse signal filtering circuit, an electrocardio acquisition circuit and a controller. The voltage stabilizing circuit supplies power for the pulse signal filtering circuit, the electrocardio acquisition circuit and the controller. The pulse signal filtering circuit comprises a first three-wire plug-in connector and an amplifier. The first wiring of the first three-wire connector is connected with one end of the resistor R301 and one end of the capacitor C301. The other end of the resistor R301 is connected to one end of the resistor R302, the capacitor C303 and the capacitor C304. The other ends of the capacitor C303 and the capacitor C304 are grounded. The other end of the capacitor C301 is connected to one end of the resistor R303, the resistor R304, and the capacitor C302. The other ends of the resistor R302 and the capacitor C302 are connected with the non-inverting input end of the amplifier. The other ends of the resistor R303 and the resistor R304 are connected with the inverting input end and the output end of the amplifier. The second terminal of the first three-wire connector and the positive supply voltage terminal of the amplifier are both connected with the voltage output terminal of the voltage stabilizing circuit. The third wiring end of the first three-wire connector and the negative power supply voltage end of the amplifier are grounded. The first wiring end, the second wiring end and the third wiring end of the first three-wire plug connector are respectively connected with a signal output pin, a power supply pin and a ground wire pin of the pulse sensor. The output end of the amplifier is a pulse signal output end of the pulse signal filter circuit and is connected with a digital-to-analog conversion pin of the controller.
The electrocardio acquisition circuit comprises a heart rate acquisition chip and a second three-wire plug connector. The SEP pin of the heart rate acquisition chip is connected with the second wiring end of the second three-wire plug connector, the SEN pin is connected with the third wiring end of the second three-wire plug connector, the GND pin is grounded, and the VDD pin is connected with the voltage output end. The first wiring terminal of the second three-wire plug connector is grounded. The first terminal, the second terminal and the third terminal of the second three-wire connector are respectively and electrically connected with the first electrode slice, the second electrode slice and the third electrode slice. RX pins and TX pins of the heart rate acquisition chip are electrocardio signal output pins of an electrocardio acquisition circuit and are respectively connected with a UART serial port signal transmitting pin and a UART serial port signal receiving pin of the controller.
Further, the information processing circuit also comprises a wireless transmission module. The wireless transmission module is connected with the controller and is in wireless communication with the upper computer. The model of the heart rate acquisition chip is BMD101. The model of the pulse sensor is PulseSensor. The controller adopts a singlechip of model STM32F 103.
Further, the voltage stabilizing circuit comprises a voltage stabilizing chip and a two-wire plug connector. The model of the voltage stabilizing chip is SGM2020-3.3. The pins 1 and 2 of the voltage stabilizing chip are connected with one end of the capacitor C201 and one wiring end of the two-wire plug connector. The 3 pins of the voltage stabilizing chip, the other end of the capacitor C201 and the other wiring end of the two-wire plug connector are all grounded. The voltage stabilizing chip has 4 pins connected to one end of the capacitor C202 and 5 pins connected to one end of the capacitor C203. The other ends of the capacitor C202 and the capacitor C203 are grounded. The two-wire plug connector is connected with an external 5V power supply. The 5 pins of the voltage stabilizing chip are the voltage output ends of the voltage stabilizing circuit.
The method for acquiring the blood pressure of the electrocardiographic pulse monitoring closestool comprises the following steps of:
step one, a user needs to sit on the toilet seat to enable buttocks to be in contact with the second electrode plate and the third electrode plate, the thumb presses the detection head of the pulse sensor, and the arm or the palm is in contact with the first electrode plate.
And step two, continuously detecting pulse signals of the user by the pulse sensor, transmitting the pulse signals to the pulse signal filtering circuit for filtering, and transmitting the filtered pulse signals to the controller for digital-to-analog conversion. So that the controller obtains the pulse waveform graph curve of the user.
The second electrode plate and the third electrode plate continuously transmit the detected electrocardiosignals of the user to an electrocardiosignal acquisition circuit. The heart rate acquisition chip in the electrocardio acquisition circuit converts the received electrocardio signals into digital signals and transmits the digital signals to the controller, so that the controller obtains an electrocardiographic curve of a user.
And thirdly, assigning 1 to i.
And fourthly, continuously positioning the effective peak point of the electrocardiograph curve to obtain the effective peak position of the electrocardiograph curve. And (3) positioning an effective peak point of the pulse waveform graph curve to obtain an effective peak position of the pulse waveform graph curve.
After the ith effective peak point appears on the electrocardiogram curve ECG, determining the voltage level PPV of the ith effective peak point on the electrocardiogram curve ECG i And determining the effective peak point position of the pulse waveform graph corresponding to the ith effective peak point on the electrocardiogram graph. Calculate the userIth heart rate HR of (2) i ；HR i ＝1/T i ；T i Is the time difference between the i-th effective peak point and the i+1-th effective peak point on the electrocardiographic curve ECG, in minutes. Calculating the ith pulse wave conduction time PWTT i 。
Step five, according to the voltage PPV of the ith effective peak point on the ECG curve i Ith heart rate HR i And an ith pulse wave transit time PWTT i Calculation of the ith systolic pressure SBP i And ith diastolic blood pressure DBP i 。
Thereafter, the ith systolic pressure SBP i Ith diastolic blood pressure DBP i Respectively adding the blood pressure values into a blood pressure coordinate system with the time on the abscissa and the blood pressure value on the ordinate, and proceeding to the step six.
Step six, if the user leaves the toilet, the step seven is entered, otherwise, after i is increased by 1, the steps four and five are repeatedly executed.
And step seven, connecting discrete points corresponding to systolic pressure in the blood pressure coordinate system, and connecting discrete points corresponding to diastolic pressure in the blood pressure coordinate system to obtain a blood pressure change curve of the user in the toilet process.
Further, the ith systolic pressure SBP i The calculated expression of (1) is SBP i ＝k·PWTT i +t; ith diastolic blood pressure DBP i Is expressed as DBP i ＝a·PWTT i +b·HR i +c·PPV i +d。
k. t, a, b, c, d is determined in one of two ways.
Mode 1: k= -63, t= 110.897, a= -268.86, b=1.432, c=0.0056, d= 21.2948.
Mode 2: k. t, a, b, c, d is obtained by initializing matching by a user in the following way;
a user sits on the closestool to obtain n groups of electrocardio pulse data groups, wherein n is more than or equal to 3, and a sphygmomanometer is used for synchronously measuring systolic pressure and diastolic pressure. The electrocardio pulse data set comprises the voltage magnitude, the heart rate and the pulse wave conduction time of effective peak points on an electrocardiogram curve. N groups of electrocardio pulse data groupsAnd the corresponding n blood pressure values are substituted into SBP i ＝k·PWTT i +t and DBP i ＝a·PWTT i +b·HR i +c·PPV i +d is calculated and linear fitting is performed by least square method to obtain k, t, a, b, c, d.
Further, the ith pulse wave conduction time is the time difference between the ith effective peak point on the electrocardiogram curve and the corresponding effective peak point of the pulse waveform diagram curve. The method for matching the effective peak point on the electrocardiogram ECG with the effective peak point of the pulse waveform curve PPG is as follows: if the time of one effective peak point on the electrocardiogram curve ECG is earlier than the time of one effective peak point on the pulse waveform curve PPG and no other effective peak points of the electrocardiogram curve ECG and the other effective peak points on the pulse waveform curve PPG exist between the two points, the two points correspond to each other.
Further, the method for locating the effective peak point of the electrocardiographic curve ECG or the pulse waveform curve PPG is specifically as follows:
(1) The electrocardiographic curve ECG or the pulse waveform curve PPG is filtered, denoised and smoothed by wavelet threshold filtering.
(2) And (3) deriving the curve obtained after the treatment in the step (1) to obtain a derivative function curve. And solving zero point of the derivative function curve, thereby determining the positions of the maximum value point and the minimum value point of the curve obtained after the treatment in the step (1).
(3) And screening a primary fixed peak points from the extreme points. The initial peak point is a maximum point with an ordinate greater than S ', S' =k· (S max -S min )+S min The method comprises the steps of carrying out a first treatment on the surface of the Wherein S is max Is the maximum value of the ordinate among all the points obtained in (1); s is S min Is the minimum value of the ordinate among all the points obtained in (1). If the active peak point location is an electrocardiographic ECG, then k=2/3; if the effective peak point location is performed by the pulse waveform graph PPG, k=1/2.
(4) The a primary set peak points are divided into b primary valid peak groups. The time difference (abscissa interval) between any two adjacent initial fixed peak points in the same initial effective peak group is larger than X; x takes any value of 0.2-0.5 seconds.
(5) The initial peak point with the largest ordinate in each initial effective peak group is taken as an effective peak point; thus obtaining b effective peak points.
In the fifth step, if the ith systolic pressure is higher than the high pressure alarm preset value or the ith diastolic pressure is higher than the low pressure alarm preset value, the wireless transmission module sends an alarm signal to the upper computer. The high-pressure alarm preset value is equal to 146mmHg; the low-pressure alarm preset value is equal to 96mmHg.
The invention has the beneficial effects that:
1. the invention can realize real-time accurate detection of the electrocardio, pulse and blood pressure of the user and has good monitoring effect on the physical health of the user.
2. The invention collects signals in the toilet process of the user, and can realize the monitoring of each physiological data in a non-aware mode, so that the monitoring is simpler and more convenient.
3. The invention can give an alarm when the blood pressure of the user is too high, so that a caretaker can timely find the abnormality of the user, and further the danger caused by too great force of the user in the toilet process is avoided.
Drawings
FIG. 1 is a schematic diagram of the overall structure of the present invention;
FIG. 2 is a system block diagram of an information processing circuit according to the present invention;
FIG. 3 is a schematic circuit diagram of a voltage regulator circuit according to the present invention;
FIG. 4 is a schematic circuit diagram of a pulse signal filter circuit according to the present invention;
FIG. 5 is a schematic circuit diagram of a central electrical acquisition circuit of the present invention;
FIG. 6 is a diagram illustrating a pulse transit time determination according to the present invention.
Description of the embodiments
The invention is further described below with reference to the accompanying drawings.
As shown in fig. 1, an electrocardiographic pulse monitoring toilet comprises a toilet body 1, a toilet seat 2, a handle 3, a pulse sensor 4, a first electrode sheet 5, a second electrode sheet 6, a third electrode sheet 7 and an information processing circuit. The inner end of the toilet seat 2 and the toilet body 1 form a revolute pair. The inner end of the handle 3 is fixed with the toilet body 1. The handle 3 is arranged at one side of the toilet bowl and is arranged at the same height as the toilet seat 2. The pulse sensor 4 is arranged at the outer end of the handle 3. The first electrode sheet 5 is disposed in the middle of the handle 3. The second electrode piece 6 and the third electrode piece 7 are both arranged on the toilet seat 2. The pulse sensor 4 is of the type PulseSensor.
As shown in FIG. 2, the information processing circuit comprises a voltage stabilizing circuit 8-1, a pulse signal filtering circuit 8-2, an electrocardio acquisition circuit 8-3, a controller 8-4 and a wireless transmission module 8-5. The wireless transmission module 8-5 is connected with the controller 8-4 and is in wireless communication with the upper computer. The voltage stabilizing circuit 8-1 supplies power to the pulse signal filter circuit 8-2, the electrocardio acquisition circuit 8-3, the controller 8-4 and the wireless transmission module 8-5. The controller 8-4 adopts a singlechip of model STM32F 103. The pulse signal filtering circuit 8-2 filters the pulse signal transmitted by the pulse sensor and transmits the pulse signal to the controller; the electrocardiosignal transmitted by the second electrode plate and the third electrode plate is converted into a digital signal by the electrocardiosignal acquisition circuit 8-3 and then transmitted to the controller;
as shown in fig. 3, the voltage stabilizing circuit 8-1 includes a voltage stabilizing chip U2 and a two-wire plug connector P2. The model of the voltage stabilizing chip U2 is SGM2020-3.3. Pins 1 and 2 of the voltage stabilizing chip U2 are connected with one end of the capacitor C201 and one terminal of the two-wire plug connector P2. The 3 pin of the voltage stabilizing chip U2, the other end of the capacitor C201 and the other wiring end of the two-wire plug connector P2 are all grounded. The voltage stabilizing chip U2 has 4 pins connected to one end of the capacitor C202 and 5 pins connected to one end of the capacitor C203. The other ends of the capacitor C202 and the capacitor C203 are grounded. The two-wire plug connector P2 is connected with an external 5V power supply interface, so that pins 1 and 2 of the voltage stabilizing chip U2 are connected with 5V voltage. The 5 pin of the voltage stabilizing chip U2 is the voltage output end VDD of the voltage stabilizing circuit 8-1.
As shown in fig. 4, the pulse signal filtering circuit 8-2 includes a first three-wire plug P3 and an amplifier U3. The first connection terminal of the first three-wire plug P3 is connected to one end of the resistor R301 and one end of the capacitor C301. The other end of the resistor R301 is connected to one end of the resistor R302, the capacitor C303 and the capacitor C304. The other ends of the capacitor C303 and the capacitor C304 are grounded. The other end of the capacitor C301 is connected to one end of the resistor R303, the resistor R304, and the capacitor C302. The other ends of the resistor R302 and the capacitor C302 are connected with the non-inverting input end of the amplifier U3. The other ends of the resistor R303 and the resistor R304 are connected with the inverting input end and the output end of the amplifier U3. The second terminal of the first three-wire plug-in connector P3 and the positive supply voltage terminal of the amplifier U3 are connected with the voltage output terminal VDD of the voltage stabilizing circuit 8-1. The third terminal of the first three-wire plug-in connector P3 and the negative supply voltage terminal of the amplifier U3 are all grounded. The first terminal, the second terminal and the third terminal of the first three-wire plug connector P3 are respectively connected with a signal output pin, a power supply pin and a ground wire pin of the pulse sensor 4. The output end of the amplifier U3 is a pulse signal output end of the pulse signal filter circuit 8-2 and is connected with a digital-to-analog conversion pin of the controller 8-4.
As shown in fig. 5, the electrocardiograph acquisition circuit 8-3 includes a heart rate acquisition chip U4 and a second three-wire connector P4. The model of the heart rate acquisition chip U4 is BMD101. The SEP pin of the heart rate acquisition chip U4 is connected with the second wiring end of the second three-wire plug connector P4, the SEN pin is connected with the third wiring end of the second three-wire plug connector P4, the GND pin is grounded, and the VDD pin is connected with the voltage output end VDD. The first terminal of the second three-wire plug P4 is grounded. The first terminal, the second terminal, and the third terminal of the second three-wire connector P4 are electrically connected to the first electrode tab 5, the second electrode tab 6, and the third electrode tab 7, respectively. The RX pin and the TX pin of the heart rate acquisition chip U4 are electrocardio signal output pins of the electrocardio acquisition circuit 8-3 and are respectively connected with a UART serial port signal transmitting pin and a UART serial port signal receiving pin of the controller 8-4. The rest pins of the heart rate acquisition chip U4 are suspended.
The method for acquiring the blood pressure of the electrocardiographic pulse monitoring closestool comprises the following steps of:
step one, a user needs to sit on the toilet seat 2, so that the buttocks are contacted with the second electrode plate 6 and the third electrode plate 7, the thumb presses the detection head of the pulse sensor 4, and the arm or palm is contacted with the first electrode plate 5.
And step two, the pulse sensor 4 detects the pulse signal of the user through an infrared light volume scanning method, transmits the pulse signal to the pulse signal filtering circuit for filtering, and then transmits the pulse signal to the controller 8-4 for digital-to-analog conversion. So that the controller 8-4 obtains a pulse waveform of the user. The pulse waveform is updated continuously with the increase of the detection time.
The second electrode sheet 6 and the third electrode sheet 7 transmit the detected electrocardiographic signals of the user to the electrocardiograph acquisition circuit 8-3. The heart rate acquisition chip U4 in the electrocardio acquisition circuit 8-3 converts the received electrocardio signals into digital signals after transmission and processing and transmits the digital signals to the controller 8-4, so that the controller 8-4 obtains an electrocardiogram of a user. The electrocardiogram is continuously updated with the increase of the detection time.
And thirdly, assigning 1 to i.
And step four, continuously positioning effective peak points of the electrocardiogram curve ECG (namely determining the corresponding time of each peak point of the electrocardiogram curve) to obtain the effective peak positions of the electrocardiogram. And (3) carrying out effective peak point positioning on the pulse waveform graph PPG (namely determining the time corresponding to each peak of the pulse waveform graph) to obtain the effective peak position of the pulse waveform graph.
After the ith effective peak point appears on the electrocardiogram curve ECG, determining the voltage level PPV of the ith effective peak point on the electrocardiogram curve ECG i And determining the effective peak point position of the pulse waveform curve PPG corresponding to the ith effective peak point on the electrocardiogram curve ECG. Calculating the ith heart rate HR of the user i ；HR i ＝1/T i ；T i Is the time difference between the i-th effective peak point and the i+1-th effective peak point on the electrocardiographic curve ECG, in minutes. Calculating the ith pulse wave conduction time PWTT i . Ith pulse wave conduction time PWTT i Is the time difference between the i-th effective peak point on the electrocardiographic curve ECG and the effective peak point of the corresponding pulse waveform curve PPG.
The method for matching the effective peak point on the electrocardiogram ECG with the effective peak point of the pulse waveform curve PPG is as follows: if the time of one effective peak point on the ECG of the ECG trace is earlier than the time of one effective peak point on the PPG of the pulse waveform trace and there is no other effective peak point of the ECG trace and no other effective peak point on the PPG of the pulse waveform trace between them, the two (the effective peak point on the ECG trace and the effective peak point on the PPG of the pulse waveform trace) correspond to each other.
The method for positioning the effective peak point of the electrocardiogram curve ECG or the pulse waveform curve PPG specifically comprises the following steps:
(1) The electrocardiographic curve ECG or the pulse waveform curve PPG is filtered, denoised and smoothed by wavelet threshold filtering.
(2) And (3) deriving the curve obtained after the treatment in the step (1) to obtain a derivative function curve. And solving zero point of the derivative function curve, thereby determining the positions of the maximum value point and the minimum value point of the curve obtained after the treatment in the step (1).
(3) And screening a primary fixed peak points from the extreme points. The initial peak point is a maximum point with an ordinate greater than S ', S' =k· (S max -S min )+S min The method comprises the steps of carrying out a first treatment on the surface of the Wherein S is max Is the maximum value of the ordinate among all the points obtained in (1); s is S min Is the minimum value of the ordinate among all the points obtained in (1). If the active peak point location is an electrocardiographic ECG, then k=2/3; if the effective peak point location is performed by the pulse waveform graph PPG, k=1/2. Thereby excluding P-waves, T-waves in the electrocardiographic curve ECG and dicrotic waves in the pulse waveform curve PPG.
(4) The a primary set peak points are divided into b primary valid peak groups. The time difference (abscissa distance) between any two adjacent initial fixed peak points in the same initial effective peak group is smaller than X; x takes any value of 0.2-0.5 seconds.
(5) The initial peak point with the largest ordinate in each initial effective peak group is taken as an effective peak point; thus obtaining b effective peak points.
Step five, as shown in FIG. 6, according to the voltage level PPV of the ith effective peak point on the ECG trace ECG i Ith heart rate HR i And an ith pulse wave transit time PWTT i Calculation of the ith systolic pressure SBP i And ith diastolic blood pressure DBP i And the ith systolic pressure SBP i Ith diastolic blood pressure DBP i Respectively adding the blood pressure values into a blood pressure coordinate system with the time on the abscissa and the blood pressure value on the ordinate.
Ith systolic pressure SBP i The calculated expression of (1) is SBP i ＝k·PWTT i +t; ith diastolic blood pressure DBP i Is expressed as DBP i ＝a·PWTT i +b·HR i +c·PPV i +d。
If the ith systolic pressure is higher than the high pressure alarm preset value or the ith diastolic pressure is higher than the low pressure alarm preset value, the wireless transmission module 8-5 sends an alarm signal to the upper computer, so that a caretaker is informed of curing the user in time, and the high pressure alarm preset value is equal to 146mmHg; the low-pressure alarm preset value is equal to 96mmHg. And then step six is entered. Otherwise, directly enter step six.
k. t, a, b, c, d is determined in one of two ways.
Mode 1: fitting is performed according to the R peak (effective peak) sizes of a large number of systolic pressures, diastolic pressures, heart rates and electrocardiosignals measured in the existing database, so as to obtain k= -63, t= 110.897, a= -268.86, b=1.432, c=0.0056 and d= 21.2948.
Mode 2: k. t, a, b, c, d by user initiated matching, the matching is as follows:
a user sits on the closestool to obtain n groups of electrocardio pulse data groups, wherein n is more than or equal to 3, and a sphygmomanometer is used for synchronously measuring systolic pressure and diastolic pressure. The electrocardio pulse data set comprises the voltage magnitude, the heart rate and the pulse wave conduction time of effective peak points on an electrocardiogram curve. Substituting n groups of electrocardiographic pulse data groups and corresponding n blood pressure values into SBP i ＝k·PWTT i +t and DBP i ＝a·PWTT i +b·HR i +c·PPV i +d is calculated and linear fitting is performed by least square method to obtain k, t, a, b, c, d.
Step six, if the user leaves the toilet (i.e. the first electrode sheet 5, the second electrode sheet 6 and the third electrode sheet 7 cannot detect the electrocardiosignal, and the pulse sensor 4 cannot detect the pulse signal of the user), step seven is entered, otherwise, after i is increased by 1, the steps four and five are repeatedly executed.
And step seven, connecting discrete points corresponding to systolic pressure in the blood pressure coordinate system through a smooth curve, and connecting discrete points corresponding to diastolic pressure in the blood pressure coordinate system through a smooth curve to obtain a blood pressure change curve of a user in the toilet process, so as to assist doctors in judging illness states.
Claims (5)
1. A blood pressure acquisition method of an electrocardiographic pulse monitoring closestool is characterized by comprising the following steps of: the adopted equipment comprises a closestool, a handle, a pulse sensor, a first electrode plate, a second electrode plate, a third electrode plate and an information processing circuit; the handle is arranged on one side of the closestool; the pulse sensor is arranged at the outer end of the handle; the first electrode plate is arranged in the middle of the handle; the second electrode plate and the third electrode plate are arranged on the toilet seat;
the information processing circuit comprises a voltage stabilizing circuit, a pulse signal filtering circuit, an electrocardio acquisition circuit and a controller; the voltage stabilizing circuit supplies power to the pulse signal filter circuit, the electrocardio acquisition circuit and the controller; the pulse signal filtering circuit comprises a first three-wire plug connector and an amplifier; the first wiring of the first three-wire plug connector is connected with one end of a resistor R301 and one end of a capacitor C301; the other end of the resistor R301 is connected with one end of the resistor R302, the capacitor C303 and the capacitor C304; the other ends of the capacitor C303 and the capacitor C304 are grounded; the other end of the capacitor C301 is connected with one end of the resistor R303, the resistor R304 and the capacitor C302; the other ends of the resistor R302 and the capacitor C302 are connected with the non-inverting input end of the amplifier; the other ends of the resistor R303 and the resistor R304 are connected with the inverting input end and the output end of the amplifier; the second wiring end of the first three-wire connector and the positive power supply voltage end of the amplifier are both connected with the voltage output end of the voltage stabilizing circuit; the third wiring end of the first three-wire connector and the negative power supply voltage end of the amplifier are grounded; the first wiring end, the second wiring end and the third wiring end of the first three-wire connector are respectively connected with a signal output pin, a power supply pin and a ground wire pin of the pulse sensor; the output end of the amplifier is a pulse signal output end of the pulse signal filter circuit and is connected with a digital-to-analog conversion pin of the controller;
the electrocardio acquisition circuit comprises a heart rate acquisition chip and a second three-wire plug connector; the SEP pin of the heart rate acquisition chip is connected with the second wiring end of the second three-wire plug connector, the SEN pin is connected with the third wiring end of the second three-wire plug connector, the GND pin is grounded, and the VDD pin is connected with the voltage output end; the first wiring terminal of the second three-wire plug connector is grounded; the first wiring end, the second wiring end and the third wiring end of the second three-wire connector are respectively and electrically connected with the first electrode slice, the second electrode slice and the third electrode slice; the RX pin and the TX pin of the heart rate acquisition chip are electrocardio signal output pins of an electrocardio acquisition circuit and are respectively connected with a UART serial port signal transmitting pin and a UART serial port signal receiving pin of the controller;
the blood pressure acquisition method of the closestool specifically comprises the following steps:
step one, a user needs to sit on a toilet seat so that buttocks are contacted with a second electrode plate and a third electrode plate, a thumb presses a detection head of a pulse sensor, and an arm or a palm is contacted with a first electrode plate;
step two, the pulse sensor continuously detects the pulse signal of the user, and transmits the pulse signal to the pulse signal filter circuit for filtering and then transmits the pulse signal to the controller for digital-to-analog conversion; so that the controller obtains the pulse waveform graph curve of the user;
the second electrode plate and the third electrode plate continuously transmit the detected electrocardiosignals of the user to an electrocardiosignal acquisition circuit; the heart rate acquisition chip in the electrocardio acquisition circuit converts the received electrocardio signals into digital signals and transmits the digital signals to the controller, so that the controller obtains an electrocardiographic curve of a user;
step three, assigning 1 to i;
continuously positioning an effective peak point of the electrocardiograph curve to obtain an effective peak position of the electrocardiograph curve; positioning an effective peak point of the pulse waveform graph curve to obtain an effective peak position of the pulse waveform graph curve;
after the ith effective peak point appears on the electrocardiogram curve ECG, determining the voltage level PPV of the ith effective peak point on the electrocardiogram curve ECG i Determining the effective peak point position of the pulse waveform graph corresponding to the ith effective peak point on the electrocardiogram graph; calculating the ith heart rate HR of the user i ；HR i ＝1/T i ；T i Is the time difference between the ith effective peak point and the (i+1) th effective peak point on the electrocardiogram curve ECG, and is expressed in minutes; calculating the ith pulse wave conduction time PWTT i ；
Step five, according to the voltage PPV of the ith effective peak point on the ECG curve i Ith heart rate HR i And an ith pulse wave transit time PWTT i Calculation of the ith systolic pressure SBP i And ith diastolic blood pressure DBP i ；
Thereafter, the ith systolic pressure SBP i Ith diastolic blood pressure DBP i Respectively adding the blood pressure values into a blood pressure coordinate system with the time on the abscissa and the blood pressure value on the ordinate, and entering a step six;
step six, if the user leaves the toilet, entering a step seven, otherwise, after increasing i by 1, repeating the steps four and five;
step seven, connecting discrete points corresponding to systolic pressure in a blood pressure coordinate system, and connecting discrete points corresponding to diastolic pressure in the blood pressure coordinate system;
wherein the ith systolic pressure SBP i The calculated expression of (1) is SBP i ＝k·PWTT i +t; ith diastolic blood pressure DBP i Is expressed as DBP i ＝a·PWTT i +b·HR i +c·PPV i +d；
k. t, a, b, c, d is determined according to one of the following two value modes;
mode 1: k= -63, t= 110.897, a= -268.86, b=1.432, c=0.0056, d= 21.2948;
mode 2: k. t, a, b, c, d is obtained by initializing matching by a user in the following way;
a user sits on the closestool to obtain n groups of electrocardiograph pulse data groups, wherein n is more than or equal to 3, and a sphygmomanometer is used for synchronously measuring systolic pressure and diastolic pressure; the electrocardio pulse data set comprises voltage magnitude, heart rate and pulse wave conduction time of effective peak points on an electrocardiogram curve; substituting n groups of electrocardiographic pulse data groups and corresponding n blood pressure values into SBP i ＝k·PWTT i +t and DBP i ＝a·PWTT i +b·HR i +c·PPV i +d, calculate, andlinear fitting is carried out through a least square method to obtain a k, t, a, b, c, d value;
the method for positioning the effective peak point of the electrocardiogram curve ECG or the pulse waveform curve PPG specifically comprises the following steps:
(1) Filtering, denoising and smoothing the electrocardiogram curve ECG or pulse waveform curve PPG by a wavelet threshold filtering method;
(2) Deriving the curve obtained after the treatment in the step (1) to obtain a derivative function curve; solving zero point of the derivative function curve, thereby determining the positions of the maximum value point and the minimum value point of the curve obtained after the treatment in the step (1);
(3) Screening a primary fixed peak points from the extreme points; the initial peak point is a maximum point with an ordinate greater than S ', S' =k· (S max -S min )+S min The method comprises the steps of carrying out a first treatment on the surface of the Wherein S is max Is the maximum value of the ordinate among all the points obtained in (1); s is S min A value of (1) which is the smallest ordinate among all the points obtained; if the active peak point location is an electrocardiographic ECG, then k=2/3; if the effective peak point positioning is performed by the pulse waveform graph curve PPG, k=1/2;
(4) Dividing a primary fixed peak points into b primary effective peak groups; the time difference (abscissa interval) between any two adjacent initial fixed peak points in the same initial effective peak group is larger than X; x takes any value of 0.2-0.5 seconds;
(5) The initial peak point with the largest ordinate in each initial effective peak group is taken as an effective peak point; thus obtaining b effective peak points.
2. The method for acquiring the blood pressure of the electrocardiographic pulse monitoring toilet according to claim 1, wherein the method comprises the following steps: the information processing circuit also comprises a wireless transmission module; the wireless transmission module is connected with the controller and is in wireless communication with the upper computer; the model of the heart rate acquisition chip is BMD101; the model of the pulse sensor is PulseSensor; the controller adopts a singlechip of model STM32F 103.
3. The method for acquiring the blood pressure of the electrocardiographic pulse monitoring toilet according to claim 1, wherein the method comprises the following steps: the voltage stabilizing circuit comprises a voltage stabilizing chip and a two-wire plug connector; the model of the voltage stabilizing chip is SGM2020-3.3; pins 1 and 2 of the voltage stabilizing chip are connected with one end of a capacitor C201 and one wiring end of the two-wire plug connector; the 3 pin of the voltage stabilizing chip, the other end of the capacitor C201 and the other wiring end of the two-wire plug connector are grounded; the 4 pin of the voltage stabilizing chip is connected with one end of the capacitor C202, and the 5 pin is connected with one end of the capacitor C203; the other ends of the capacitor C202 and the capacitor C203 are grounded; the two-wire plug connector is connected with an external 5V power supply; the 5 pins of the voltage stabilizing chip are the voltage output ends of the voltage stabilizing circuit.
4. The method for acquiring the blood pressure of the electrocardiographic pulse monitoring toilet according to claim 1, wherein the method comprises the following steps: the ith pulse wave conduction time is the time difference between the ith effective peak point on the electrocardiogram curve and the effective peak point of the corresponding pulse waveform curve; the method for matching the effective peak point on the electrocardiogram ECG with the effective peak point of the pulse waveform curve PPG is as follows: if the time of one effective peak point on the electrocardiogram curve ECG is earlier than the time of one effective peak point on the pulse waveform curve PPG and no other effective peak points of the electrocardiogram curve ECG and the other effective peak points on the pulse waveform curve PPG exist between the two points, the two points correspond to each other.
5. The method for acquiring the blood pressure of the electrocardiographic pulse monitoring toilet according to claim 1, wherein the method comprises the following steps: fifthly, if the ith systolic pressure is higher than a high-pressure alarm preset value or the ith diastolic pressure is higher than a low-pressure alarm preset value, the wireless transmission module sends an alarm signal to the upper computer; the high-pressure alarm preset value is equal to 146mmHg; the low-pressure alarm preset value is equal to 96mmHg.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201811108041.7A CN109199349B (en) | 2018-09-21 | 2018-09-21 | Electrocardiogram pulse monitoring closestool and blood pressure acquisition method thereof |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201811108041.7A CN109199349B (en) | 2018-09-21 | 2018-09-21 | Electrocardiogram pulse monitoring closestool and blood pressure acquisition method thereof |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CN109199349A CN109199349A (en) | 2019-01-15 |
| CN109199349B true CN109199349B (en) | 2023-08-22 |
Family
ID=64985415
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN201811108041.7A Active CN109199349B (en) | 2018-09-21 | 2018-09-21 | Electrocardiogram pulse monitoring closestool and blood pressure acquisition method thereof |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN109199349B (en) |
Families Citing this family (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN111759301A (en) * | 2020-07-06 | 2020-10-13 | 深圳市博声医疗器械有限公司 | Toilet seat with electrocardio monitoring function and electrocardio monitoring method |
| CN117243579A (en) * | 2022-06-10 | 2023-12-19 | 荣耀终端有限公司 | Blood pressure measurement method and electronic equipment |
Citations (8)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US4331154A (en) * | 1979-10-15 | 1982-05-25 | Tech Engineering & Design | Blood pressure and heart rate measuring watch |
| JPH08131404A (en) * | 1994-11-14 | 1996-05-28 | Matsushita Electric Ind Co Ltd | Lavatory seat |
| JPH10323331A (en) * | 1998-05-28 | 1998-12-08 | Toto Ltd | Health management network system |
| CN104323770A (en) * | 2014-11-20 | 2015-02-04 | 康泰医学系统（秦皇岛）股份有限公司 | Pedestal pan type quick physical examination device |
| CN204483982U (en) * | 2015-03-13 | 2015-07-22 | 广州市易风通讯科技有限公司 | A kind of intellectual water closet cushion |
| JP2017006183A (en) * | 2015-06-17 | 2017-01-12 | パナソニックＩｐマネジメント株式会社 | Biological information measurement sensor and toilet seat for measuring biological information |
| CN106901705A (en) * | 2017-01-11 | 2017-06-30 | 南京邮电大学 | A kind of unaware human Body Physiology Multi-parameter harvester and acquisition method and application |
| CN108010578A (en) * | 2017-10-30 | 2018-05-08 | 西安艾润物联网技术服务有限责任公司 | Intellectual medical closestool, platform and its management method and storage medium |
Family Cites Families (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US8465424B2 (en) * | 2008-03-24 | 2013-06-18 | Sudhir Aggarwal | Mobile device and system for monitoring and recording body vital signs |
| WO2015162566A1 (en) * | 2014-04-24 | 2015-10-29 | Ecole Polytechnique Federale De Lausanne (Epfl) | A method and a device for non invasive blood pressure measurement |
| US20180078191A1 (en) * | 2016-09-20 | 2018-03-22 | David R. Hall | Medical Toilet for Collecting and Analyzing Multiple Metrics |
-
2018
- 2018-09-21 CN CN201811108041.7A patent/CN109199349B/en active Active
Patent Citations (8)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US4331154A (en) * | 1979-10-15 | 1982-05-25 | Tech Engineering & Design | Blood pressure and heart rate measuring watch |
| JPH08131404A (en) * | 1994-11-14 | 1996-05-28 | Matsushita Electric Ind Co Ltd | Lavatory seat |
| JPH10323331A (en) * | 1998-05-28 | 1998-12-08 | Toto Ltd | Health management network system |
| CN104323770A (en) * | 2014-11-20 | 2015-02-04 | 康泰医学系统（秦皇岛）股份有限公司 | Pedestal pan type quick physical examination device |
| CN204483982U (en) * | 2015-03-13 | 2015-07-22 | 广州市易风通讯科技有限公司 | A kind of intellectual water closet cushion |
| JP2017006183A (en) * | 2015-06-17 | 2017-01-12 | パナソニックＩｐマネジメント株式会社 | Biological information measurement sensor and toilet seat for measuring biological information |
| CN106901705A (en) * | 2017-01-11 | 2017-06-30 | 南京邮电大学 | A kind of unaware human Body Physiology Multi-parameter harvester and acquisition method and application |
| CN108010578A (en) * | 2017-10-30 | 2018-05-08 | 西安艾润物联网技术服务有限责任公司 | Intellectual medical closestool, platform and its management method and storage medium |
Also Published As
| Publication number | Publication date |
|---|---|
| CN109199349A (en) | 2019-01-15 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| JP7350806B2 (en) | Observational heart failure monitoring system | |
| US20220192513A1 (en) | Remote Physiological Monitor | |
| Yoon et al. | Cuff-less blood pressure estimation using pulse waveform analysis and pulse arrival time | |
| Fortino et al. | PPG-based methods for non invasive and continuous blood pressure measurement: An overview and development issues in body sensor networks | |
| US20210236014A1 (en) | Blood pressure estimation using finger-wearable sensor array | |
| CN105832317B (en) | System for measuring cardiac output, stroke volume, heart force and blood pressure | |
| Gilaberte et al. | Heart and respiratory rate detection on a bathroom scale based on the ballistocardiogram and the continuous wavelet transform | |
| KR20220007872A (en) | Patch-Based Physiological Sensors | |
| CN110974172A (en) | Real-time physiological parameter measuring system | |
| CN109199349B (en) | Electrocardiogram pulse monitoring closestool and blood pressure acquisition method thereof | |
| CN115299899A (en) | Activity recognition and beat-to-beat blood pressure monitoring, analyzing and early warning system based on multiple sensors | |
| CN210121136U (en) | Electrocardio pulse monitoring closestool | |
| JP7315146B2 (en) | patch-based physiological sensor | |
| CN112826471B (en) | Blood pressure detection device, blood pressure detection system, and blood pressure monitoring method | |
| US20170188963A1 (en) | Physiological monitoring system featuring floormat and handheld sensor | |
| CN116548935A (en) | Blood pressure measurement system based on flexible organic light detector and deep learning algorithm | |
| US20170188967A1 (en) | Physiological monitoring system featuring floormat and wired handheld sensor | |
| CN213883186U (en) | Sleeveless blood pressure monitoring device | |
| US20170188962A1 (en) | Physiological monitoring system featuring floormat and handheld sensor | |
| Kaushik et al. | A comprehensive study on blood pressure measurement techniques | |
| US20170188964A1 (en) | Physiological monitoring system featuring floormat and handheld sensor | |
| Sheng et al. | Modeling a safety-related system for continuous non-invasive blood pressure monitoring | |
| US20170188890A1 (en) | Physiological monitoring system featuring floormat and handheld sensor | |
| US20170188944A1 (en) | Physiological monitoring system featuring floormat and handheld sensor | |
| US20210401297A1 (en) | Patient-monitoring system |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| PB01 | Publication | ||
| PB01 | Publication | ||
| SE01 | Entry into force of request for substantive examination | ||
| SE01 | Entry into force of request for substantive examination | ||
| GR01 | Patent grant | ||
| GR01 | Patent grant |