CN111166335A - Absolute pressure sensor assembly and air bag type respiration measuring device - Google Patents
Absolute pressure sensor assembly and air bag type respiration measuring device Download PDFInfo
- Publication number
- CN111166335A CN111166335A CN201911415299.6A CN201911415299A CN111166335A CN 111166335 A CN111166335 A CN 111166335A CN 201911415299 A CN201911415299 A CN 201911415299A CN 111166335 A CN111166335 A CN 111166335A
- Authority
- CN
- China
- Prior art keywords
- pressure sensor
- absolute pressure
- sensor chip
- pin
- resistor
- 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.)
- Pending
Links
- 230000029058 respiratory gaseous exchange Effects 0.000 title claims description 17
- 230000006698 induction Effects 0.000 claims abstract description 29
- 239000003990 capacitor Substances 0.000 claims description 16
- 239000000463 material Substances 0.000 claims description 9
- 230000000241 respiratory effect Effects 0.000 abstract description 14
- 210000001015 abdomen Anatomy 0.000 abstract description 2
- 238000009531 respiratory rate measurement Methods 0.000 abstract 1
- 238000000034 method Methods 0.000 description 16
- 238000005259 measurement Methods 0.000 description 6
- 239000007789 gas Substances 0.000 description 5
- 238000012544 monitoring process Methods 0.000 description 5
- 229920002803 thermoplastic polyurethane Polymers 0.000 description 5
- 230000001133 acceleration Effects 0.000 description 4
- 238000004891 communication Methods 0.000 description 4
- 239000002184 metal Substances 0.000 description 4
- 210000003928 nasal cavity Anatomy 0.000 description 4
- 229920001971 elastomer Polymers 0.000 description 3
- 230000003187 abdominal effect Effects 0.000 description 2
- 230000005540 biological transmission Effects 0.000 description 2
- 238000010586 diagram Methods 0.000 description 2
- 230000000694 effects Effects 0.000 description 2
- 238000005516 engineering process Methods 0.000 description 2
- 230000033001 locomotion Effects 0.000 description 2
- 238000000691 measurement method Methods 0.000 description 2
- 230000008054 signal transmission Effects 0.000 description 2
- 238000012360 testing method Methods 0.000 description 2
- 210000000115 thoracic cavity Anatomy 0.000 description 2
- 230000003321 amplification Effects 0.000 description 1
- 238000004458 analytical method Methods 0.000 description 1
- QVGXLLKOCUKJST-UHFFFAOYSA-N atomic oxygen Chemical compound [O] QVGXLLKOCUKJST-UHFFFAOYSA-N 0.000 description 1
- 230000009286 beneficial effect Effects 0.000 description 1
- 230000007547 defect Effects 0.000 description 1
- 238000009795 derivation Methods 0.000 description 1
- 238000003745 diagnosis Methods 0.000 description 1
- 239000000806 elastomer Substances 0.000 description 1
- 230000005611 electricity Effects 0.000 description 1
- 210000005036 nerve Anatomy 0.000 description 1
- 238000003199 nucleic acid amplification method Methods 0.000 description 1
- 239000001301 oxygen Substances 0.000 description 1
- 229910052760 oxygen Inorganic materials 0.000 description 1
- 208000023504 respiratory system disease Diseases 0.000 description 1
- 238000006467 substitution reaction Methods 0.000 description 1
Images
Classifications
-
- 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
-
- 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
-
- 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
Abstract
An absolute pressure sensor assembly and a bladder-style respiratory measurement device, the absolute pressure sensor assembly comprising: the absolute pressure sensor chip is used for converting the 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 and the output end are connected through the connecting part, the absolute pressure sensor chip is arranged in the induction area, the induction area is further 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. The application discloses measuring device is breathed to absolute pressure sensor subassembly and gasbag formula simple structure, convenient to use owing to can gather respiratory signal with the belly of gasbag constraint, is noiseless to the human body, gathers more reliable respiratory signal, has improved user experience.
Description
Technical Field
The application relates to the field of medical treatment, especially, relate to an absolute pressure sensor subassembly and gasbag formula respiratory measuring device.
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 an absolute pressure sensor assembly comprising:
the absolute pressure sensor chip is used for converting the 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 and the output end are connected through the connecting part, the absolute pressure sensor chip is arranged in the induction area, the induction area is further 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.
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 gas bag type respiration measuring device comprising a gas bag and an absolute pressure sensor assembly, the 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 and the output end are connected 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 further provided with a circuit matched with the absolute pressure sensor chip, and the circuit is used for leading out an electric signal through the output end.
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.
Further, the output is mated with a J5 interface.
Further, the air bag comprises a bracket, one end of the bracket is fixed on the inner surface of the air bag, and the sensing area is suspended in the air bag through the bracket.
Furthermore, the support is in a cuboid shape with an opening at the bottom end, a window is arranged on the side face of the cuboid shape, the induction area is inserted into the support through the window, and the support is made of TPU materials respectively.
Further, the height of the sensing area in the vertical direction is larger than one half of the total height of the air bag.
Furthermore, an inflation hole is formed in the air bag.
Further, the balloon is made of TPU material, and the balloon is sealed by high frequency waves.
Due to the adoption of the technical scheme, the beneficial effects of the application are as follows:
the absolute pressure sensor assembly and the air bag type respiration measuring device provided by the embodiment of the application comprise an absolute pressure sensor chip and are 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 and the output end are connected through the connecting part, the absolute pressure sensor chip is arranged in the induction area, the induction area is further 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. The application discloses measuring device is breathed to absolute pressure sensor subassembly and gasbag formula simple structure, convenient to use owing to can gather respiratory signal with the belly of gasbag constraint, is noiseless to the human body, gathers more reliable respiratory signal, has 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 a second embodiment of the present application;
fig. 4 is a front view of a balloon type respiration measuring device according to a second 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 and 2, an absolute pressure sensor assembly according to an embodiment of the present invention includes:
an absolute pressure sensor chip 21 for converting a pressure signal into an electric signal;
the flexible printed circuit board 10 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. It is equipped with the circuit at induction zone 12 to press sensor chip 21 absolutely, induction zone 12 still be equipped with, the circuit with press sensor chip 21 absolutely the cooperation, connecting portion 13 is equipped with wire, wire's both ends are connected with circuit and output 11 electricity respectively, the circuit is used for exporting the signal of telecommunication through the output.
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. J5 in the figure is an interface defined as a power line 3.3V, a ground line GND, a clock signal line SCL and a data transmission signal line SDA, respectively. 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.
Example two:
as shown in fig. 1 to 4, the air bag type respiration measuring device of the present application, one embodiment of which includes an air bag 30 and an absolute pressure sensor assembly. 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.
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 absolute pressure 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.
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. An absolute pressure sensor assembly, comprising:
the absolute pressure sensor chip is used for converting the 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 and the output end are connected through the connecting part, the absolute pressure sensor chip is arranged in the induction area, the induction area is further 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.
2. The absolute pressure sensor assembly according to 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 the capacitor C1 is connected to a ground, 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 a resistor R2 is connected to the SCL pin, and the other end of the resistor R2 is connected to the power line.
3. The air bag type respiration measuring device is characterized by comprising 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 and the output end are connected 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 further provided with a circuit matched with the absolute pressure sensor chip, and the circuit is used for leading out an electric signal through the output end.
4. The apparatus of claim 3, 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.
5. The apparatus of claim 4, wherein the output is mated to a J5 interface.
6. The device of any one of claims 3 to 5, further comprising a stent, one end of which is fixed to the inner surface of the balloon, the sensing region being suspended within the balloon by the stent.
7. The apparatus of claim 6, wherein said frame is a rectangular parallelepiped with an open bottom, said rectangular parallelepiped having a window on a side thereof, said sensing area being inserted into said frame through said window, said frame being made of TPU material.
8. The apparatus of claim 7, wherein the height of the sensing region in the vertical direction is greater than one-half of the total height of the airbag.
9. The device of claim 6, wherein the balloon is provided with an inflation port.
10. The apparatus of claim 6, wherein said balloon is made of TPU material, said balloon being sealed by high frequency.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201911415299.6A CN111166335A (en) | 2019-12-31 | 2019-12-31 | Absolute pressure sensor assembly and air bag type respiration measuring device |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201911415299.6A CN111166335A (en) | 2019-12-31 | 2019-12-31 | Absolute pressure sensor assembly and air bag type respiration measuring device |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CN111166335A true CN111166335A (en) | 2020-05-19 |
Family
ID=70648997
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN201911415299.6A Pending CN111166335A (en) | 2019-12-31 | 2019-12-31 | Absolute pressure sensor assembly and air bag type respiration measuring device |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN111166335A (en) |
Citations (13)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US5611349A (en) * | 1993-04-26 | 1997-03-18 | I Am Fine, Inc. | Respiration monitor with simplified breath detector |
| CN101073495A (en) * | 2007-06-15 | 2007-11-21 | 东华大学 | Embedded clothing intelligent device and method for estimating human-body sub-health |
| US20070293781A1 (en) * | 2003-11-04 | 2007-12-20 | Nathaniel Sims | Respiration Motion Detection and Health State Assesment System |
| CN104287734A (en) * | 2014-08-27 | 2015-01-21 | 深圳市惟拓力医疗电子有限公司 | Breathing continuous monitoring method and device |
| CN105043651A (en) * | 2015-05-25 | 2015-11-11 | 林相平 | Low-stress packaging structure suitable for MEMS sensor chip |
| 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 |
| CN106404237A (en) * | 2015-07-29 | 2017-02-15 | 浙江盾安人工环境股份有限公司 | Pressure sensor chip and preparation method, and absolute pressure sensor chip |
| 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 |
| CN108030472A (en) * | 2017-12-21 | 2018-05-15 | 南京麦狄司特科技有限公司 | Sleep monitor band |
| WO2019003620A1 (en) * | 2017-06-30 | 2019-01-03 | ヤマハ株式会社 | Biological information measuring device and sphygmomanometer |
| CN109316655A (en) * | 2017-07-31 | 2019-02-12 | 深圳市美好创亿医疗科技有限公司 | Air-supply mask system and air blowing control method |
| CN208740982U (en) * | 2018-01-02 | 2019-04-16 | 北京津发科技股份有限公司 | A kind of wearable respiration measurement device and respiration transducer |
| CN212037525U (en) * | 2019-12-31 | 2020-12-01 | 深圳大学 | Absolute pressure sensor assembly and air bag type respiration measuring device |
-
2019
- 2019-12-31 CN CN201911415299.6A patent/CN111166335A/en active Pending
Patent Citations (13)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US5611349A (en) * | 1993-04-26 | 1997-03-18 | I Am Fine, Inc. | Respiration monitor with simplified breath detector |
| US20070293781A1 (en) * | 2003-11-04 | 2007-12-20 | Nathaniel Sims | Respiration Motion Detection and Health State Assesment System |
| CN101073495A (en) * | 2007-06-15 | 2007-11-21 | 东华大学 | Embedded clothing intelligent device and method for estimating human-body sub-health |
| CN104287734A (en) * | 2014-08-27 | 2015-01-21 | 深圳市惟拓力医疗电子有限公司 | Breathing continuous monitoring method and device |
| CN105043651A (en) * | 2015-05-25 | 2015-11-11 | 林相平 | Low-stress packaging structure suitable for MEMS sensor chip |
| CN106404237A (en) * | 2015-07-29 | 2017-02-15 | 浙江盾安人工环境股份有限公司 | Pressure sensor chip and preparation method, and absolute pressure sensor chip |
| 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 |
| WO2019003620A1 (en) * | 2017-06-30 | 2019-01-03 | ヤマハ株式会社 | Biological information measuring device and sphygmomanometer |
| CN109316655A (en) * | 2017-07-31 | 2019-02-12 | 深圳市美好创亿医疗科技有限公司 | Air-supply mask system and air blowing control method |
| CN108030472A (en) * | 2017-12-21 | 2018-05-15 | 南京麦狄司特科技有限公司 | Sleep monitor band |
| CN208740982U (en) * | 2018-01-02 | 2019-04-16 | 北京津发科技股份有限公司 | A kind of wearable respiration measurement device and respiration transducer |
| CN212037525U (en) * | 2019-12-31 | 2020-12-01 | 深圳大学 | Absolute pressure sensor assembly and air bag type respiration measuring device |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| US20060047215A1 (en) | Combined sensor assembly | |
| KR100903172B1 (en) | Method for monitoring respiration in a wireless way and device for performing the same | |
| US8672853B2 (en) | Pressure sensor for monitoring a subject and pressure sensor with inflatable bladder | |
| US8696588B2 (en) | Device and method for determining a respiration rate | |
| US6254551B1 (en) | Apparatus for monitoring a mechanically transmitted signal based on the organs or vital functions and for processing the results | |
| US20090281394A1 (en) | Bio-mechanical sensor system | |
| US20180271380A1 (en) | Respiration rate monitoring by multiparameter algorithm in a device including integrated belt sensor | |
| CN107997768A (en) | A kind of wearable respiration measurement device and breath measuring method | |
| EP1681018A1 (en) | Sleep aspiration state measurement device | |
| AU2013322868B2 (en) | Pulse meter for new-borns | |
| CN212037525U (en) | Absolute pressure sensor assembly and air bag type respiration measuring device | |
| EP2236080B1 (en) | Sensor | |
| EP3551075B1 (en) | System and method for facilitating detection of a respiratory status | |
| CN208319203U (en) | A kind of device for sleep apnea syndrome monitoring | |
| CN111166335A (en) | Absolute pressure sensor assembly and air bag type respiration measuring device | |
| US20110251510A1 (en) | Respiration sensor for an infant feeding performance measurement device | |
| CN208740982U (en) | A kind of wearable respiration measurement device and respiration transducer | |
| CN214965439U (en) | SMD sleep breathing monitoring structure and sleep breathing monitoring system | |
| CN111166334A (en) | Respiration measuring method and device | |
| CN208551844U (en) | A kind of wearable sticker acquiring body sound signal | |
| CN209518869U (en) | A kind of respiratory effort identifies the sleep apnea monitoring device of equipment and its application | |
| US20220039749A1 (en) | Multiple sensor wearable and portable non-invasive respiration monitoring instrumentation | |
| CN212650828U (en) | Portable nasal respiration function detection device | |
| CN114831622A (en) | SMD sleep breathing monitoring structure and sleep breathing monitoring system | |
| WO2017007187A1 (en) | Ear insertion-type health monitoring device using piezo sensor |
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 | ||
| RJ01 | Rejection of invention patent application after publication |
Application publication date: 20200519 |
|
| RJ01 | Rejection of invention patent application after publication |