CN111166334A - Respiration measuring method and device - Google Patents
Respiration measuring method and device Download PDFInfo
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- 238000000034 method Methods 0.000 title claims abstract description 32
- 230000029058 respiratory gaseous exchange Effects 0.000 title claims description 28
- 230000000241 respiratory effect Effects 0.000 claims abstract description 45
- 238000009531 respiratory rate measurement Methods 0.000 claims abstract description 5
- 238000012545 processing Methods 0.000 claims description 15
- 238000005259 measurement Methods 0.000 claims description 11
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- QVGXLLKOCUKJST-UHFFFAOYSA-N atomic oxygen Chemical compound [O] QVGXLLKOCUKJST-UHFFFAOYSA-N 0.000 description 1
- 230000009286 beneficial effect Effects 0.000 description 1
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/08—Detecting, measuring or recording devices for evaluating the respiratory organs
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- 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
- A61B5/6801—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be attached to or worn on the body surface
- A61B5/6813—Specially adapted to be attached to a specific body part
- A61B5/6823—Trunk, e.g., chest, back, abdomen, hip
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- 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
- A61B5/6801—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be attached to or worn on the body surface
- A61B5/683—Means for maintaining contact with the body
- A61B5/6831—Straps, bands or harnesses
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Abstract
A method and apparatus for respiratory measurement, the method comprising: collecting the absolute pressure sensor pressure value and sending the absolute pressure sensor pressure value to a processor; the processor calibrates the pressure value of the absolute pressure sensor to obtain a calibrated pressure value; and the processor calculates the respiratory amplitude according to the calibrated pressure value. The method comprises the step of collecting the absolute pressure value of the absolute pressure sensor, the absolute pressure value of the absolute pressure sensor is calibrated to obtain a calibrated pressure value, and the respiratory amplitude value is calculated according to the calibrated pressure value. This application is because can gather respiratory signal with the gasbag constraint in the belly, and is noiseless to the human body, can gather more reliable respiratory signal, carries out the check-up to respiratory signal for respiratory signal more accurate, especially when the sleep respiratory monitoring, can extract the respiratory signal of high reliability under the condition that does not influence the measurand rest, improved user experience.
Description
Technical Field
The present application relates to the medical field, and in particular, to a method and an apparatus for measuring respiration.
Background
Respiration is one of basic physical signs of a human body, is controlled by vegetative nerves, and is one of key indexes of life monitoring because the respiration causes the internal and external alternation of gas. In recent years, respiratory signals have been widely used in the field of sleep respiration and in the field of analysis of respiratory diseases in hospitals. In these areas, a high reliability of the respiratory signal is crucial. Currently, techniques for monitoring a respiratory signal generally include an impedance method, a thermal method, a flow method, an acceleration sensor method, and the like.
The impedance method is to apply one high frequency constant current source signal of tens KHz to two special electrocardio electrodes adhered to the chest cavity, and the principle is that the impedance signal is loaded on the high frequency constant current source signal due to the impedance change caused by the fluctuation of the chest cavity caused by respiration, and then the respiratory signal is acquired through amplification and demodulation. The disadvantages of the impedance method measurement technology are: the impedance monitoring is easily interfered by an analog circuit and external factors, particularly the interference of a tested person, so that the measuring result is not accurate enough. In addition, it is not guaranteed that the impedance in the respiratory signal frequency band is obtained in real time.
The thermosensitive method is to place a special miniature thermistor in the nasal cavity, so that the temperature in the nasal cavity can change along with the exchange of gas due to the exchange of exhalation and inhalation of human body, and the monitoring of breathing signals and characteristic parameters is realized by collecting the change of resistance of the thermistor. The disadvantages of the thermographic measurement technique are: the thermosensitive method is easily affected by the ambient temperature, so that the measurement result is not accurate enough. In addition, the thermistor is arranged in the nasal cavity, so that great discomfort is brought to the tested person.
The flow method is to monitor the respiratory signal by measuring the change of the airflow. The defects of the flow method testing technology are as follows: the flow method test needs to insert the nasal oxygen tube into the nasal cavity of a human body, great discomfort is brought to a tested person, and the measurement result is not accurate enough.
The acceleration sensor method is used for monitoring respiratory signals and characteristic parameters by measuring abdominal motion caused by abdominal respiration of a human body. The disadvantages of the acceleration measurement technique are: the acceleration method is easy to cause interference to the respiration measurement due to other movements (such as turning over and moving the body of a measured person during sleeping), so that the measurement result is not accurate enough.
When the respiratory signal is collected, the interference from the external environment or the tested person is easily caused, and the reliability of the collected respiratory signal is greatly reduced, so that the signal quality and the diagnosis reliability are influenced.
Disclosure of Invention
The application provides an absolute pressure sensor assembly and a bladder type respiration measuring device.
According to a first aspect of the present application, there is provided a respiratory measurement device comprising a processor, an airbag, and an absolute pressure sensor assembly comprising an absolute pressure sensor chip and a flexible circuit board;
the air bag is filled with air;
the absolute pressure sensor chip is used for converting a pressure signal into an electric signal;
the flexible circuit board comprises an induction area, a connecting part and an output end, wherein the induction area is connected with the output end through the connecting part, the induction area is sealed in the air bag, the output end is arranged outside the air bag, the absolute pressure sensor chip is arranged in the induction area, the induction area is also provided with a circuit matched with the absolute pressure sensor chip, and the circuit is used for leading out the electric signal through the output end;
and the processor is used for receiving the electric signal, processing the electric signal and acquiring a respiratory signal.
Furthermore, an SD signal line is connected to an SDA pin of the absolute pressure sensor chip, an SO signal line is connected to an SCL pin of the absolute pressure sensor chip, a GND pin of the absolute pressure sensor chip is grounded, a VDD pin of the absolute pressure sensor chip is connected to a power line, one end of a capacitor C1 is connected to the VDD pin, the other end of the capacitor C1 is grounded, one end of a resistor R1 is connected to the SDA pin, the other end of the resistor R1 is connected to the power line, one end of the resistor R2 is connected to the SCL pin, and the other end of the resistor R2 is connected to the power line.
According to a second aspect of the present application, there is provided a respiration measurement method for use in the respiration measurement apparatus described above, the method comprising:
collecting the absolute pressure sensor pressure value and sending the absolute pressure sensor pressure value to a processor;
the processor calibrates the pressure value of the absolute pressure sensor to obtain a calibrated pressure value;
and the processor calculates the respiratory amplitude according to the calibrated pressure value.
Further, the processor calibrates the absolute pressure sensor pressure value to obtain a calibrated pressure value, including:
performing first-order calibration on the pressure value of the absolute pressure sensor to obtain a first-order pressure calibration value;
and carrying out second-order calibration on the first-order pressure calibration value to obtain a second-order pressure calibration value.
Further, the first order pressure calibration value is calculated by the following formula:
P1＝(D1*SENS/221-OFF)/213
the second-order pressure calibration value is obtained by calculating the following formula:
P2＝0.4*(((D1*SENS2)/221-OFF2)/211)
wherein, P1 is a first-order pressure calibration value, P2 is a second-order pressure calibration value, D1 is a read data pressure value, SENS is an actual temperature offset value, SENS2 is a second-order pressure sensitivity value, and OFF2 is a second-order pressure offset value.
Further, the processor calculates a respiratory amplitude value according to the calibrated pressure value, and includes:
the respiratory amplitude is calculated by the following formula:
RESPAmp＝P2*(3.3/216)
wherein RESPAmp is the respiratory amplitude.
According to a third aspect of the present application, there is provided a respiratory measurement device comprising:
the acquisition module is used for acquiring the absolute pressure sensor pressure value and sending the absolute pressure sensor pressure value to the processor;
the calibration module is used for calibrating the pressure value of the absolute pressure sensor to obtain a calibrated pressure value;
and the processing module is used for calculating the respiratory amplitude according to the calibrated pressure value.
Further, the calibration module includes:
the first-order calibration unit is used for performing first-order calibration on the absolute pressure sensor pressure value to obtain a first-order pressure calibration value;
and the second-order calibration unit is used for carrying out second-order calibration on the first-order pressure calibration value to obtain a second-order pressure calibration value.
Further, the first order pressure calibration unit is further used for calculating a first order pressure calibration value through the following formula:
P1＝(D1*SENS/221-OFF)/213
the second-order pressure calibration unit is also used for calculating a second-order pressure calibration value through the following formula:
P2＝0.4*(((D1*SENS2)/221-OFF2)/211)
wherein, P1 is a first-order pressure calibration value, P2 is a second-order pressure calibration value, D1 is a read data pressure value, SENS is an actual temperature offset value, SENS2 is a second-order pressure sensitivity value, and OFF2 is a second-order pressure offset value.
Further, the processing module comprises:
a processing unit, configured to calculate the respiration amplitude according to the following formula:
RESPAmp＝P2*(3.3/216)
wherein RESPAmp is the respiratory amplitude.
Due to the adoption of the technical scheme, the beneficial effects of the application are as follows:
the method comprises the step of collecting the absolute pressure value of the absolute pressure sensor, the absolute pressure value of the absolute pressure sensor is calibrated to obtain a calibrated pressure value, and the respiratory amplitude value is calculated according to the calibrated pressure value. This application is because can gather respiratory signal with the gasbag constraint in the belly, and is noiseless to the human body, can gather more reliable respiratory signal, carries out the check-up to respiratory signal for respiratory signal more accurate, especially when the sleep respiratory monitoring, can extract the respiratory signal of high reliability under the condition that does not influence the measurand rest, improved user experience.
Drawings
Fig. 1 is a schematic circuit diagram of an absolute pressure sensor assembly according to a first embodiment of the present disclosure;
FIG. 2 is a schematic structural diagram of an absolute pressure sensor assembly according to an embodiment of the present disclosure;
FIG. 3 is a top view of a bladder type respiration measurement device according to one embodiment of the present disclosure;
FIG. 4 is a front view of a bladder type respiration measurement device according to one embodiment of the present disclosure;
FIG. 5 is a flow chart of a method in example two of the present application in one implementation;
FIG. 6 is a flow chart of a method in another embodiment of the second embodiment of the present application;
FIG. 7 is a schematic diagram of program modules of an apparatus according to a third embodiment of the present application;
fig. 8 is a schematic diagram of program modules of an apparatus in a third embodiment of the present application.
Detailed Description
The present invention will be described in further detail with reference to the following detailed description and accompanying drawings. The present application may be embodied in many different forms and is not limited to the embodiments described in the present embodiment. The following detailed description is provided to facilitate a more thorough understanding of the present disclosure, and the words used to indicate orientation, top, bottom, left, right, etc. are used solely to describe the illustrated structure in connection with the accompanying figures.
One skilled in the relevant art will recognize, however, that one or more of the specific details can be omitted, or other methods, components, or materials can be used. In some instances, some embodiments are not described or not described in detail.
The numbering of the components as such, e.g., "first", "second", etc., is used herein only to distinguish the objects as described, and does not have any sequential or technical meaning.
Furthermore, the technical features, aspects or characteristics described herein may be combined in any suitable manner in one or more embodiments. It will be readily appreciated by those of skill in the art that the order of the steps or operations of the methods associated with the embodiments provided herein may be varied. Thus, any sequence in the figures and examples is for illustrative purposes only and does not imply a requirement in a certain order unless explicitly stated to require a certain order.
The first embodiment is as follows:
as shown in fig. 1-4, the air bag type respiration measuring device of the present application, in one embodiment, includes an air bag 30, an absolute pressure sensor assembly, and a processor (not shown). The absolute pressure sensor assembly includes an absolute pressure sensor chip 21 and a flexible wiring board. The bladder 30 may be filled with air. In one embodiment, the airbag 30 is provided with an inflation hole 31, and the airbag 30 can be filled with air through the inflation hole 31. The bladder 30 may be made of a gas impermeable material, and in one embodiment, the bladder 30 may be made of a TPU (Thermoplastic Urethane elastomer) material. The inflation hole 31 may be further provided with a rubber plug (not shown), and after inflation, the inflation hole 31 may be blocked by the rubber plug.
And an absolute pressure sensor chip 21 for converting the pressure signal into an electrical signal. The flexible circuit board comprises a sensing area 12, a connecting part 13 and an output end 11, wherein the sensing area 12 and the output end 11 are connected through the connecting part 13. The absolute pressure sensor chip 21 is arranged in the sensing area 12, and the sensing area 12 is further provided with a circuit which is matched with the absolute pressure sensor chip 21. Sensing region 12 is sealed within bladder 20 and output 11 is disposed outside bladder 30. The connecting portion 13 is provided with a metal wire, two ends of the metal wire are respectively electrically connected with the circuit and the output end 11, and the circuit is used for leading out an electric signal through the output end. The balloon 30 may be sealed by high frequency. And the processor can be used for receiving the electric signals, processing the electric signals and acquiring the respiratory signals.
Further, the metal wire may include an SD signal line 14, an SO signal line 15, a power line 16, and a ground line 17, the SD signal line 14 is connected to an SDA pin of the absolute pressure sensor chip 21, the SO signal line 15 is connected to an SCL pin of the absolute pressure sensor chip 21, a GND pin of the absolute pressure sensor chip 21 is grounded, a VDD pin of the absolute pressure sensor chip 21 is connected to the power line 16, one end of a capacitor C1 is connected to the VDD pin, the other end of a capacitor C1 is grounded, one end of a resistor R1 is connected to the SDA pin, the other end of a resistor R1 is connected to the power line 16, one end of a resistor R2 is connected to the SCL pin, and the other end of the resistor R2 is connected to.
In one embodiment, an SDA pin of the absolute pressure sensor chip 21 may be connected to a TXD terminal of the J5 interface through the SD signal line 14, an SCL pin of the absolute pressure sensor chip 21 may be connected to an RXD terminal of the J5 interface through the SO signal line 15, a GND pin of the absolute pressure sensor chip 21 is connected to the ground 17, a VDD pin of the absolute pressure sensor chip 21 is connected to a VCC terminal of the J5 interface, one end of the capacitor C1 is connected to the VDD pin, the other end of the capacitor C1 is grounded, one end of the resistor R1 is connected to the SDA pin, the other end of the resistor R1 is connected to the VCC terminal, one end of the resistor R2 is connected to the SCL pin, and the other end of the resistor R2 is connected to the VCC terminal.
Fig. 1 is a circuit schematic of the present application. The output terminal 11 is coupled to the J5 interface, and the J5 interface is defined as a power line 3.3V, a ground line GND, a clock signal line SCL, and a data transmission signal line SDA. U1 is MS5637 absolute pressure sensor, and this chip carries out signal transmission through II2C agreement, and the signal line is SDA and SCL, according to the requirement of II2C universal protocol, needs two signal lines to connect R1 and R2 resistance to power 3.3V, plays the effect of pulling up, increases II 2C's communication ability. The main working principle of the circuit is that when the sensor U1 senses the change of the external pressure, the change of the pressure is converted into an electric signal and is transmitted to the interface J5 through the II2C communication protocol.
Further, the airbag type respiration measuring device of the present application may further include a bracket 40, one end of the bracket 40 is fixed to the inner surface of the airbag 30, and the sensing region 12 is suspended in the airbag 30 by the bracket 40. The bracket 40 can be designed in various shapes as long as the sensing area 12 of the flexible circuit board can be fixed in the air bag. In one embodiment, the bracket 40 may have a rectangular parallelepiped shape with a bottom end open and a side surface having a window through which the sensing region 12 is inserted into the bracket 40, and the bracket 40 may be made of various materials, and in this embodiment, the bracket 40 is made of TPU material.
Further, the height of the sensing region 12 in the vertical direction is greater than one-half of the total height of the airbag 30.
Example two:
as shown in fig. 5, the present application provides a respiration measurement method, which can be used in the respiration measurement device according to the first embodiment, and the method can include:
step 502: and collecting the absolute pressure sensor pressure value and sending the absolute pressure sensor pressure value to the processor.
Step 504: and the processor calibrates the pressure value of the absolute pressure sensor to obtain a calibrated pressure value.
Further, step 104 may specifically include:
step 5042: and carrying out first-order calibration on the pressure value of the absolute pressure sensor to obtain a first-order pressure calibration value.
In one embodiment, the first order pressure calibration value is calculated by the following formula:
P1＝(D1*SENS/221-OFF)/213
wherein P1 is the first-order pressure calibration value, D1 is the read data pressure value, SENS is the actual temperature offset value, and OFF is the actual temperature offset value.
Step 5044: and carrying out second-order calibration on the first-order pressure calibration value to obtain a second-order pressure calibration value.
In one embodiment, the second-order pressure calibration value may be specifically calculated by the following formula:
P2＝0.4*(((D1*SENS2)/221-OFF2)/211)
wherein, P2 is the second order pressure calibration value, D1 is the read data pressure value, SENS2 is the second order pressure sensitivity value, and OFF2 is the second order pressure offset value.
Step 506: and the processor calculates the respiratory amplitude according to the calibrated pressure value.
Further, step 506 may include:
the respiratory amplitude is calculated by the following formula:
RESPAmp＝P2*(3.3/216)
wherein RESPAmp is the respiratory amplitude.
As shown in fig. 6, the present application provides a respiration measurement method, another embodiment of which may include the steps of:
step 602: and collecting the absolute pressure sensor pressure value and sending the absolute pressure sensor pressure value to the processor.
Step 604: and the processor performs first-order calibration on the absolute pressure sensor pressure value to obtain a first-order pressure calibration value.
In one embodiment, the first order pressure calibration value is calculated by the following formula:
P1＝(D1*SENS/221-OFF)/213
wherein P1 is the first-order pressure calibration value, D1 is the read data pressure value, SENS is the actual temperature offset value, and OFF is the actual temperature offset value.
Step 606: and the processor carries out second-order calibration on the first-order pressure calibration value to obtain a second-order pressure calibration value.
In one embodiment, the second-order pressure calibration value may be specifically calculated by the following formula:
P2＝0.4*(((D1*SENS2)/221-OFF2)/211)
wherein, P2 is the second order pressure calibration value, D1 is the read data pressure value, SENS2 is the second order pressure sensitivity value, and OFF2 is the second order pressure offset value.
Step 608: the processor calculates the respiration amplitude according to the following formula and the calibrated pressure value.
RESPAmp＝P2*(3.3/216)
Wherein RESPAmp is the respiratory amplitude, and P2 is the second-order pressure calibration value.
Example three:
as shown in fig. 7, the breath measurement device of the present application, one embodiment of which may include an acquisition module 710, a calibration module 720, and a processing module 730.
And the acquisition module 710 is used for acquiring the absolute pressure sensor pressure value and sending the absolute pressure sensor pressure value to the processor.
And the calibration module 720 is used for calibrating the pressure value of the absolute pressure sensor to obtain a calibrated pressure value.
And the processing module 730 is configured to calculate a respiratory amplitude according to the calibrated pressure value.
As shown in fig. 8, a respiratory measurement device of the present application, in another embodiment thereof, may include an acquisition module 810, a calibration module 820, and a processing module 730.
And the acquisition module 810 is used for acquiring the absolute pressure sensor pressure value and sending the absolute pressure sensor pressure value to the processor.
And the calibration module 820 is used for calibrating the pressure value of the absolute pressure sensor to obtain a calibrated pressure value.
And the processing module 830 is configured to calculate a respiratory amplitude according to the calibrated pressure value.
Further, the calibration module 820 may include a first order calibration unit 821 and a second order calibration unit 822.
The first-order calibration unit 821 is used for performing first-order calibration on the absolute pressure sensor pressure value to obtain a first-order pressure calibration value.
Further, the first-order calibration unit 821 may be specifically configured to calculate the first-order pressure calibration value according to the following formula:
P1＝(D1*SENS/221-OFF)/213
wherein P1 is the first-order pressure calibration value, D1 is the read data pressure value, SENS is the actual temperature offset value, and OFF is the actual temperature offset value.
And the second-order calibration unit 822 performs second-order calibration on the first-order pressure calibration value to obtain a second-order pressure calibration value.
Further, the second order pressure calibration unit 822 is further configured to calculate a second order pressure calibration value according to the following formula:
P2＝0.4*(((D1*SENS2)/221-OFF2)/211)
wherein, P2 is the second order pressure calibration value, D1 is the read data pressure value, SENS2 is the second order pressure sensitivity value, and OFF2 is the second order pressure offset value.
Further, the processing module 830 may include:
a processing unit 831, configured to calculate the respiration amplitude by the following equation:
RESPAmp＝P2*(3.3/216)
wherein RESPAmp is the respiratory amplitude.
Those skilled in the art will appreciate that all or part of the steps of the various methods in the above embodiments may be implemented by instructions associated with hardware via a program, which may be stored in a computer-readable storage medium, and the storage medium may include: read-only memory, random access memory, magnetic or optical disk, and the like. The foregoing is a more detailed description of the present application in connection with specific embodiments thereof, and it is not intended that the present application be limited to the specific embodiments thereof. It will be apparent to those skilled in the art from this disclosure that many more simple derivations or substitutions can be made without departing from the spirit of the disclosure.
Claims (10)
1. The respiration measuring device is characterized by comprising a processor, an air bag and an absolute pressure sensor assembly, wherein the absolute pressure sensor assembly comprises an absolute pressure sensor chip and a flexible circuit board;
the air bag is filled with air;
the absolute pressure sensor chip is used for converting a pressure signal into an electric signal;
the flexible circuit board comprises an induction area, a connecting part and an output end, wherein the induction area is connected with the output end through the connecting part, the induction area is sealed in the air bag, the output end is arranged outside the air bag, the absolute pressure sensor chip is arranged in the induction area, the induction area is also provided with a circuit matched with the absolute pressure sensor chip, and the circuit is used for leading out the electric signal through the output end;
and the processor is used for receiving the electric signal, processing the electric signal and acquiring a respiratory signal.
2. The apparatus of claim 1, wherein an SDA pin of the absolute pressure sensor chip is connected to an SD signal line, an SCL pin of the absolute pressure sensor chip is connected to an SO signal line, a GND pin of the absolute pressure sensor chip is connected to a ground, a VDD pin of the absolute pressure sensor chip is connected to a power line, one end of a capacitor C1 is connected to the VDD pin, the other end of a capacitor C1 is connected to a ground, one end of a resistor R1 is connected to the SDA pin, the other end of a resistor R1 is connected to the power line, one end of a resistor R2 is connected to the SCL pin, and the other end of the resistor R2 is connected to the power line.
3. A respiration measurement method for use in a respiration measurement apparatus according to claim 1 or 2, the method comprising:
collecting the absolute pressure sensor pressure value and sending the absolute pressure sensor pressure value to a processor;
the processor calibrates the pressure value of the absolute pressure sensor to obtain a calibrated pressure value;
and the processor calculates the respiratory amplitude according to the calibrated pressure value.
4. The method of claim 3, wherein the processor calibrating the absolute pressure sensor pressure value to obtain a calibrated pressure value comprises:
performing first-order calibration on the pressure value of the absolute pressure sensor to obtain a first-order pressure calibration value;
and carrying out second-order calibration on the first-order pressure calibration value to obtain a second-order pressure calibration value.
5. The method of claim 4, wherein the first order pressure calibration value is calculated by the following equation:
P1＝(D1*SENS/221-OFF)/213
the second-order pressure calibration value is obtained by calculating the following formula:
P2＝0.4*(((D1*SENS2)/221-OFF2)/211)
wherein, P1 is a first-order pressure calibration value, P2 is a second-order pressure calibration value, D1 is a read data pressure value, SENS is an actual temperature offset value, SENS2 is a second-order pressure sensitivity value, and OFF2 is a second-order pressure offset value.
6. The method of claim 5, wherein the processor calculates a respiration amplitude from the calibrated pressure value, comprising:
the respiratory amplitude is calculated by the following formula:
RESPAmp＝P2*(3.3/216)
wherein RESPAmp is the respiratory amplitude.
7. A respiratory measurement device, comprising:
the acquisition module is used for acquiring the absolute pressure sensor pressure value and sending the absolute pressure sensor pressure value to the processor;
the calibration module is used for calibrating the pressure value of the absolute pressure sensor to obtain a calibrated pressure value;
and the processing module is used for calculating the respiratory amplitude according to the calibrated pressure value.
8. The apparatus of claim 7, wherein the calibration module comprises:
the first-order calibration unit is used for performing first-order calibration on the absolute pressure sensor pressure value to obtain a first-order pressure calibration value;
and the second-order calibration unit is used for carrying out second-order calibration on the first-order pressure calibration value to obtain a second-order pressure calibration value.
9. The apparatus of claim 8, wherein the first order pressure calibration unit is further configured to calculate a first order pressure calibration value by the following equation:
P1＝(D1*SENS/221-OFF)/213
the second-order pressure calibration unit is also used for calculating a second-order pressure calibration value through the following formula:
P2＝0.4*(((D1*SENS2)/221-OFF2)/211)
wherein, P1 is a first-order pressure calibration value, P2 is a second-order pressure calibration value, D1 is a read data pressure value, SENS is an actual temperature offset value, SENS2 is a second-order pressure sensitivity value, and OFF2 is a second-order pressure offset value.
10. The apparatus of claim 9, wherein the processing module comprises:
a processing unit, configured to calculate the respiration amplitude according to the following formula:
RESPAmp＝P2*(3.3/216)
wherein RESPAmp is the respiratory amplitude.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201911415265.7A CN111166334A (en) | 2019-12-31 | 2019-12-31 | Respiration measuring method and device |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201911415265.7A CN111166334A (en) | 2019-12-31 | 2019-12-31 | Respiration measuring method and device |
Publications (1)
| Publication Number | Publication Date |
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| CN111166334A true CN111166334A (en) | 2020-05-19 |
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| CN105784258A (en) * | 2016-03-09 | 2016-07-20 | 安徽久工健业有限责任公司 | Air bag with built-in baroceptor and manufacturing method thereof |
| CN106901713A (en) * | 2017-03-06 | 2017-06-30 | 清华大学 | A kind of implantation type wireless monitoring intracranial pressure system based on air bag |
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Application publication date: 20200519 |