CN108704209B

CN108704209B - Respiratory rate monitoring device, respiratory rate monitoring system, respirator and oxygen inhaler

Info

Publication number: CN108704209B
Application number: CN201710356303.0A
Authority: CN
Inventors: 徐传毅
Original assignee: Nazhiyuan Technology Tangshan Co Ltd
Current assignee: Nazhiyuan Technology Tangshan Co Ltd
Priority date: 2017-05-19
Filing date: 2017-05-19
Publication date: 2024-04-16
Anticipated expiration: 2037-05-19
Also published as: CN108704209A

Abstract

The invention discloses a respiratory rate monitoring device, a respiratory rate monitoring system, a respirator and an oxygen inhaler. Wherein, respiratory rate monitoring device includes: the respiratory monitoring module and circuit processing module, the circuit processing module includes: the system comprises a signal preprocessing module, a central control module and a power supply module; the respiration monitoring module is used for outputting respiration electric signals according to air flow generated by inhalation or exhalation of a user; the signal preprocessing module is electrically connected with the respiration monitoring module and is used for preprocessing the respiration electric signal output by the respiration monitoring module; the central control module is electrically connected with the signal preprocessing module and is used for analyzing and calculating the respiratory frequency of a user in a first preset time interval according to the respiratory electric signals preprocessed by the signal preprocessing module; and the power supply module is electrically connected with the central control module and is used for providing electric energy. The respiratory rate monitoring device, the respiratory rate monitoring system, the breathing machine and the oxygen inhaler provided by the invention can sensitively and accurately monitor the respiratory rate of a user.

Description

Respiratory rate monitoring device, respiratory rate monitoring system, respirator and oxygen inhaler

Technical Field

The invention relates to the technical field of sensors, in particular to a respiratory rate monitoring device, a respiratory rate monitoring system, a respirator and an oxygen inhaler.

Background

At present, in serious patients treated in hospitals, a great part of patients have the choking risk due to the diseases, and particularly after such events happen at night, the patients cannot be found timely by family members and medical staff of the patients, so that the best rescue opportunity is missed.

Even in intensive care units, the time interval for nurses of the intensive care patients to visit the patients is at least more than 15 minutes due to related factors such as personnel and energy, and family members often mistakenly pause breathing and heartbeat as asleep due to lack of expertise although they are nursing at the bedside. The ischemic and anoxic tolerance of the human brain is extremely poor, and ischemic and anoxic brain diseases can be formed in excess of 5 minutes, so that even if patients are found to successfully finish cardiopulmonary resuscitation, cerebral resuscitation is difficult, and patients suffering from a plurality of respiratory arrest are caused, and even if cardiopulmonary resuscitation is successful, the ischemic and anoxic brain diseases are disabled to be plant people, so that medical resource waste and pain of family members of the patients are caused.

At present, although a plurality of breathing machine devices or oxygen inhalation devices with respiratory function are available on the market, the devices are large in price, most hospitals only have a small number of devices, so that the needs of patients cannot be met, most of the existing devices are complex in structure and operation, low in sensitivity and accuracy, and great inconvenience is brought to the use of related personnel such as doctors and/or guardians.

Therefore, the monitoring device, the system, the breathing machine and the oxygen inhalation machine which are low in cost, simple to operate and capable of sensitively and accurately monitoring the breathing frequency of a user are lacked in the prior art.

Disclosure of Invention

The invention aims at overcoming the defects of the prior art, and provides a respiratory rate monitoring device, a respiratory rate monitoring system, a respiratory machine and an oxygen inhalation machine, which are used for solving the problem that equipment in the prior art cannot sensitively and accurately monitor the respiratory rate of a user.

The invention provides a respiratory rate monitoring device, comprising: the respiratory monitoring module and circuit processing module, the circuit processing module includes: the system comprises a signal preprocessing module, a central control module and a power supply module; wherein,

the respiration monitoring module is used for outputting respiration electric signals according to air flow generated by inhalation or exhalation of a user;

the signal preprocessing module is electrically connected with the respiration monitoring module and is used for preprocessing the respiration electric signal output by the respiration monitoring module;

the central control module is electrically connected with the signal preprocessing module and is used for analyzing and calculating the respiratory frequency of a user in a first preset time interval according to the respiratory electric signals preprocessed by the signal preprocessing module;

And the power supply module is electrically connected with the central control module and is used for providing electric energy.

The invention also provides a respiratory rate monitoring system, comprising: the respiratory rate monitoring device and the terminal equipment; wherein,

the terminal equipment is connected with the respiratory rate monitoring device in a wired communication or wireless communication mode and is used for storing and displaying the respiratory rate obtained by analysis and calculation of the respiratory rate monitoring device and/or sending a control instruction for controlling the respiratory rate monitoring device.

The invention also provides a respiratory rate monitoring system, comprising: the respiratory rate monitoring device and the large database service platform; wherein,

the large database service platform is connected with the respiratory rate monitoring device in a wired communication or wireless communication mode and is used for receiving and storing the respiratory rate obtained by analysis and calculation of the respiratory rate monitoring device, analyzing and comparing the received respiratory rate with the respiratory rate in the large database service platform to obtain user analysis information, and sending the user analysis information to the respiratory rate monitoring device.

The invention also provides a respirator, comprising: the respiratory rate monitoring device or any one of the two respiratory rate monitoring systems, and a ventilator body, an airflow conduit, and a mask; wherein, the respiration monitoring module is arranged in the airflow pipeline and/or the mask;

The circuit processing module is arranged in the breathing machine main body; or the main body of the breathing machine is connected with the circuit processing module of the breathing frequency monitoring device through a preset port.

The invention also provides an oxygen inhaler, comprising: the respiratory rate monitoring device or any one of the two respiratory rate monitoring systems, and an oxygen inhaler main body, an air flow pipe and a mask; wherein, the respiration monitoring module is arranged in the airflow pipeline and/or the mask;

the circuit processing module is arranged in the oxygen inhaler main body; or oxygen inhalation machine main body and respiratory frequency monitoring device the circuit processing modules of the circuit processing modules are connected through preset ports.

According to the respiratory rate monitoring device, the respiratory rate monitoring system, the breathing machine and the oxygen inhalation machine, the respiratory rate of the user can be sensitively and accurately monitored by monitoring the air flow generated by inspiration or expiration of the user through the respiratory monitoring module. In addition, the respiratory rate monitoring device, the respiratory rate monitoring system, the respiratory machine and the oxygen inhalation machine provided by the invention have the advantages of high sensitivity and accuracy, reduced trouble caused by false alarm, simple structure and manufacturing process, low cost and suitability for large-scale industrial production.

Drawings

FIG. 1a is a functional block diagram of a respiratory rate monitoring apparatus according to an embodiment of the present invention;

fig. 1b is a functional block diagram of a signal preprocessing module in a first embodiment of a respiratory rate monitoring device according to the present invention;

fig. 2a is a schematic perspective view of an example one of a pneumatic sensor in a first embodiment of a respiratory rate monitoring device according to the present invention;

FIG. 2b is a schematic cross-sectional view of an example of a pneumatic sensor in a first embodiment of a respiratory rate monitoring device according to the present invention;

fig. 2c is a schematic structural diagram of an example two pneumatic sensor in the first embodiment of the respiratory rate monitoring device according to the present invention;

fig. 2d is a schematic structural diagram of an example three pneumatic sensor in the first embodiment of the respiratory rate monitoring device according to the present invention;

fig. 2e is a schematic structural diagram of an example four pneumatic sensor in the first embodiment of the respiratory rate monitoring device according to the present invention;

fig. 2f is a schematic structural diagram of an example five pneumatic sensor in a first embodiment of the respiratory rate monitoring device according to the present invention;

fig. 2g is a schematic structural diagram of an example six pneumatic sensor in a first embodiment of the respiratory rate monitoring device provided by the present invention;

FIG. 2h is a schematic diagram of a rebound ring according to the present invention;

FIG. 2i is a schematic structural view of an example seven of a pneumatic sensor employing the rebound ring provided by the present invention shown in FIG. 2 h;

fig. 2j is a schematic perspective view of a pneumatic sensor according to a first embodiment of the respiratory rate monitoring device of the present invention;

FIG. 3 is a functional block diagram of a respiratory rate monitoring device according to a second embodiment of the present invention;

FIG. 4 is a functional block diagram of a third embodiment of a respiratory rate monitoring device according to the present invention;

FIG. 5 is a functional block diagram of a respiratory rate monitoring system employing the respiratory rate monitoring apparatus of FIG. 4 according to the present invention;

FIG. 6 is another functional block diagram of a respiratory rate monitoring system employing the respiratory rate monitoring apparatus of FIG. 4 in accordance with the present invention;

fig. 7 is a schematic structural diagram of a first embodiment of a ventilator according to the present invention;

fig. 8 is a schematic structural diagram of a second embodiment of a ventilator according to the present invention;

FIG. 9 is a schematic diagram of an oxygen inhaler according to a first embodiment of the present invention;

fig. 10 is a schematic structural diagram of a second embodiment of the oxygen inhaler according to the present invention.

Detailed Description

The present invention will be described in detail with reference to the following embodiments for a full understanding of the objects, features and effects of the present invention, but the present invention is not limited thereto.

Fig. 1a is a functional block diagram of a respiratory rate monitoring device according to an embodiment of the present invention. As shown in fig. 1a, the respiratory rate monitoring device includes: a respiration monitoring module 110 and a circuit processing module 120, the circuit processing module 120 comprising: a signal preprocessing module 121, a central control module 122, and a power supply module 123; wherein, the respiration monitoring module 110 is configured to output a respiration electrical signal according to an airflow generated by inhalation or exhalation of the user; the signal preprocessing module 121 is electrically connected with the respiration monitoring module 110 and is used for preprocessing the respiration electric signal output by the respiration monitoring module 110; the central control module 122 is electrically connected with the signal preprocessing module 121 and is used for analyzing and calculating the respiratory rate of the user according to the respiratory electric signals preprocessed by the signal preprocessing module 121; the power supply module 123 is electrically connected to the central control module 122, and is used for providing electric energy.

Optionally, the respiration monitoring module comprises: at least one pneumatic sensor for converting the pressure of the air flow generated by inhalation or exhalation of the user acting on the at least one pneumatic sensor into respiratory electric signal output.

In an embodiment of the present invention, the respiration monitoring module may include one pneumatic sensor or may include a plurality of pneumatic sensors. The respiratory monitoring module comprises a pneumatic sensor and has the advantages of simple structure and easy realization, so that the respiratory frequency monitoring device is simpler in structure; the respiratory monitoring module comprises a plurality of pneumatic sensors and has the advantages of enabling the respiratory frequency monitoring device to be more sensitive and enabling the monitoring result to be more accurate.

The number of the signal preprocessing modules may be one or more, and may be selected as required by those skilled in the art, which is not limited herein. However, it should be noted that the number of signal preprocessing modules should be the same as the number of pneumatic sensors in the respiration monitoring module so that the signal preprocessing modules can be electrically connected to the pneumatic sensors in the respiration monitoring module in a one-to-one correspondence.

Specifically, if the respiration monitoring module comprises a pneumatic sensor, the number of the signal preprocessing modules is only one, and the signal preprocessing modules are respectively and electrically connected with the pneumatic sensor and the central control module; if the respiration monitoring module includes a plurality of pneumatic sensors, the number of the signal preprocessing modules is the same as the number of the plurality of pneumatic sensors, and the plurality of signal preprocessing modules are also a plurality of, and are respectively and electrically connected with the plurality of pneumatic sensors in a one-to-one correspondence manner, and meanwhile, the plurality of signal preprocessing modules are also respectively and electrically connected with the central control module, for example: if the respiration monitoring module comprises 2 pneumatic sensors, the number of the signal preprocessing modules is the same as that of the 2 pneumatic sensors, the number of the signal preprocessing modules is also 2, the input ends of the 2 signal preprocessing modules are respectively and electrically connected with the output ends of the 2 pneumatic sensors in one-to-one correspondence, and meanwhile, the output ends of the 2 signal preprocessing modules are respectively and electrically connected with different signal input ends of the central control module in one-to-one correspondence.

Wherein, at least one pneumatic sensor is a friction power generation type pneumatic sensor and/or a piezoelectric power generation type pneumatic sensor. That is, the at least one pneumatic sensor may be a pneumatic sensor made of a friction generator and/or a piezoelectric generator, and may be selected by those skilled in the art according to actual needs, which is not limited herein.

Further, at least one pneumatic sensor in the respiration monitoring module may distinguish between electrical respiratory signals resulting from pressure conversion of the air flow generated by the inhalation or exhalation of the user acting thereon. Specifically, the at least one pneumatic sensor is further configured to: converting the pressure of the air flow generated by inhalation of a user on the pneumatic sensor into a forward respiratory electric signal to be output; the pressure of the airflow generated by the user exhaling on the pneumatic sensor is converted into negative respiratory electric signal output. In this case, the signal preprocessing module is further configured to: preprocessing a positive respiratory electric signal or a negative respiratory electric signal output by at least one pneumatic sensor; a timer and a counter are arranged in the central control module; the central control module is further configured to: when the forward respiratory electric signal preprocessed by the signal preprocessing module is received, starting a timer to count time; and stopping timing when the negative respiration electric signal preprocessed by the signal preprocessing module is received, obtaining timing time, and starting a counter to count so as to obtain the respiration times of the user.

Further, as shown in fig. 1b, the signal preprocessing module 121 may include: a rectification module 1211, a filtering module 1212, an amplifying module 1213, and an analog-to-digital conversion module 1214. The rectification module 1211 is electrically connected with the pneumatic sensor in the respiration monitoring module and is used for rectifying the respiration electric signal output by the pneumatic sensor; the filtering module 1212 is electrically connected with the rectifying module 1211 and is used for filtering the respiratory electric signal after rectifying treatment to remove interference clutter; the amplifying module 1213 is electrically connected with the filtering module 1212 and is used for amplifying the respiratory electric signal after the filtering process; the analog-to-digital conversion module 1214 is electrically connected to the amplification module 1213, and is configured to convert the analog respiratory electrical signal output by the amplification module 1213 into a digital respiratory electrical signal, and output the converted digital respiratory electrical signal to the central control module 122. It should be noted that the above modules (i.e., the rectifying module 1211, the filtering module 1212, the amplifying module 1213, and the analog-to-digital converting module 1214) may be selected according to the needs of those skilled in the art, and are not limited herein. For example, the rectification module 1211 may be omitted if the respiratory electrical signal output by the at least one pneumatic sensor in the respiratory monitoring module 110 does not require rectification.

For ease of understanding, the pneumatic sensor in the first embodiment of the respiratory rate monitoring device provided by the present invention will be described in detail below with reference to examples one to seven. Among them, examples one to seven are friction power generation type pneumatic sensors.

Example one

Fig. 2a and fig. 2b are a schematic perspective view and a schematic cross-sectional view of an example of a pneumatic sensor in a first embodiment of a respiratory rate monitoring device according to the present invention. As shown in fig. 2a and 2b, the pneumatic sensor includes: a housing 211, a diaphragm assembly 212, and an electrode assembly 213. Wherein, the housing 211 is formed with a receiving chamber inside, an air inlet 2111 is formed on a side wall of the housing 211, at least one air outlet 2112 is formed on a bottom wall, and the air inlet 2111 and the air outlet 2112 are respectively communicated with the receiving chamber to form an air flow path, so that an air flow generated by inhalation or exhalation of a user passes through the air flow path; the two ends of the diaphragm assembly 212 are fixedly arranged in the accommodating chamber inside the housing 211, and a vibration gap is formed between the diaphragm assembly 212 and the bottom wall of the housing 211 and the electrode assembly 213 respectively, and the diaphragm assembly 212 vibrates reciprocally between the electrode assembly 213 and the bottom wall of the housing 211 under the driving of the air flow inside the accommodating chamber; the electrode assembly 213 is a signal output end of the pneumatic sensor, is located in a receiving chamber inside the housing 211, is opposite to the diaphragm assembly 212, and the diaphragm assembly 212 vibrating reciprocally rubs against the bottom wall of the housing 211 and/or the electrode assembly 213 to generate a respiratory electrical signal, and is output by the electrode assembly 213.

The diaphragm assembly 212 is a flexible assembly, preferably has a long strip shape, and the long strip diaphragm assembly 212 is located in the accommodating chamber inside the housing 211, and two ends of the diaphragm assembly are fixedly arranged. Specifically, a diaphragm ring 2113, a first gasket 2114, and a second gasket 2115 are provided in an accommodation chamber inside the housing 211. Wherein, the vibrating diaphragm ring 2113 is annular, two ends of the vibrating diaphragm assembly 212 are respectively fixed on the vibrating diaphragm ring 2113, and an air flow channel is formed between the side edge of the vibrating diaphragm assembly 212 and the vibrating diaphragm ring 2113, and the vibrating diaphragm assembly 212 on the vibrating diaphragm ring 2113 can vibrate reciprocally between the electrode assembly 213 and the bottom wall of the housing 211 under the driving of the air flow in the accommodating chamber. The first gasket 2114 is a ring with a notch, and is located between the diaphragm ring 2113 and the electrode assembly 213, so that a vibration gap is formed between the diaphragm assembly 212 and the electrode assembly 213; the second gasket 2115 is also notched annular and is positioned between the diaphragm ring 2113 and the bottom wall of the housing 211 so that a vibration gap is formed between the diaphragm assembly 212 and the bottom wall of the housing 211.

Optionally, the pneumatic sensor may further include a friction film assembly disposed on a lower surface of the electrode assembly 213, wherein a vibration gap is formed between the diaphragm assembly 212 and the bottom wall of the housing 211 and the friction film assembly, respectively, and the diaphragm assembly 212 is driven by the air flow in the accommodating chamber to vibrate reciprocally between the friction film assembly and the bottom wall of the housing 211, so as to generate a respiratory electric signal by contacting and rubbing with the friction film assembly and/or the bottom wall of the housing 211.

Example two

Fig. 2c is a schematic structural diagram of an example two pneumatic sensor in the first embodiment of the respiratory rate monitoring device according to the present invention. As shown in fig. 2c, the pneumatic sensor includes: the sensor includes a shield case 221, an insulating layer 222 provided on a part or all of an inner side surface of the shield case 221, and at least one sensing unit. Wherein, the shielding shell 221 is provided with at least two air ports 2211, and air flow generated by inhalation or exhalation of a user passes through the at least two air ports 2211; specifically, one air vent 2211 is formed in the middle of the left and right sides of the shielding shell 221, and air flow can enter from one air vent 2211 and flow out from the other air vent 2211. The sensing unit includes: at least one fixed layer and one free layer; at least one fixing layer is fixedly arranged on the shielding shell 221; the free layer is provided with a fixed part and a friction part; the fixed portion of the free layer is fixedly connected with at least one fixed layer or shield shell 221; the free layer is rubbed with at least one fixed layer and/or the shield shell 221 by the rubbing portion. At least one fixed layer is a signal output end of the pneumatic sensor, or at least one fixed layer and the shield case 221 are signal output ends of the pneumatic sensor.

Wherein fig. 2c shows only schematically a schematic structural view of an embodiment of the pneumatic sensor comprising a sensor unit comprising: a fixed layer and a free layer 2231. At this time, the air inlet direction of the air flow is parallel to the plane of the fixing layer in the pneumatic sensor. Specifically, the fixing layer is fixed below the inside of the shield case 221. The fixing layer is a polymer insulating layer 2233 with a side surface coated with an electrode 2232, and the insulating layer 222 is disposed between the side surface coated with the electrode 2232 of the polymer insulating layer 2233 and the inner side surface of the shield shell 221. The fixed portion of the free layer 2231 is fixedly connected with the high polymer insulating layer 2233 through a gasket 2234, the free layer 2231 is rubbed with the surface of the high polymer insulating layer 2233, which is not plated with the electrode 2232, and/or the surface of the shielding shell 221, which is not provided with the insulating layer, through a friction portion, and the electrode 2232 and the shielding shell 221 are signal output ends of the pneumatic sensor.

Example three

Fig. 2d is a schematic structural diagram of an example three pneumatic sensor in the first embodiment of the respiratory rate monitoring device according to the present invention. As shown in fig. 2d, the pneumatic sensor includes: a housing 231, and a first polymer film 233, a support structure 234, and an electrode 232 which are sequentially provided inside the housing 231. The support structure 234 is disposed outside the electrode 232, and the first polymer film 233 is sleeved outside the electrode 232 and the support structure 234. The housing 231 has a hollow structure, and an electrode 232 and a first polymer film 233 are sleeved inside the housing. The central axes of the housing 231, the electrode 232 and the first polymer film 233 are positioned on the same straight line, and the surfaces of the three are separated from each other. The housing 231 may be a metal housing or a nonmetallic insulating housing. Structurally, housing 231 further includes oppositely disposed first and second end surfaces 2311 and 2312. Wherein, the first end surface 2311 is provided with at least one air inlet hole for air to flow in, and the second end surface 2312 is provided with at least one air outlet hole for air to flow out. Specifically, at least one of the first end surface 2311 and the second end surface 2312 may be integrally provided on the housing 231, thereby better protecting the internal structure of the pneumatic sensor; alternatively, at least one of the first end surface 2311 and the second end surface 2312 may be detachably provided to the housing 231 to facilitate replacement and disassembly of the housing 231 by a user, etc.

The electrode 232 is provided inside the housing 231, and is provided along the central axis direction of the housing 231, and the surface thereof may be provided as a metal electrode layer or a non-metal electrode layer. The electrode 232 may have a solid or hollow structure. Preferably, the electrode 232 has a hollow structure inside, so that the air flow channel is formed between the electrode 232 and the first polymer film 233 and/or the air flow channel is formed inside the electrode 232, and meanwhile, the weight of the electrode 232 with the hollow structure is smaller, so that the whole pneumatic sensor is lighter; more preferably, the electrode 232 is further provided with a through hole communicating inside and outside so as to increase the size of the air flow in the air flow channel and enhance the friction effect. The first polymer film 233 is a cylindrical film sleeved outside the electrode 232, and the shape of the first polymer film 233 is matched with the shape of the electrode 232. The first polymer film 233 is further provided with at least one vibrating diaphragm, and when the air flow enters the air inlet hole, the air flow drives the vibrating diaphragm to vibrate through the air flow channel. Each diaphragm has a fixed end integrally connected with the first polymer film 233 and a free end capable of rubbing against the electrode 232 under the driving of air flow. The fixed end of each vibrating diaphragm is arranged on one side close to the air inlet hole, and the free end of each vibrating diaphragm is arranged on one side close to the air outlet hole. And, the electrode 232 serves as a signal output terminal of the air sensor.

Specifically, in order to prevent the middle portion of the first polymer film 233 from contacting the electrode 232 to be unable to be effectively separated, further provided between the electrode 232 and the first polymer film 233 are: at least one support structure 234, the support structure 234 is used for forming a gap between the electrode 232 and the first polymer film 233, so that the free end of the diaphragm on the first polymer film 233 is contacted and separated from the electrode 232. Wherein the thickness of the support structure 234 is preferably between 0.01-2.0 mm. Under the condition that no air flow flows in, the vibrating diaphragm on the first polymer film 233 does not rub with the surface of the electrode 232, and no induced charge is generated; when the air flows in from the air inlet on the first end surface 2311, the vortex generated by the air flow vibrates the free end of the diaphragm, and the vibrating free end is contacted with and separated from the surface of the electrode 232 at a corresponding frequency, that is, the diaphragm rubs against the surface of the electrode 232, so that induced charges are generated on the electrode 232. The electrode 232 is used as a signal output end of the pneumatic sensor, and a wire connected with the electrode is arranged on the electrode 232, so that the induced charges on the surface of the electrode 232 are output as induced electric signals through the wire. The electrode 232 may form a current loop together with a ground point in an external circuit, so that an electrical signal output is realized in a single electrode manner.

Therefore, the pneumatic sensor provided by the invention has the advantages of simple manufacturing process and low manufacturing cost. In addition, the pneumatic sensor provided by the invention fully utilizes the inertia effect of the free end of the vibrating diaphragm by further arranging the vibrating diaphragm on the first polymer film, increases the friction effect of friction power generation and improves the signal sensitivity.

Example four

Fig. 2e is a schematic structural diagram of an example four pneumatic sensor in the first embodiment of the respiratory rate monitoring device according to the present invention. As shown in fig. 2e, the pneumatic sensor includes: first electrode ring 241, annular friction pack and second electrode ring 243, which are stacked in this order along the same central axis, wherein the annular friction pack in this example comprises: a first high molecular polymer insulating ring 242; wherein, two surfaces of the first electrode ring 241 opposite to the first high polymer insulating ring 242 and/or two surfaces of the first high polymer insulating ring 242 opposite to the second electrode ring 243 constitute a friction interface.

In this example, a tubular structure formed by stacking a first electrode ring 241, a first polymer insulating ring 242, and a second electrode ring 243 is used to form a fluid passage 244. When fluid passes through the fluid channel 244, the two surfaces of the first electrode ring 241 opposite to the first polymer insulating ring 242 and/or the two surfaces of the first polymer insulating ring 242 opposite to the second electrode ring 243 contact and rub, and charges are induced at the first electrode ring 241 and the second electrode ring 243, and the first electrode ring 241 and/or the second electrode ring 243 are the electrical signal output ends of the pneumatic sensor.

The working principle of the pneumatic sensor is briefly described as follows: as the fluid passes through the fluid passage 244, the fluid acts on the pneumatic sensor such that the two surfaces of the first electrode ring 241 opposite the first polymer insulating ring 242 and/or the two surfaces of the first polymer insulating ring 242 opposite the second electrode ring 243 contact and rub and induce an electrical charge at the first electrode ring 241 and the second electrode ring 243, wherein the magnitude of the electrical signal output at the first electrode ring 241 and the second electrode ring 243 has an approximately linear relationship with the magnitude of the pressure of the fluid acting on the pneumatic sensor, which in turn reflects the magnitude of the flow of the fluid (the magnitude of the pressure of the fluid acting on the pneumatic sensor has an approximately linear relationship with the magnitude of the flow of the fluid), that is, the magnitude of the electrical signal output at the first electrode ring 241 and the second electrode ring 243 has an approximately linear relationship with the magnitude of the flow of the fluid, i.e., the magnitude of the electrical signal output at the first electrode ring 241 and the second electrode ring 243 has a larger magnitude of the flow of the fluid, such that the greater the pressure of the fluid acting on the pneumatic sensor acts on the pneumatic sensor has the magnitude of the electrical signal at the first electrode ring 241 and the second electrode ring 243.

Example five

Fig. 2f is a schematic structural diagram of an example five pneumatic sensor in a first embodiment of the respiratory rate monitoring device according to the present invention. As shown in fig. 2f, the pneumatic sensor includes: a first electrode ring 251, an annular friction member, and a second electrode ring 254, which are sequentially stacked along the same central axis; the annular friction pack in this example comprises: the first polymer insulating ring 252 and the second polymer insulating ring 253, the two surfaces of the first electrode ring 251 opposite to the first polymer insulating ring 252 and/or the two surfaces of the first polymer insulating ring 252 opposite to the second polymer insulating ring 253 and/or the two surfaces of the second polymer insulating ring 253 opposite to the second electrode ring 254 form a friction interface.

In the present example of the present invention, the first electrode ring 251, the first polymer insulating ring 252, the second polymer insulating ring 253, and the second electrode ring 254 are stacked to form a tubular structure for forming the fluid passage 255. When fluid passes through the fluid channel 255, under the action of the fluid, two surfaces of the first electrode ring 251 opposite to the first high polymer insulating ring 252 and/or two surfaces of the first high polymer insulating ring 252 opposite to the second high polymer insulating ring 253 and/or two surfaces of the second high polymer insulating ring 253 opposite to the second electrode ring 254 contact and rub, and charges are induced at the first electrode ring 251 and the second electrode ring 254, and the first electrode ring 251 and/or the second electrode ring 254 are electric signal output ends of the pneumatic sensor.

In this example, the principle of operation of the pneumatic sensor is similar to that of the example shown in fig. 2e, and will not be described in detail here.

Example six

Fig. 2g is a schematic structural diagram of an example six pneumatic sensor in a first embodiment of the respiratory rate monitoring device provided by the present invention. As shown in fig. 2g, the pneumatic sensor includes: a first electrode ring 261, an annular friction member, and a second electrode ring 265, which are sequentially stacked along the same central axis; the annular friction pack in this example comprises: the first polymer insulating ring 262, the intermediate film ring 263, and the second polymer insulating ring 264, and the two surfaces of the first electrode ring 261 opposite to the first polymer insulating ring 262 and/or the two surfaces of the first polymer edge ring 262 opposite to the intermediate film ring 263 and/or the two surfaces of the intermediate film ring 263 opposite to the second polymer edge ring 264 and/or the two surfaces of the second polymer insulating ring 264 opposite to the second electrode ring 265 constitute a friction interface.

In this example, a tubular structure of a first electrode ring 261, a first polymer insulating ring 262, an intermediate film ring 263, a second polymer insulating ring 264, and a second electrode ring 265 are stacked to form a fluid passage 266. As fluid passes through the fluid channel 266, the two surfaces of the first electrode ring 261 opposite the first polymer insulating ring 262 and/or the two surfaces of the first polymer edge ring 262 opposite the intervening film ring 263 and/or the two surfaces of the intervening film ring 263 opposite the second polymer edge ring 264 and/or the two surfaces of the second polymer insulating ring 264 opposite the second electrode ring 265 contact and rub, and an electrical charge is induced at the first electrode ring 261 and the second electrode ring 265, the first electrode ring 261 and/or the second electrode ring 265 being the electrical signal output of the pneumatic sensor.

In this example, the working principle of the pneumatic sensor is similar to that of the pneumatic sensor in the example shown in fig. 2e, and will not be described here again.

The first electrode ring and the second electrode ring of the pneumatic sensor in the above examples four to six may be led out through a first lead and a second lead (not shown in the drawings), which facilitates subsequent processing of the electrical signal generated by the pneumatic sensor, and of course, those skilled in the art may not use the leads, which is not limited herein.

In a preferred example of the present invention, the pneumatic sensor includes: the first electrode ring, the annular friction assembly and the second electrode ring are sequentially stacked along the same central axis; in this example, the annular friction pack includes: a first high polymer insulating ring, an intermediate electrode ring a second high molecular polymer insulating ring; the two surfaces of the first electrode ring opposite to the first high polymer insulating ring and/or the two surfaces of the first high polymer edge ring opposite to the middle electrode ring and/or the two surfaces of the middle electrode ring opposite to the second high polymer edge ring and/or the two surfaces of the second high polymer insulating ring opposite to the second electrode ring form a friction interface, when fluid passes through the fluid channel, charges are induced at the first electrode ring, the middle electrode ring and the second electrode ring, and the first electrode ring and/or the middle electrode ring and/or the second electrode ring are electric signal output ends of the pneumatic sensor.

It should be understood that the pneumatic sensor in this preferred example is replaced by an intermediate electrode ring in the example shown in fig. 2g, and the specific embodiment and the working principle thereof are similar to those of the example shown in fig. 2g, except that when fluid passes through the fluid channel, charges are induced at the first electrode ring, the intermediate electrode ring and the second electrode ring, and the first electrode ring and/or the intermediate electrode ring and/or the second electrode ring are/is the electrical signal output end of the pneumatic sensor.

In this preferred example, the first electrode ring, the second electrode ring and the intermediate electrode ring of the pneumatic sensor may be led out through a first lead, a second lead and a third lead (not shown in the figure), which facilitates subsequent processing of the electrical signal generated by the pneumatic sensor, although the person skilled in the art may not use any leads, and this is not limited herein.

In the above-described fourth to sixth examples, in order to further increase the effect of friction power generation, a micro-nano structure (not shown in the drawing) is provided on at least one of the two opposite surfaces constituting the friction interface, so that more electric charges are induced on the first electrode ring and/or the intermediate electrode ring and/or the second electrode ring.

The first electrode ring and/or the annular friction assembly and/or the second electrode ring in the above-described examples four to six comprise a rebound ring having a rebound effect, wherein the rebound ring comprises: a fixed ring and a rebound net arranged on the fixed ring.

Specifically, in order to enhance the effect of friction power generation, the first electrode ring and/or the first high polymer insulating ring and/or the intervening thin film ring and/or the intervening electrode ring and/or the second high polymer insulating ring and/or the second electrode ring in the above-described fourth to sixth examples may be rebound rings having a rebound effect, wherein the rebound rings 270 include: a stationary ring 271 and a resilient web 272 disposed on the stationary ring, as shown in fig. 2 h.

In the above-described examples four to six, the first electrode ring was a first electrode rebound ring having a rebound effect, wherein the material of the rebound net of the first electrode rebound ring was the same as the material of the first electrode ring.

In the above-described examples four to six, the second electrode ring was a second electrode rebound ring having a rebound effect, wherein the material of the rebound net of the second electrode rebound ring was the same as the material of the second electrode ring.

In the fourth to sixth examples, the first high polymer insulating ring is a first high polymer rebound ring having a rebound effect, wherein a rebound net of the first high polymer rebound ring is the same as a material of the first high polymer insulating ring.

In the fifth to sixth examples, the second high polymer insulating ring is a second high polymer rebound ring, wherein a rebound net of the second high polymer rebound ring is made of the same material as the second high polymer insulating ring.

In example six above, the intermediate film loop is a high molecular polymer rebound loop, wherein the material of the rebound net of the intermediate film rebound loop is the same as the material of the intermediate film loop.

Preferably, the intermediate electrode ring is an electrode rebound ring, wherein the material of the rebound net of the electrode rebound ring is the same as the material of the intermediate electrode ring.

In the present example, the rebound effect of the rebound net is related not only to the material of the rebound net, but also to the net structure of the rebound net itself, the net structure itself has a certain elasticity, and in addition, the density of the net structure also affects the rebound effect.

Example seven

FIG. 2i is a schematic structural view of an example seven of a pneumatic sensor employing the rebound ring provided by the present invention shown in FIG. 2 h. As shown in fig. 2i, the pneumatic sensor includes: a first electrode ring 281, a first high polymer rebound ring 282, and a second electrode ring 283 stacked in this order along the same central axis; wherein, two surfaces of the first electrode ring 281 opposite to the first high polymer rebound ring 282 and/or two surfaces of the first high polymer rebound ring 282 opposite to the second electrode ring 283 constitute a friction interface. In this example, a tubular structure of a first electrode ring 281, a first high polymer rebound ring 282, and a second electrode ring 283 are stacked to form a fluid passage 284. When fluid passes through the fluid channel 284, the first polymer rebound ring 282 rubs against the first electrode ring 281 and/or the second electrode ring 283 due to the fluid effect, and induces charges at the first electrode ring 281 and the second electrode ring 283, and the first electrode ring 281 and/or the second electrode ring 283 are electrical signal output ends of the pneumatic sensor.

Similarly, the specific structure of other pneumatic sensors employing resilient rings is not described herein.

In the above-described fourth to seventh examples, in order to enhance the contact friction effect between the two surfaces constituting the friction interface, the pneumatic sensor may further include: at least one washer disposed between the two surfaces constituting the friction interface, and a contact separation space is formed between portions of the two surfaces not in contact with the washer. However, the disposed washer cannot affect the contact friction between the two surfaces constituting the friction interface, and thus, the disposed washer has a smaller surface area than the two surfaces constituting the friction interface, so that a contact separation space is formed between the two surfaces constituting the friction interface and the portion where the two surfaces are not in contact with the washer, and the size of the surface area of the washer can be set as required by those skilled in the art, which is not limited herein.

In the fourth to seventh examples, in order to better protect the pneumatic sensor, to reduce the influence of external factors such as electromagnetic interference and moisture on the normal operation of the pneumatic sensor, the pneumatic sensor may further include: and the shielding component and the packaging component are sequentially arranged from inside to outside and are used for coating the first electrode ring, the annular friction component and the second electrode ring and exposing the fluid channel. That is, the shielding member and the packing member are covered along the annular body structure formed by the first electrode ring, the annular friction member and the second electrode ring, and during the covering, the fluid passage 291 through which the fluid passes is exposed, as shown in fig. 2j, so that the two surfaces constituting the friction interface rub against each other as the fluid passes through the pneumatic sensor to induce an electrical charge at the first electrode ring and the second electrode ring.

In order to enhance the vibration of the fluid acting on the pneumatic sensor, the pneumatic sensor may further comprise: at least one vibration assembly 292, which may be disposed on an inner wall of the pneumatic sensor encased with the encapsulation assembly, wherein the at least one vibration assembly vibrates under the influence of the fluid for enhancing the vibration of the fluid on the pneumatic sensor, as shown in fig. 2 j.

Wherein the electrode assembly of the pneumatic sensor in example one, the electrodes of the pneumatic sensors in example two and example three, the first electrode ring, the second electrode ring and the intervening electrode ring of the pneumatic sensor in examples four to seven may be selected from indium tin oxide, graphene, silver nanowire film, metal or alloy.

It should be appreciated that when the airflow generated by the user's breath acts on at least one of the pneumatic sensors of examples one to seven described above, the electrical signals output by the electrodes of examples one to seven are respiratory electrical signals referred to in the present invention. Specifically, when the air flow generated by inhalation of the user acts on the pneumatic sensor in the above examples one to seven, the electric signals output by the electrodes in the examples one to seven are the forward respiratory electric signals mentioned in the present invention; when the air flow generated by the user exhaling acts on the pneumatic sensor in the above examples one to seven, the electric signal output by the electrode in the examples one to seven is the negative respiration electric signal mentioned in the present invention.

Fig. 3 is a functional block diagram of a respiratory rate monitoring device according to a second embodiment of the present invention. As shown in fig. 3, the respiratory rate monitoring device of the second embodiment is different from the respiratory rate monitoring device of the first embodiment in that: the circuit processing module 120 includes, in addition to: the signal preprocessing module 121, the central control module 122, the power supply module 123, the wireless transceiver module 124 and the interactive function module 125. The wireless transceiver module 124 is electrically connected to the central control module 122, and is configured to send the respiratory rate obtained by analysis and calculation by the central control module 122 to a preset receiving device in a wireless communication manner, so that a doctor and/or a guardian can check the respiratory rate on the preset receiving device, where the preset receiving device may be a terminal device and/or a large database service platform; the interactive function module 125 is electrically connected to the central control module 122, and is configured to send a user interactive instruction to the central control module 122; wherein the user interaction instruction comprises at least one of the following: an on command, an off command, and a user information initialization command.

Specifically, the on or off command is used to control the on or off of the central control module 122, so as to control the on or off of the monitoring process; the user information initialization instructions are used for zeroing the monitored respiratory rate or establishing new respiratory rate monitoring data, such as respiratory monitoring time, respiratory monitoring frequency and user related information. In addition, the interactive function module 125 may preset the identification information of the user, so as to monitor the same user continuously. Other descriptions are referred to in the first embodiment, and will not be repeated here.

Fig. 4 is a functional block diagram of a respiratory rate monitoring device according to a third embodiment of the present invention. As shown in figure 4 of the drawings, the respiratory rate monitoring device of the third embodiment differs from the respiratory rate monitoring device of the second embodiment in that: the circuit processing module further includes: a display module 126 and an alarm module 127. The display module 126 is electrically connected to the central control module 122, and is configured to display the respiratory rate obtained by the central control module 122; the central control module 122 is further configured to: judging whether the respiratory frequency obtained by analysis and calculation accords with a preset respiratory frequency range or not, and outputting an alarm control signal according to a judging result; the alarm module 127 is electrically connected to the central control module 122, and is configured to perform alarm prompting according to an alarm control signal output by the central control module 122. The preset respiratory rate range reasonably indicates a range value of a normal respiratory rate, and a respiratory abnormality of a user is indicated by a respiratory rate range which is larger than or smaller than the preset respiratory rate range, and a shortness of breath of the user is indicated by a respiratory rate range which is larger than the preset respiratory rate range; less than the preset frequency range indicates that the user breathes slowly. Specifically, when the central control module 122 determines that the respiratory rate obtained by analysis and calculation does not conform to the preset respiratory rate range, an alarm control signal is sent out, and the alarm module 127 carries out alarm prompt according to the alarm control signal so as to prompt the user of abnormal respiration. Other descriptions can refer to the descriptions in the second embodiment, and are not repeated here.

It should be understood that the wireless transceiver module 124, the interactive function module 125, the display module 126 and the alarm module 127 in the second and third embodiments may be selected according to the design of those skilled in the art, and are not limited herein. For example, if communication with the predetermined receiving device is not required or is performed by a wired connection, the wireless transceiver module 124 may be omitted; the interactive function module 125 may be omitted if manual control of the respiratory rate monitoring device is not required; if the respiratory rate does not need to be displayed, the display module 126 may be omitted; the alarm module 127 may be omitted if the alarm function is not required.

The specific working principles of the first embodiment and the third embodiment of the respiratory rate monitoring device provided by the present invention are described in detail below.

First case: the respiration monitoring module comprises a pneumatic sensor, and a signal preprocessing module electrically connected with the pneumatic sensor is arranged in the circuit processing module.

In the third embodiment, the user can control the power supply module to communicate with the central control module through the interactive function module, so that the central control module starts working; and the user can also set the respiratory rate to be monitored through the interactive function module. If the interactive function module is not arranged in the circuit processing module (as shown in the embodiment I), the operation is started according to the preset respiratory frequency.

Step one: when a user inhales, the pneumatic sensor senses the pressure acted on the pneumatic sensor by the air flow generated by the inhalation of the user, converts the pressure acted on the pneumatic sensor into a corresponding forward respiratory electric signal, and outputs the corresponding forward respiratory electric signal to the signal preprocessing module which is correspondingly and electrically connected with the pneumatic sensor, and the signal preprocessing module preprocesses the forward respiratory electric signal output by the pneumatic sensor; when the central control module receives the forward respiratory electric signal preprocessed by the signal preprocessing module, a timer arranged in the central control module is started to count.

Step two: when a user exhales, the pneumatic sensor senses the pressure acted on the air flow generated by the user exhales and converts the pressure acted on the air flow into a corresponding negative respiratory electric signal to be output to a signal preprocessing module which is correspondingly and electrically connected with the pneumatic sensor, and the signal preprocessing module preprocesses the negative respiratory electric signal output by the pneumatic sensor; when the central control module receives the negative respiration electric signal preprocessed by the signal preprocessing module, stopping the timer arranged in the central control module to count to obtain a first count time X1 (namely, the time interval of first respiration of a user), and then resetting the timer arranged in the central control module; meanwhile, the central control module is started to count the counter arranged inside, so that the breathing times C1=1 of the user are obtained.

It should be noted that, when the user inhales again, the procedure of the first step will be repeated, which will not be described here again; after the process is finished, when the user exhales again, the pneumatic sensor senses the pressure acted on the air flow generated by the user exhales and converts the pressure acted on the air flow into a corresponding negative respiratory electric signal, and the negative respiratory electric signal is output to a signal preprocessing module which is correspondingly and electrically connected with the pneumatic sensor, and the signal preprocessing module preprocesses the negative respiratory electric signal output by the pneumatic sensor; when the central control module receives the negative respiration electric signal preprocessed by the signal preprocessing module, stopping the timer arranged in the central control module to count to obtain second count time X2 (namely, the time interval of the second respiration of the user), and resetting the timer arranged in the central control module; meanwhile, the central control module starts a counter arranged in the central control module to count up, so that the breathing times C2=C1+1=2 of the user are obtained, the cycle is repeated, and the like, and finally, the time intervals X1 and X2 … … Xn of each breathing of the user and the total breathing times C=Cn=n of the user are obtained.

Step three: the central control module judges whether the positive respiration electric signal or the negative respiration electric signal preprocessed by the signal preprocessing module is received again in the second preset time interval, if the corresponding positive respiration electric signal or the negative respiration electric signal output by the pneumatic sensor through the signal preprocessing module is not received in the second preset time interval, the danger that the user may have respiratory disorder or sudden stop is indicated, the central control module outputs an alarm control signal to the alarm module under the condition that the positive respiration electric signal or the negative respiration electric signal output by the signal preprocessing module is not received in the second preset time interval, the alarm module carries out alarm prompt according to the alarm control signal to inform doctors, guardians and other related personnel to take necessary measures, and meanwhile, the central control module continues to wait for receiving the positive respiration electric signal or the negative respiration electric signal preprocessed by the signal preprocessing module, so that the process of the first step or the second step is repeated. The person skilled in the art may set the second preset time interval according to actual needs, which is not limited herein, and for example, the second preset time interval may be 1s.

Step four: in the process of monitoring the respiration of a user by using the respiration rate monitoring device, the central control module analyzes and calculates the respiration rate of the user within a first preset time interval, judges whether the respiration rate obtained by analysis and calculation accords with a preset respiration rate range, if so, indicates that the respiration of the user is normal, and if the respiration rate obtained by analysis and calculation is greater than or less than the preset respiration rate range, indicates that the respiration of the user is abnormal, and specifically, if the respiration rate obtained by analysis and calculation is greater than the preset respiration rate range, indicates that the respiration of the user is rapid; if the respiratory rate obtained by analysis and calculation is smaller than the preset respiratory rate range, the user is indicated to breathe slowly, the central control module outputs an alarm control signal to the alarm module under the condition that the respiratory rate obtained by analysis and calculation does not accord with the preset respiratory rate range, the alarm module carries out alarm prompt according to the alarm control signal so as to inform doctors and/or guardians and other related personnel to take necessary measures, and meanwhile, the central control module also continues to wait for receiving the positive respiratory electric signal or the negative respiratory electric signal after being preprocessed by the signal preprocessing module, so that the processes from the first step to the third step are repeated. The first preset time interval may be set by a person skilled in the art according to actual needs, and is not limited herein, for example, the first preset time interval may be 1min, and the preset respiratory frequency range may be 14-16 times/min.

Second case: the respiration monitoring module comprises a plurality of pneumatic sensors, the circuit processing module also comprises a plurality of signal preprocessing modules, the plurality of signal preprocessing modules are the same as the plurality of pneumatic sensors included in the respiration monitoring module in number, the plurality of signal preprocessing modules are electrically connected with the plurality of pneumatic sensors in one-to-one correspondence, and meanwhile, the plurality of signal preprocessing modules are also electrically connected with the central control module respectively.

Step one: when a user inhales, the plurality of pneumatic sensors sense the pressure acted on the air flow generated by the inhalation of the user, the pressure acted on the air flow is converted into corresponding forward respiratory electric signals, the forward respiratory electric signals are output to the plurality of signal preprocessing modules which are electrically connected with the plurality of pneumatic sensors in a one-to-one correspondence mode, and the forward respiratory electric signals output by the plurality of pneumatic sensors are preprocessed by the plurality of signal preprocessing modules. When the central control module receives the plurality of forward respiratory electric signals, the central control module starts a timer arranged in the central control module to count according to a first forward respiratory electric signal received in the plurality of forward respiratory electric signals, meanwhile, the central control module respectively analyzes and calculates peak values of the plurality of forward respiratory electric signals, and adds the peak values of the plurality of forward respiratory electric signals to calculate an average value to obtain a final peak value of the forward respiratory electric signals, so that the inhalation amplitude of a user is calculated according to the peak value analysis of the obtained final forward respiratory electric signals. Among them, for convenience of description hereinafter, the above-described air flow sensor that outputs the first inhalation air flow pressure electric signal is referred to as an air flow sensor a.

Step two: when a user exhales, the plurality of pneumatic sensors sense the pressure acted on the air flow generated by the user exhales and convert the pressure acted on the air flow into corresponding negative respiratory electric signals to be output to a plurality of signal preprocessing modules which are electrically connected with the plurality of pneumatic sensors in a one-to-one correspondence mode, and the negative respiratory electric signals output by the plurality of pneumatic sensors are preprocessed by the plurality of signal preprocessing modules.

At this time, the central control module still stops the timer set in the central control module according to the negative respiration electric signal output by the pneumatic sensor A to count so as to obtain a first count time X1 (namely, the time interval of the first respiration of the user), and then clears the timer set in the central control module; meanwhile, a counter arranged in the central control module is started to count to obtain at least one respiration frequency C1=1, in addition, the central control module can respectively analyze and calculate peak values of the negative respiration electric signals, the peak values of the negative respiration electric signals are added to obtain an average value, and the peak value of the final negative respiration electric signal is obtained, so that the user exhalation amplitude is calculated according to the peak value analysis of the obtained final negative respiration electric signal.

It should be noted that, when the user inhales again, the procedure of the first step will be repeated, which will not be described here again; after the process is finished, when the user exhales again, the plurality of pneumatic sensors sense the pressure acted on the air flow generated by the user exhales and convert the pressure acted on the air flow into corresponding negative respiratory electric signals and output the negative respiratory electric signals to a plurality of signal preprocessing modules which are in one-to-one corresponding electric connection with the plurality of pneumatic sensors, and the plurality of signal preprocessing modules preprocess the negative respiratory electric signals output by the plurality of pneumatic sensors; the central control module still stops the timer arranged in the central control module to count according to the negative respiration electric signal output by the pneumatic sensor A, so as to obtain a second count time X2 (namely, the time interval of the second respiration of the user), and then clears the timer arranged in the central control module; meanwhile, the central control module starts a counter arranged in the central control module to count up, so that the respiration times C2=C1+1 of the user are obtained, the repeated circulation is performed, and the like, the time intervals X1 and X2 … … Xn of each respiration of the user and the total respiration times C=Cn=n of the user are finally obtained, and a plurality of breaths are calculated.

Step three: the central control module judges whether the positive respiration electric signal or the negative respiration electric signal which is preprocessed by the signal preprocessing module and corresponds to the pneumatic sensor A is received again in the second preset time interval, if the corresponding positive respiration electric signal or the negative respiration electric signal which is output by the pneumatic sensor A through the signal preprocessing module is not received in the second preset time interval, the danger that the user possibly has respiratory disorder or sudden stop is indicated, the central control module outputs an alarm control signal to the alarm module under the condition that the positive respiration electric signal or the negative respiration electric signal which is output by the signal preprocessing module is not received in the second preset time interval is judged, the alarm module carries out alarm prompt according to the alarm control signal so as to inform doctors, guardians and the like to take necessary measures, and meanwhile, the central control module also continuously waits for receiving the positive respiration electric signal or the negative respiration electric signal which is preprocessed by the signal preprocessing module, so that the process of the step one or the step two is repeated. The person skilled in the art may set the second preset time interval according to actual needs, which is not limited herein, and for example, the second preset time interval may be 1s.

In the embodiment of the invention, the situation that partial pneumatic sensors output invalid forward respiratory electrical signals may occur, at this time, the central control module may determine whether the forward respiratory electrical signals output by the pneumatic sensors are greater than or equal to a preset signal threshold, if so, the corresponding forward respiratory electrical signals are considered to be valid forward respiratory electrical signals, the central control module may respectively analyze and calculate peak values of the forward respiratory electrical signals, and sum and average the peak values of the forward respiratory electrical signals to obtain a final peak value of the forward respiratory electrical signals, so as to calculate the inhalation amplitude of the user according to the peak value analysis of the obtained final forward respiratory electrical signals. In addition, the central control module can also control and output alarm control signals, and the alarm module can carry out alarm prompt according to the alarm control signals so as to inform doctors and/or guardianship personnel that the pneumatic sensor has faults and needs to be maintained or replaced. Similar to the exhalation process, the description is omitted here.

Fig. 5 is a functional block diagram of a respiratory rate monitoring system using the respiratory rate monitoring device of fig. 4 according to the present invention. As shown in fig. 5, the respiratory rate monitoring system includes: respiratory rate monitoring device 510 and terminal device 520. Wherein, the respiratory rate monitoring device 510 is the respiratory rate monitoring device shown in fig. 4; the terminal device 520 is connected to the respiratory rate monitoring device 510 in a wireless communication manner, and is used for storing and displaying the respiratory rate obtained by analysis and calculation of the respiratory rate monitoring device 510, and/or sending a control instruction for controlling the respiratory rate monitoring device 510.

Specifically, as shown in fig. 5, the terminal device 520 is connected to the wireless transceiver module 124 in the respiratory rate monitoring apparatus 510 in a wireless communication manner, and is configured to receive the calculated respiratory rate from the central control module 122 sent by the wireless transceiver module 124, and/or send a control instruction for controlling the central control module 122 to the wireless transceiver module 124. Specifically, the control instructions may include: an on command for turning on the operation of the central control module 122 and a termination command for terminating the operation of the central control module 122. The terminal device 520 may be a mobile phone, a computer, or the like, and may perform the task of counting the breath of the user by designing a specific application program therein, and may be selected by those skilled in the art according to needs, which is not limited herein.

Fig. 6 is another functional block diagram of a respiratory rate monitoring system using the respiratory rate monitoring device of fig. 4 according to the present invention. As shown in fig. 6, the respiratory rate monitoring system shown in fig. 6 differs from the respiratory rate monitoring system shown in fig. 5 in that: the respiratory rate monitoring system shown in fig. 6 also includes a large database service platform 630. Wherein the terminal device 520 is further configured to: transmitting the received respiratory rate to the large database service platform 630; the large database service platform 630 is connected to the terminal device 520 in a wireless communication manner, and is configured to receive and store the respiratory rate transmitted by the terminal device 520, analyze and compare the received respiratory rate with the respiratory rate in the large database service platform 630, the user analysis information is obtained and sent to the terminal device 520 for viewing or reference by the doctor and/or guardian on the terminal device 520, so that the doctor and/or guardian can more deeply understand the breathing condition of the user.

In addition, the respiratory rate monitoring system provided by the invention may not include the terminal device 520, but only include the large database service platform 630, so that the respiratory rate of the user is analyzed and calculated by the central control module 122 in the respiratory rate monitoring device 510, then the respiratory rate is sent to the large database service platform 630 for analysis and comparison by the wireless transceiver module 124, so as to obtain user analysis information, and finally the user analysis information is sent to the central control module 122 by the wireless transceiver module 124, so that the central control module 122 controls the display module 126 to display the user analysis information for viewing or reference by doctors and/or guardians, and the doctors and/or guardians can know the respiratory condition of the user more deeply.

It should be understood that the respiratory rate monitoring system shown in fig. 5 and 6 may employ not only the respiratory rate monitoring device of the third embodiment, but also the respiratory rate monitoring device of the first or second embodiments, and those skilled in the art may select the respiratory rate monitoring device according to need, which is not limited herein.

In addition, in all the respiratory rate monitoring systems described above, the connection manner between the respiratory rate monitoring device 510 and the terminal device 520 or the large database service platform 630 may be not only connected by wireless communication, but also directly connected by wired communication, where when connected by wired communication, the corresponding wireless communication device may be omitted, for example: the wireless transceiver module 124 in the respiratory rate monitoring device 510.

Fig. 7 is a schematic structural diagram of a ventilator according to a first embodiment of the present invention. As shown in fig. 7, the ventilator includes: a respiratory rate monitoring device, a ventilator body 710, an airflow conduit 720, and a mask 730; wherein, the respiration monitoring module 110 is disposed in the airflow pipeline 720; a circuit processing module (not shown) is disposed in the ventilator body. In the embodiment of the invention, when the respiratory rate monitoring module adopts the pneumatic sensors from example one to example seven, the problem that the pneumatic sensors block the airflow pipeline to cause the airflow to flow through the airflow pipeline cannot be avoided as much as possible, and therefore, the defects can be overcome by reducing the volumes of the pneumatic sensors from example one to example seven.

Fig. 8 is a schematic structural diagram of a second embodiment of a ventilator according to the present invention. As shown in fig. 8, the ventilator includes: a respiratory rate monitoring device, a ventilator body 810, an airflow conduit 820, and a mask 830; wherein the respiratory monitoring module 110 is disposed in the mask 830; the ventilator body is connected to a circuit processing module (not shown) of the respiratory rate monitoring device through a preset port, for example, a central control module in the ventilator body may be connected to a central control in the respiratory rate monitoring device through the preset port. In the embodiment of the invention, when the respiratory rate monitoring module adopts the pneumatic sensors from example one to example seven, the problem that the pneumatic sensors block the airflow pipeline to cause the airflow to flow through the airflow pipeline cannot be avoided as much as possible, and therefore, the defects can be overcome by reducing the volumes of the pneumatic sensors from example one to example seven.

Fig. 9 is a schematic structural diagram of an oxygen inhaler according to a first embodiment of the present invention. As shown in fig. 9, the oxygen inhaler includes: respiratory rate monitoring device, oxygen inhaler body 910, gas flow conduit 920 and mask 930; wherein the respiration monitoring module 110 is disposed in the airflow conduit 920; the circuit processing module (drawing is not shown) is arranged in the oxygen inhaler main body. In the embodiment of the invention, when the respiratory rate monitoring module adopts the pneumatic sensors from example one to example seven, the problem that the pneumatic sensors block the airflow pipeline to cause the airflow to flow through the airflow pipeline cannot be avoided as much as possible, and therefore, the defects can be overcome by reducing the volumes of the pneumatic sensors from example one to example seven.

Fig. 10 is a schematic structural diagram of a second embodiment of the oxygen inhaler according to the present invention. As shown in fig. 10, the oxygen inhaler includes: a respiratory rate monitoring device, an oxygen inhaler body 1010, a gas flow conduit 1020, and a mask 1030; wherein the respiratory monitoring module 110 is disposed in the mask 1030; the oxygen inhaler body is connected to a circuit processing module (not shown) of the respiratory rate monitoring device through a preset port, for example, a central control module in the oxygen inhaler body may be connected to a central control in the respiratory rate monitoring device through the preset port. In the embodiment of the invention, when the respiratory rate monitoring module adopts the pneumatic sensors from example one to example seven, the problem that the pneumatic sensors block the airflow pipeline to cause the airflow to flow through the airflow pipeline cannot be avoided as much as possible, and therefore, the defects can be overcome by reducing the volumes of the pneumatic sensors from example one to example seven.

The present invention provides a ventilator, comprising: the respiratory rate monitoring system shown in fig. 5 or 6, a ventilator body, an airflow conduit, and a mask; wherein, the respiration monitoring module is arranged in the airflow pipeline and/or the mask;

the circuit processing module is arranged in the breathing machine main body; or, the ventilator body is connected with the circuit processing module of the respiratory rate monitoring device through a preset port, for example, the central control module in the ventilator body can be connected with the central control in the respiratory rate monitoring device through the preset port.

The invention provides an oxygen inhaler, which is characterized by comprising: the respiratory rate monitoring system shown in figure 5 or figure 6, an oxygen inhaler body, an air flow pipeline and a mask; wherein, the respiration monitoring module is arranged in the airflow pipeline and/or the mask;

the circuit processing module is arranged in the oxygen inhaler main body; or the oxygen inhaler body is connected with the circuit processing module of the respiratory rate monitoring device through a preset port, for example, the central control module in the oxygen inhaler body can be connected with the central control in the respiratory rate monitoring device through the preset port.

The various modules and circuits mentioned in the present invention are all hardware implemented circuits, for example, the central control module may include a microcontroller or a micro-control chip, the rectifying module may include a rectifying circuit, the filtering module may include a comparing circuit, the amplifying module may include an amplifying circuit, etc., and the analog-to-digital conversion module may include an analog-to-digital converter, etc. Although some of the modules and circuits are integrated with software, the present invention is intended to cover a hardware circuit integrated with the corresponding functions of the software, not just the software itself.

It should be appreciated by those skilled in the art that the device structures shown in the figures or embodiments are merely schematic and represent logical structures. Where the modules shown as separate components may or may not be physically separate, the components shown as modules may or may not be physical modules.

Finally, it should be noted that: the above description is only illustrative of the specific embodiments of the invention and it is of course possible for those skilled in the art to make modifications and variations to the invention, which are deemed to be within the scope of the invention as defined in the claims and their equivalents.

Claims

1. A respiratory rate monitoring device, comprising: a respiration monitoring module and a circuit processing module, the circuit processing module comprising: the system comprises a signal preprocessing module, a central control module and a power supply module; wherein,

the power supply module is provided with a power supply circuit, the central control module is electrically connected with the power supply module and is used for supplying electric energy;

wherein, the respiration monitoring module includes: at least one pneumatic sensor for converting the pressure of the air flow generated by inhalation or exhalation of the user acting on the at least one pneumatic sensor into a respiratory electric signal output;

wherein the at least one pneumatic sensor comprises: the first electrode ring, the annular friction assembly and the second electrode ring are sequentially stacked along the same central axis; wherein,

The first electrode ring, the annular friction assembly and the second electrode ring are arranged in a stacked manner to form a tubular structure for forming a fluid channel; inducing an electrical charge at the first electrode ring and the second electrode ring as fluid passes through the fluid channel; the first electrode ring and/or the second electrode ring is/are an electric signal output end of the pneumatic sensor; the first electrode ring and/or the annular friction assembly and/or the second electrode ring comprise a rebound ring having a rebound effect, wherein the rebound ring comprises: a fixed ring and a rebound net arranged on the fixed ring;

the at least one pneumatic the sensor further comprises: the electrode ring is sequentially arranged from inside to outside and used for coating the first electrode ring a shielding assembly and a packaging assembly of the annular friction assembly and the second electrode ring and exposing a fluid passage;

the at least one pneumatic sensor further comprises: at least one vibration assembly is disposed on an inner wall of the pneumatic sensor for enhancing vibration of the fluid acting on the pneumatic sensor.

2. The respiratory rate monitoring device of claim 1, wherein the circuit processing module further comprises: a wireless transceiver module and/or an interactive function module;

The wireless transceiver module is electrically connected with the central control module and is used for transmitting the respiratory frequency obtained by analysis and calculation of the central control module to preset receiving equipment in a wireless communication mode;

the interaction function module is electrically connected with the central control module and is used for sending a user interaction instruction to the central control module;

wherein the user interaction instruction comprises at least one of the following: an on command, an off command, and a user information initialization command.

3. The respiratory rate monitoring device of claim 1, wherein the circuit processing module further comprises: a display module and/or an alarm module;

the display module is electrically connected with the central control module and used for displaying the respiratory frequency obtained by analysis and calculation of the central control module;

the central control module is further configured to: judging whether the respiratory frequency obtained by analysis and calculation accords with a preset respiratory frequency range or not, and outputting an alarm control signal according to a judging result;

and the alarm module is electrically connected with the central control module and is used for carrying out alarm prompt according to an alarm control signal output by the central control module.

4. The respiratory rate monitoring device of claim 1, wherein the at least one pneumatic sensor is further configured to: converting the pressure of the air flow generated by inhalation of a user acting on the at least one pneumatic sensor into a positive respiratory electric signal to be output; converting the pressure of the air flow generated by the user breathing on the at least one pneumatic sensor into negative respiratory electric signal output;

the signal preprocessing module is further used for: preprocessing the positive respiratory electric signal or the negative respiratory electric signal output by the at least one pneumatic sensor;

a timer and a counter are arranged in the central control module;

the central control module is further configured to: when the forward respiratory electric signal preprocessed by the signal preprocessing module is received, starting the timer to count time; and stopping the timer when the negative respiration electric signal preprocessed by the signal preprocessing module is received, obtaining timing time, and starting the counter to count, thus obtaining the respiration times of the user.

5. The respiratory rate monitoring device of claim 4, wherein the central control module is further configured to: judging whether the positive respiratory electric signal or the negative respiratory electric signal output by the signal preprocessing module is received within a second preset time interval; if not, sending an alarm control signal to the alarm module.

6. The respiratory rate monitoring device of claim 1, wherein the at least one pneumatic sensor is a friction-generating pneumatic sensor and/or a piezoelectric-generating pneumatic sensor.

7. A respiratory rate monitoring system, comprising: the respiratory rate monitoring device of any one of claims 1-6, and a terminal device; wherein,

8. The respiratory rate monitoring system of claim 7, further comprising a large database service platform; wherein,

the terminal device is further configured to: transmitting the received respiratory rate to the large database service platform;

the large database service platform is connected with the terminal equipment in a wired communication or wireless communication mode and is used for receiving and storing the breathing frequency sent by the terminal equipment, analyzing and comparing the received breathing frequency with the breathing frequency in the large database service platform to obtain user analysis information, and sending the user analysis information to the terminal equipment.

9. A respiratory rate monitoring system, comprising: the respiratory rate monitoring device of any one of claims 1-6, a large database service platform; wherein,

10. A ventilator, comprising: a respiratory rate monitoring device according to any one of claims 1 to 6 or a respiratory rate monitoring system according to claim 7 or 8 or a respiratory rate monitoring system according to claim 9, and a ventilator body, an airflow conduit and a mask; wherein the respiratory monitoring module is arranged in the airflow pipeline and/or the mask;

the circuit processing module is arranged in the respirator main body; or, the main body of the respirator is connected with the circuit processing module of the respiratory rate monitoring device through a preset port.

11. An oxygen inhaler, comprising: the respiratory rate monitoring device of any one of claims 1-6 or the respiratory rate monitoring system of claim 7 or 8 or the respiratory rate monitoring system of claim 9, and an oxygen inhaler body, an air flow conduit, and a mask; wherein the respiratory monitoring module is arranged in the airflow pipeline and/or the mask;

the circuit processing module is arranged in the oxygen inhaler main body; or the oxygen inhaler main body is connected with the circuit processing module of the respiratory rate monitoring device through a preset port.