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WO2016138792A1 - 经鼻高流量氧疗压力监测系统及其监测方法 - Google Patents

经鼻高流量氧疗压力监测系统及其监测方法 Download PDF

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Publication number
WO2016138792A1
WO2016138792A1 PCT/CN2015/099837 CN2015099837W WO2016138792A1 WO 2016138792 A1 WO2016138792 A1 WO 2016138792A1 CN 2015099837 W CN2015099837 W CN 2015099837W WO 2016138792 A1 WO2016138792 A1 WO 2016138792A1
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WIPO (PCT)
Prior art keywords
pressure
control device
data
detection signal
resistor
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Ceased
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PCT/CN2015/099837
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English (en)
French (fr)
Inventor
邹栋
吴本清
黄裕钦
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Shenzhen Comen Medical Instruments Co Ltd
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Shenzhen Comen Medical Instruments Co Ltd
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Publication of WO2016138792A1 publication Critical patent/WO2016138792A1/zh
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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. ventilators; Tracheal tubes
    • A61M16/021—Devices for influencing the respiratory system of patients by gas treatment, e.g. ventilators; Tracheal tubes operated by electrical means
    • A61M16/022—Control means therefor
    • A61M16/024—Control means therefor including calculation means, e.g. using a processor

Definitions

  • the invention relates to the technical field of medical technology, in particular to a nasal high-flow oxygen therapy pressure monitoring system and a monitoring method thereof.
  • nasal high-flow oxygen therapy is a nasal ventilation mode developed in recent years, through the output of high-temperature, high-humidity air-oxygen mixing Gas to achieve respiratory therapy for the patient.
  • the nasal high-flow oxygen therapy device adopts a ⁇ -type nasal oxygen tube, and the ⁇ -type nasal oxygen tube is non-sealedly connected with the patient's nostril. After the gas enters the nostril, the gas leaks from the nasal plug of the nasal oxygen tube and the nasal cavity to realize the nose of the patient. Positive airway pressure is generated inside.
  • the nasal nasal cannula used in the traditional nasal high-flow oxygen therapy device is small and soft, and the pressure sampling port cannot be added at the nasal plug of the nasal itching tube. Therefore, the nasal airway pressure is generally not monitored by the nasal high-flow oxygen therapy device. The risk of clinical use is high.
  • a nasal high-flow oxygen therapy pressure monitoring system includes a pressure detecting device and a control device, wherein the pressure detecting device is connected to the control device,
  • the pressure detecting device is configured to detect airway pressure in a breathing circuit of the nasal high-flow oxygen therapy device, acquire a detection signal and send the signal to the control device; and the control device is configured to receive the first collection instruction Receiving a detection signal sent by the pressure detecting device to obtain a first detection signal, and receiving a detection signal sent by the pressure detecting device to obtain a second detection signal after receiving the second acquisition instruction; The first detection signal and the second detection signal are subjected to analog-to-digital conversion to obtain first detection data and second detection data, and the patient end airway pressure value is calculated and output according to the first detection data and the second detection data.
  • a method for monitoring a nasal high-flow oxygen therapy pressure monitoring system includes the following steps:
  • the pressure detecting device detects the airway pressure in the breathing circuit of the nasal high-flow oxygen therapy device, acquires the detection signal and sends it to the control device;
  • the control device After receiving the first acquisition instruction, the control device receives the detection signal sent by the pressure detection device to obtain a first detection signal;
  • control device After receiving the second acquisition instruction, the control device receives the detection signal sent by the pressure detection device to obtain a second detection signal;
  • the control device performs analog-to-digital conversion on the first detection signal and the second detection signal to obtain first detection data and second detection data;
  • the control device calculates and outputs a patient end airway pressure value according to the first detection data and the second detection data.
  • the pressure detecting device detects the airway pressure in the breathing pipeline of the nasal high-flow oxygen therapy device, acquires the detection signal and sends it to the control device.
  • the control device receives the detection signal sent by the pressure detection device to obtain the first detection signal
  • the control device performs analog-to-digital conversion on the first detection signal and the second detection signal to obtain first detection data and second detection data, and calculates a patient end airway pressure value according to the first detection data and the second detection data, and outputs the same.
  • the nasal oxygen tube accessory for nasal high-flow oxygen therapy equipment is small in size and soft and can not monitor the pressure of the patient end.
  • the airway pressure in the respiratory circuit is detected to measure the airway pressure at the patient end, and the nasal flow is high.
  • oxygen therapy provides a pressure monitoring reference for medical staff, which reduces the risk of clinical use.
  • FIG. 1 is a structural view of a nasal high-flow oxygen therapy pressure monitoring system in an embodiment
  • Figure 2 is a schematic diagram of a pressure detecting device in an embodiment
  • FIG. 3 is a structural view of a nasal high-flow oxygen therapy pressure monitoring system in another embodiment
  • Figure 4 is a structural view of a zeroing valve in an embodiment
  • Figure 5 is a schematic diagram of a zero control circuit in an embodiment
  • FIG. 6 is a flow chart of a monitoring method for a nasal high flow oxygen therapy pressure monitoring system in an embodiment.
  • a nasal high-flow oxygen therapy pressure monitoring system for monitoring patient airway pressure of a nasal high-flow oxygen therapy device.
  • the nasal high-flow oxygen therapy device delivers fresh air with a good oxygen concentration and flow through the breathing tube to the nasal oxygen tube for the patient to breathe.
  • the nasal high flow oxygen therapy pressure monitoring system includes a pressure detecting device 110 and a control device 120, and the pressure detecting device 110 is connected to the control device 120.
  • the pressure detecting device 110 is configured to detect the airway pressure in the breathing circuit of the nasal high-flow oxygen therapy device, acquire the detection signal, and send it to the control device 120.
  • the control device 120 is configured to: after receiving the first acquisition instruction, receive the detection signal sent by the pressure detection device 110 to obtain the first detection signal, and after receiving the second acquisition instruction, receive the detection signal sent by the pressure detection device 110 to obtain the first detection signal. a second detection signal; the control device 120 performs analog-to-digital conversion on the first detection signal and the second detection signal to obtain first detection data and second detection data, and calculates a patient end airway according to the first detection data and the second detection data.
  • the pressure value is output.
  • a pressure sampling port can be designed at the gas input port of the breathing circuit, and the pressure detecting device 110 is connected to the pressure sampling port to detect the gas output from the pressure sampling port, and the airway pressure in the breathing pipe is monitored in real time.
  • the pressure detecting device 110 can employ a high-precision differential pressure type pressure sensor with a measuring range of 1 PSI and an output signal of a differential signal.
  • a ventilation mode button may be provided on the display interface of the control device 120 to set the oxygen concentration and flow rate of the fresh gas input to the breathing circuit. After the breathing tube is connected to the nasal oxygen tube, the patient is not connected.
  • the medical staff can input the first collection instruction through the display interface of the control device 120, and the control device 120 receives the first collection instruction.
  • the detection signal sent by the pressure detecting device 110 is used as the first detection signal, and the first detection data is obtained by analog-to-digital conversion.
  • the measured pressure is the pressure generated by the resistance of the breathing tube and the nasal oxygen tube, as a basis. pressure.
  • the medical staff After the nasal oxygen tube is connected to the patient, the medical staff inputs a second acquisition command through the display interface of the control device 120, and after receiving the second acquisition command, the control device 120 uses the detection signal sent by the pressure detecting device 110 as the second detection signal, and performs The analog-to-digital conversion obtains the second detection data, and the measured pressure is the sum of the pressure generated by the resistance of the pipeline and the nasal oxygen tube and the airway pressure generated by the patient end, so that the airway pressure of the patient end can be calculated as the first The difference between the second detection data and the first detection data, thereby obtaining the patient's airway pressure value and outputting through the display interface, to achieve the patient end airway pressure monitoring.
  • the above-mentioned nasal high-flow oxygen therapy pressure monitoring system measures the patient's nasal pressure in the nasal high-flow oxygen therapy device, and the patient can measure the pressure of the patient's end by detecting the airway pressure in the respiratory circuit.
  • the end-to-airway pressure provides a pressure monitoring reference for medical personnel while transnasal high-flow oxygen therapy, which reduces the risk of clinical use.
  • the device structure is simple and easy to operate, low in cost, and does not require additional devices such as tubing to cause an increase in nasal damage to the newborn.
  • the pressure detecting device 110 includes a detecting circuit 112 including a first operational amplifier U1A, a first resistor R189 and a pressure detector U2, and an in-phase input of the first operational amplifier U1A.
  • Terminal + connected to the constant voltage source access terminal VDRI, inverting input terminal - connected to the pressure detector U2, specifically connected to the port -IN of the pressure detector U2, and grounded through the first resistor R189, the output of the first operational amplifier U1A is connected
  • the pressure detector U2 is specifically connected to the port +IN of the pressure detector U2.
  • the pressure detector U2 is connected to the control device 120, specifically to the control device 120 via port-OUT and port +OUT.
  • the first operational amplifier U1A uses the LMC6482AIM chip
  • the pressure detector U2 uses the NPC-1210 chip.
  • the pressure detecting device 110 adopts a constant current source driving mode, and the constant current source design is realized by using the first operational amplifier U1A and the first resistor R189, and the driving current of the pressure detector U2 can be set to 1 mA.
  • the pressure detector U2 is used to detect the airway pressure in the breathing circuit of the nasal high-flow oxygen therapy device, acquire a detection signal, and send it to the control device 120.
  • the detecting circuit 112 may further include a capacitor C162. One end of the capacitor C162 is connected to the output end of the first operational amplifier U1A, and the other end is grounded through the first resistor R189.
  • the pressure detecting device 110 may further include a signal amplifying circuit 114 connected to the pressure detector U2 and the control device 120 for performing the detection signal sent by the pressure detector U2. After amplification, it is transmitted to the control device 120.
  • the signal amplifying circuit 114 includes a meter operational amplifier U3, a second resistor R143, a third resistor R140, and a fourth resistor R193.
  • the non-inverting input terminal IN+ of the meter operational amplifier U3 is connected to the pressure detector U2 through a second resistor R143. Connect port +OUT of pressure detector U2.
  • the inverting input terminal IN of the meter operational amplifier U3 is connected to the pressure detector U2 through a third resistor R140, specifically connected to the port -OUT of the pressure detector U2.
  • the output terminal OUT of the meter operational amplifier U3 is connected to the control device 120 via a fourth resistor R193, and the feedback terminal REF of the meter operational amplifier U3 is connected to a constant voltage.
  • the signal amplifying circuit 114 may further include a resistor R144, a capacitor C163, a capacitor C166, a capacitor C164, and a capacitor C205.
  • One end of the resistor R144 is connected to the port RG+ of the meter operational amplifier U3, and the other end is connected to the port RG- of the instrument operational amplifier U3.
  • One end of the capacitor C163 is connected to the common terminal of the third resistor R140 and the meter operational amplifier U3, and the other end is grounded.
  • One end of the capacitor C166 is connected to the common terminal of the third resistor R140 and the meter operational amplifier U3, and the other end is connected to the common terminal of the second resistor R143 and the meter operational amplifier U3.
  • One end of the capacitor C164 is connected to the common terminal of the second resistor R143 and the meter operational amplifier U3, and the other end is grounded.
  • One end of the capacitor C205 is connected to the fourth resistor R193 away from the end of the instrument operational amplifier U3, and the other end of the capacitor C205 is grounded.
  • the instrument operational amplifier U3 adopts an AD623 chip, which has high input impedance, high common mode rejection ratio, low noise, low drift, good temperature stability, wide frequency band of amplification, and low noise figure, and the operational amplifier is amplified by 35 times.
  • the signal is amplified by the signal amplifying circuit 114 and transmitted to the control device 120, thereby improving data acquisition accuracy.
  • the pressure detecting device 110 may further include a signal filtering circuit 116.
  • the signal filtering circuit 116 is connected to the signal amplifying circuit 114 and the control device 120 for filtering the signal output by the signal amplifying circuit 114 and transmitting the signal to the control device 120.
  • the signal filtering circuit 116 may include a second operational amplifier U1B, a fifth resistor R190, a sixth resistor R191, and a seventh resistor R192.
  • the fifth resistor R190 and the sixth resistor R191 are connected in series, and the other end of the fifth resistor R190 is connected to the signal.
  • the amplifying circuit 124 is specifically connected to the fourth resistor R193.
  • the other end of the sixth resistor R191 is connected to the non-inverting input terminal of the second operational amplifier U1B, the inverting input terminal of the second operational amplifier U1B is connected to the output end of the second operational amplifier U1B, and the output end of the second operational amplifier U1B is passed through the seventh resistor.
  • R192 is connected to the control device 120, and specifically connected to the control device 120 via the port ADC_Pressure.
  • the signal filtering circuit 116 can also include a capacitor C176, a capacitor C178, and a capacitor C187.
  • One end of the capacitor C176 is connected to the common terminal of the sixth resistor R191 and the second operational amplifier U1B, and the other end is grounded.
  • One end of the capacitor C178 is connected to the common end of the fifth resistor R190 and the sixth resistor R191, and the other end is connected to the output end of the second operational amplifier U1B.
  • One end of the capacitor C187 is connected to one end of the seventh resistor R192 away from the second operational amplifier U1B, and the other end of the capacitor C187 is grounded.
  • the second operational amplifier U1B can adopt the TLC2272A CDR chip.
  • the signal output from the signal amplifying circuit 114 is filtered by the second-order active filter circuit and then transmitted to the control device 120, which can further improve the accuracy of data detection.
  • control device 120 is further configured to perform filtering processing on the first detection data and the second detection data to obtain first pressure data and second pressure data.
  • the control device 120 calculates and outputs the patient end airway pressure value based on the first pressure data and the second pressure data.
  • control device 120 filters the first detection data and the second detection data to obtain 50 Hz pressure data, and performs filtering processing on the first detection data and the second detection data to make the pressure data obtained after filtering more stable.
  • the precision is high, and the control device 120 calculates the airway pressure value of the patient end according to the pressure data obtained by the filtering, which can also improve the accuracy of data detection.
  • the nasal high flow oxygen therapy pressure monitoring system further includes a zero calibration device 130 that connects the pressure sensing device 110 and the control device 120 with gas input to the breathing circuit.
  • the port is connected.
  • the control device 120 periodically controls the zero calibration device 130 to calibrate the pressure detecting device 110, receives the calibration signal transmitted by the pressure detecting device 110, and calculates calibration data.
  • control device 120 is further configured to perform calibration processing on the first pressure data and the second pressure data according to the calibration data to obtain first correction data and second correction data; and the control device The patient end airway pressure value is calculated and output based on the first correction data and the second correction data.
  • the pressure detecting device 110 is also subjected to calibration processing and the calibration data is calculated.
  • the first pressure data and the second pressure data are calibrated according to the calibration data to obtain corresponding correction data, and then the patient end airway pressure value is calculated according to the correction data.
  • the first pressure data and the second pressure data are calibrated to correct the influence of temperature drift and zero drift of the pressure detecting device 110, thereby improving data monitoring accuracy.
  • the control device 120 can also display the calculated first correction data and second correction data through the display interface, so that the medical staff can view the record.
  • the zero calibration device 130 includes a zero calibration valve 132 and a zero calibration control circuit 134.
  • the zero valve 132 is used for zero signal calibration of the pressure detecting device 110.
  • the zero valve 132 is a three-way valve, which belongs to a 2-position 3-way valve, and the sensor is zero-calibrated through the three-way valve to solve the temperature drift. Repeatability and other problems lead to low pressure monitoring accuracy and large errors.
  • the zeroing valve 132 includes a sampling end 3, an atmospheric end 1 and an output end 2.
  • the sampling end 3 of the zeroing valve 132 is in communication with the gas input port of the breathing line, and the atmospheric end 1 of the zeroing valve 132 is used for access.
  • the ambient gas and the ambient gas specifically refer to the gas in the environment where the nasal high-flow oxygen therapy pressure monitoring system is located.
  • the atmospheric end 1 is connected to the atmosphere, and the pressure input is 0.
  • the output 2 of the zero valve 132 is connected to the pressure detecting device 110.
  • the pressure detecting device 110 works normally. When the airway pressure in the breathing pipe is detected, the sampling end 3 communicates with the output end 2. When the pressure detecting device 110 is zeroed, the sampling end 3 is closed, and the output end 2 is connected to the atmospheric end 1.
  • the pressure detecting device 110 generates a corresponding calibration signal according to the accessed ambient gas and sends it to the control device 120. After the control device 120 calculates the calibration data according to the calibration signal, the calibration data can also be filtered to improve the data accuracy.
  • the control device 120 may send a zero calibration command every half hour, one hour or two hours, and the zero calibration command may be a high level or a low level.
  • the zero control circuit 134 is connected to the zeroing valve 132 and the control device 120.
  • the control device 120 is also configured to periodically send a zero calibration command to the zero control circuit 134.
  • the zero calibration control circuit 134 controls the zero calibration valve when the zero calibration command is not received.
  • the sampling end 3 of the 132 is in communication with the output terminal 2, and controls the atmospheric end 1 of the zeroing valve 132 to communicate with the output terminal 2 upon receipt of the zeroing command.
  • the zeroing control circuit 134 includes a switching transistor Q17, an eighth resistor R1, and a ninth resistor R2.
  • the input end of the switch tube Q17 is connected to the zeroing valve 132 through the pin 2 of the connection port SOLVALVE, and the power supply terminal POWER is connected to the zeroing valve 132 through the pin 1 of the connection port SOLVALVE.
  • the control end of the switch tube Q17 is connected to the output end of the switch tube Q17 through the ninth resistor R2, and is connected to the control device 120 through the eighth resistor R1, specifically connected to the control device 120 via the port CTRL_VALVE; the output end of the switch tube Q17 is grounded.
  • the switch tube Q17 may be a triode or a MOS tube.
  • the switch tube Q17 is an N-channel MOS tube of the IRLML2502TRPBF type.
  • the switching transistor Q17 is turned on when its control terminal is at a high level, and is turned off when its control terminal is at a low level.
  • the zeroing valve 132 changes the specific communication state according to the on/off state of the switching tube Q17. Taking the zero command as the high level as an example, the switch Q17 is turned on when the control terminal receives the zero command, and the atmospheric end 1 of the zero check valve 132 communicates with the output terminal 2 to perform calibration processing on the pressure detecting device 110. .
  • the switch tube Q17 is turned off when the control terminal thereof does not receive the zero calibration command, and the sampling end 3 of the zero calibration valve 132 is in communication with the output terminal 2, so that the pressure detecting device 110 detects the airway pressure in the breathing circuit.
  • the zero control circuit 134 may further include a diode D1, a capacitor C1, a capacitor C2, a resistor R3, a resistor R4, and a resistor R5.
  • the cathode of diode D1 is connected to pin 1 of the connection port SOLVALVE, and the anode is connected to pin 2 of the connection port SOLVALVE.
  • One end of the capacitor C1 is connected to the pin 1 of the connection port SOLVALVE, and the other end is connected to the pin 2 of the connection port SOLVALVE.
  • the resistor R3 and the resistor R4 are connected in series and the common terminal is connected to the control device 120 through the resistor R5, and is connected to the control device 120 via the port TEST_VALVE.
  • the other end of the resistor R3 is connected to the pin 2 of the connection port SOLVALVE, and the other end of the resistor R4 is grounded.
  • One end of the capacitor C2 is connected to the common end of the resistor R5 and the control device 120, and the other end is grounded.
  • the state of the zeroing valve 132 is detected by the resistor R3 and the resistor R4, and a sampling signal is generated and transmitted to the control device 120.
  • the control device 120 can also determine whether the zeroing valve 132 is abnormal according to the sampling signal. For example, when the zeroing control circuit 134 controls the sampling end 3 of the zeroing valve 132 to communicate with the output terminal 2, if the sampling end 3 and the output end are judged according to the sampling signal, If the 2 is not connected or is not fully connected, it is determined that the zeroing valve 132 is abnormal.
  • the control device 120 can output reminder information to inform the guardian to perform maintenance in time, avoid the impact of hardware failure on data detection, and improve the reliability of the nasal high-flow oxygen therapy pressure monitoring system.
  • a nasal high-flow oxygen therapy pressure monitoring system for monitoring patient airway pressure of a nasal high-flow oxygen therapy device.
  • the nasal high-flow oxygen therapy device delivers fresh air with a good oxygen concentration and flow through the breathing tube to the nasal oxygen tube for the patient to breathe.
  • the nasal high flow oxygen therapy pressure monitoring system includes a pressure detecting device and a control device, and the pressure detecting device is connected to the control device.
  • the pressure detecting device is configured to detect airway pressure in the breathing circuit of the nasal high-flow oxygen therapy device when the patient is not connected to the patient and access to the patient, respectively, and obtain the first detection signal and access when the patient is not connected to the patient a second detection signal at the time of the patient is sent to the control device; the control device is configured to perform analog-to-digital conversion on the first detection signal and the second detection signal to obtain the first detection data and the second detection data, respectively, according to the first detection data and The second detection data calculates the patient's airway pressure value and outputs it.
  • the above-mentioned nasal high-flow oxygen therapy pressure monitoring system measures the patient's nasal pressure in the nasal high-flow oxygen therapy device, and the patient can measure the pressure of the patient's end by detecting the airway pressure in the respiratory circuit.
  • the end-to-airway pressure provides a pressure monitoring reference for medical personnel while transnasal high-flow oxygen therapy, which reduces the risk of clinical use.
  • the device structure is simple and easy to operate, low in cost, and does not require additional devices such as tubing to cause an increase in nasal damage to the newborn.
  • the transnasal high flow oxygen therapy pressure monitoring system further includes a zeroing device coupled to the pressure sensing device and the control device and in communication with the gas input port of the breathing circuit.
  • the control device timing control zero calibration device calibrates the pressure detecting device, receives the calibration signal sent by the pressure detecting device, and calculates calibration data.
  • the specific manner of calibrating the pressure detecting device and the corresponding hardware structure are explained in detail in the above, and will not be described herein.
  • the first pressure data and the second pressure data are calibrated to correct the effects of temperature drift and zero drift of the pressure detecting device, thereby improving data monitoring accuracy.
  • the control device may further display the calculated first correction data and the second correction data through the display interface, so that the medical staff can view the record.
  • the invention also provides a monitoring method for a nasal high-flow oxygen therapy pressure monitoring system, which is implemented based on the above-mentioned nasal high-flow oxygen therapy pressure monitoring system for monitoring the airway pressure of the patient end of the nasal high-flow oxygen therapy device.
  • the nasal high-flow oxygen therapy device delivers fresh air with a good oxygen concentration and flow through the breathing tube to the nasal oxygen tube for the patient to breathe.
  • the monitoring method of the nasal high-flow oxygen therapy pressure monitoring system includes the following steps:
  • Step S110 The pressure detecting device detects the airway pressure in the breathing circuit of the nasal high-flow oxygen therapy device, acquires the detection signal, and sends the detection signal to the control device.
  • a pressure sampling port can be designed at the gas inlet of the breathing circuit, the pressure detecting device is connected to the pressure sampling port, the gas output from the pressure sampling port is detected, and the airway pressure in the breathing pipe is monitored in real time.
  • the pressure detecting device can adopt a high-precision differential pressure type pressure sensor with a measuring range of 1 PSI and an output signal of a differential signal.
  • Step S120 After receiving the first acquisition instruction, the control device receives the detection signal sent by the pressure detecting device to obtain the first detection signal.
  • a ventilation mode button can be provided on the display interface of the control device to set the oxygen concentration and flow rate of the fresh gas input to the breathing circuit. After the breathing tube is connected with the nasal oxygen tube, the patient is not connected. When the flow output of the gas reaches the set value, the medical staff can input the first collection instruction through the display interface of the control device, and the control device will receive the first collection instruction. The detection signal transmitted by the pressure detecting device is used as the first detection signal.
  • Step S130 After receiving the second acquisition instruction, the control device receives the detection signal sent by the pressure detection device to obtain a second detection signal.
  • the medical staff After the nasal oxygen tube is connected to the patient, the medical staff inputs a second acquisition instruction through the display interface of the control device, and the control device receives the second acquisition instruction and uses the detection signal sent by the pressure detection device as the second detection signal.
  • Step S140 The control device performs analog-to-digital conversion on the first detection signal and the second detection signal to obtain first detection data and second detection data.
  • the control device performs analog-to-digital conversion on the first detection signal to obtain first detection data
  • the measured pressure is the pressure generated by the resistance of the breathing tube and the nasal oxygen tube as the base pressure.
  • the control device performs analog-to-digital conversion on the second detection signal to obtain second detection data.
  • the measured pressure is the sum of the pressure generated by the resistance of the pipeline and the nasal oxygen tube and the airway pressure generated by the patient end.
  • Step S150 The control device calculates and outputs the patient end airway pressure value according to the first detection data and the second detection data.
  • the airway pressure of the patient end can be calculated as the difference between the second detection data and the first detection data, thereby obtaining the patient end airway pressure value and outputting through the display interface.
  • the above-mentioned monitoring method for the nasal high-flow oxygen therapy pressure monitoring system is directed to the problem that the nasal oxygen tube accessory of the nasal high-flow oxygen therapy device is small in size and soft and cannot monitor the pressure of the patient end, and the airway pressure in the breathing tube is detected.
  • the airway pressure at the patient's end is measured, and the pressure monitoring reference for the medical staff is provided at the same time as the nasal high-flow oxygen therapy, which reduces the risk of clinical use.
  • step S150 specifically includes step 152 and step 154.
  • Step 152 The control device performs filtering processing on the first detection data and the second detection data to obtain first pressure data and second pressure data.
  • Step 154 The control device calculates and outputs the patient end airway pressure value according to the first pressure data and the second pressure data.
  • the first detection data and the second detection data are respectively filtered to obtain pressure data of 50 Hz, and the pressure data obtained by filtering is more stable and high precision by filtering the first detection data and the second detection data.
  • the control device calculates the airway pressure value of the patient end according to the pressure data obtained after the filtering, thereby improving the accuracy of data detection.
  • the monitoring method of the nasal high-flow oxygen therapy pressure monitoring system further comprises: the control device timing control zero-calibration device calibrates the pressure detecting device, receives the calibration signal sent by the pressure detecting device, and calculates the calibration data. A step of.
  • Step 154 includes step 1542 and step 1544.
  • Step 1542 The control device performs calibration processing on the first pressure data and the second pressure data according to the calibration data to obtain first correction data and second correction data.
  • Step 1544 The control device calculates and outputs the patient end airway pressure value according to the first correction data and the second correction data.
  • the pressure detecting device is also subjected to calibration processing and the calibration data is calculated.
  • the specific calibration method is explained in detail in the above-mentioned nasal high-flow oxygen therapy pressure monitoring system, and will not be described herein.
  • the first pressure data and the second pressure data are calibrated according to the calibration data to obtain corresponding correction data, and then the patient end airway pressure value is calculated according to the correction data.
  • the first pressure data and the second pressure data are calibrated to correct the effects of temperature drift and zero drift of the pressure detecting device, thereby improving data monitoring accuracy.
  • the step of displaying the calculated first correction data and the second correction data through the display interface may be further included by the control device, so that the medical staff can view the record.

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  • Measurement Of The Respiration, Hearing Ability, Form, And Blood Characteristics Of Living Organisms (AREA)

Abstract

一种经鼻高流量氧疗压力监测系统及其监测方法，压力检测装置(110)对经鼻高流量氧疗设备的呼吸管路内的气道压力进行检测，获取检测信号并发送至控制装置(120)(S110)。控制装置(120)在接收到第一采集指令后接收压力检测装置(110)发送的检测信号得到第一检测信号(S120)，在接收到第二采集指令后接收压力检测装置(110)发送的检测信号得到第二检测信号(S130)。控制装置(120)分别对第一检测信号和第二检测信号进行模数转换得到第一检测数据和第二检测数据(S140)，并根据第一检测数据和第二检测数据计算得到病人端气道压力值并输出(S150)。通过对呼吸管路内的气道压力进行检测进而测得病人端气道压力，为医护人员提供压力监测参考，降低临床使用风险。

Description

经鼻高流量氧疗压力监测系统及其监测方法
【技术领域】
本发明涉及医疗技术领域，特别是涉及一种经鼻高流量氧疗压力监测系统及其监测方法。
【背景技术】
目前NICU（Neonatal intensive care center，新生儿重症监护中心）呼吸治疗趋势越来越向经鼻无创通气方向发展，而经鼻高流量氧疗是最近几年发展起来的经鼻通气模式，通过输出高温、高湿的空氧混合器气体，来实现对病人的呼吸治疗。经鼻高流量氧疗设备通气模式采用π型鼻氧管，π型鼻氧管与病人鼻孔非密封性连接，气体进入鼻孔内后从鼻氧管的鼻塞与鼻腔的缝隙漏气从而实现在病人鼻子内产生气道正压。
传统的经鼻高流量氧疗设备使用的鼻氧管附件体积小且柔软，不能在鼻痒管的鼻塞处添加压力采样端口，因此经鼻高流量氧疗设备普遍没有对病人端气道压力进行监测，临床使用风险大。
【发明内容】
基于此，有必要针对上述问题，提供一种可降低经鼻高流量氧疗设备临床使用风险的经鼻高流量氧疗压力监测系统及其监测方法。
一种经鼻高流量氧疗压力监测系统，包括压力检测装置和控制装置，所述压力检测装置连接所述控制装置，
所述压力检测装置用于对经鼻高流量氧疗设备的呼吸管路内的气道压力进行检测，获取检测信号并发送至所述控制装置；所述控制装置用于在接收到第一采集指令后，接收所述压力检测装置发送的检测信号得到第一检测信号，以及在接收到第二采集指令后，接收所述压力检测装置发送的检测信号得到第二检测信号；所述控制装置分别对所述第一检测信号和第二检测信号进行模数转换得到第一检测数据和第二检测数据，并根据所述第一检测数据和第二检测数据计算得到病人端气道压力值并输出。
一种经鼻高流量氧疗压力监测系统的监测方法，包括以下步骤：
压力检测装置对经鼻高流量氧疗设备的呼吸管路内的气道压力进行检测，获取检测信号并发送至控制装置；
所述控制装置在接收到第一采集指令后，接收所述压力检测装置发送的检测信号得到第一检测信号；
所述控制装置在接收到第二采集指令后，接收所述压力检测装置发送的检测信号得到第二检测信号；
所述控制装置分别对所述第一检测信号和第二检测信号进行模数转换得到第一检测数据和第二检测数据；
所述控制装置根据所述第一检测数据和第二检测数据计算得到病人端气道压力值并输出。
上述经鼻高流量氧疗压力监测系统及其监测方法，压力检测装置对经鼻高流量氧疗设备的呼吸管路内的气道压力进行检测，获取检测信号并发送至控制装置。控制装置在接收到第一采集指令后，接收压力检测装置发送的检测信号得到第一检测信号，以及在接收到第二采集指令后，接收压力检测装置发送的检测信号得到第二检测信号。控制装置分别对第一检测信号和第二检测信号进行模数转换得到第一检测数据和第二检测数据，并根据第一检测数据和第二检测数据计算得到病人端气道压力值并输出。针对经鼻高流量氧疗设备的鼻氧管附件体积小且柔软不能监测病人端压力的问题，通过对呼吸管路内的气道压力进行检测进而测得病人端气道压力，实现在经鼻高流量氧疗的同时为医护人员提供压力监测参考，降低了临床使用风险。
【附图说明】
图1为一实施例中经鼻高流量氧疗压力监测系统的结构图；
图2为一实施例中压力检测装置的原理图；
图3为另一实施例中经鼻高流量氧疗压力监测系统的结构图；
图4为一实施例中校零阀的结构图；
图5为一实施例中校零控制电路的原理图；
图6为一实施例中经鼻高流量氧疗压力监测系统的监测方法的流程图。
【具体实施方式】
为使本发明的上述目的、特征和优点能够更加明显易懂，下面结合附图对本发明的具体实施方式做详细的说明。在下面的描述中阐述了很多具体细节以便于充分理解本发明。但是本发明能够以很多不同于在此描述的其它方式来实施，本领域技术人员可以在不违背本发明内涵的情况下做类似改进，因此本发明不受下面公开的具体实施例的限制。
除非另有定义，本文所使用的所有的技术和科学术语与属于本发明的技术领域的技术人员通常理解的含义相同。本文中在本发明的说明书中所使用的术语只是为了描述具体的实施例的目的，不是旨在于限制本发明。
一种经鼻高流量氧疗压力监测系统，用于对经鼻高流量氧疗设备的病人端气道压力进行监控。经鼻高流量氧疗设备将配置好氧浓度和流量的新鲜空气经呼吸管道传输至鼻氧管，供病人呼吸。如图1所示，经鼻高流量氧疗压力监测系统包括压力检测装置110和控制装置120，压力检测装置110连接控制装置120。
压力检测装置110用于对经鼻高流量氧疗设备的呼吸管路内的气道压力进行检测，获取检测信号并发送至控制装置120。控制装置120用于在接收到第一采集指令后，接收压力检测装置110发送的检测信号得到第一检测信号，以及在接收到第二采集指令后，接收压力检测装置110发送的检测信号得到第二检测信号；控制装置120分别对第一检测信号和第二检测信号进行模数转换得到第一检测数据和第二检测数据，并根据第一检测数据和第二检测数据计算得到病人端气道压力值并输出。
具体地，可在呼吸管路的气体输入口处设计压力采样端口，将压力检测装置110与压力采样端口连接，对压力采样端口输出的气体进行检测，实时监测呼吸管路内的气道压力。压力检测装置110可采用高精度差压式压力传感器，测量范围为1PSI，输出信号为差分信号。可在控制装置120的显示界面设置通气模式按钮，对输入呼吸管路的新鲜气体的氧浓度和流量进行设置。在呼吸管路与鼻氧管连接后不连接病人，当气体的流量输出达到设定值后，医护人员可通过控制装置120的显示界面输入第一采集指令，控制装置120接收到第一采集指令后将压力检测装置110发送的检测信号作为第一检测信号，并进行模数转换得到第一检测数据，此时测得的压力为呼吸管路和鼻氧管的阻力所产生的压力，作为基础压力。将鼻氧管连接病人后，医护人员通过控制装置120的显示界面输入第二采集指令，控制装置120接收到第二采集指令后将压力检测装置110发送的检测信号作为第二检测信号，并进行模数转换得到第二检测数据，此时测得的压力为管路和鼻氧管的阻力所产生的压力与病人端产生的气道压力之和，因此可以计算出病人端的气道压力为第二检测数据与第一检测数据之差，从而得到病人端气道压力值并通过显示界面输出，实现病人端气道压力监测。
上述经鼻高流量氧疗压力监测系统，针对经鼻高流量氧疗设备的鼻氧管附件体积小且柔软不能监测病人端压力的问题，通过对呼吸管路内的气道压力进行检测进而测得病人端气道压力，实现在经鼻高流量氧疗的同时为医护人员提供压力监测参考，降低了临床使用风险。装置结构简单易操作、成本低，且不需要增加额外的管路等装置而导致对新生儿鼻腔损伤加大。
在其中一个实施例中，如图2所示，压力检测装置110包括检测电路112，检测电路112包括第一运算放大器U1A、第一电阻R189和压力检测器U2，第一运算放大器U1A的同相输入端+连接恒压源接入端VDRI，反相输入端-连接压力检测器U2，具体连接压力检测器U2的端口-IN，并通过第一电阻R189接地，第一运算放大器U1A的输出端连接压力检测器U2，具体连接压力检测器U2的端口+IN。压力检测器U2连接控制装置120，具体可通过端口-OUT和端口+OUT与控制装置120连接。本实施例中第一运算放大器U1A采用LMC6482AIM芯片，压力检测器U2采用NPC-1210芯片。
本实施例中压力检测装置110采用恒流源驱动方式，利用第一运算放大器U1A和第一电阻R189实现恒流源设计，对压力检测器U2的驱动电流可设置为1mA。压力检测器U2用于对经鼻高流量氧疗设备的呼吸管路内的气道压力进行检测，获取检测信号并发送至控制装置120。此外，检测电路112还可包括电容C162，电容C162一端连接第一运算放大器U1A的输出端，另一端通过第一电阻R189接地。
在其中一个实施例中，继续参照图2，压力检测装置110还可包括信号放大电路114，信号放大电路114连接压力检测器U2和控制装置120，用于对压力检测器U2发送的检测信号进行放大后传输至控制装置120。
具体地，信号放大电路114包括仪表运算放大器U3、第二电阻R143、第三电阻R140和第四电阻R193，仪表运算放大器U3的同相输入端IN+通过第二电阻R143与压力检测器U2连接，具体连接压力检测器U2的端口+OUT。仪表运算放大器U3的反相输入端IN-通过第三电阻R140与压力检测器U2连接，具体连接压力检测器U2的端口-OUT。仪表运算放大器U3的输出端OUT通过第四电阻R193连接控制装置120，仪表运算放大器U3的反馈端REF接入恒定电压。
信号放大电路114还可包括电阻R144，电容C163、电容C166、电容C164和电容C205。电阻R144一端连接仪表运算放大器U3的端口RG+，另一端连接仪表运算放大器U3的端口RG-。电容C163一端连接第三电阻R140和仪表运算放大器U3的公共端，另一端接地。电容C166一端连接第三电阻R140和仪表运算放大器U3的公共端，另一端连接第二电阻R143和仪表运算放大器U3的公共端。电容C164一端连接第二电阻R143和仪表运算放大器U3的公共端，另一端接地。电容C205一端连接第四电阻R193远离仪表运算放大器U3的一端，电容C205另一端接地。
本实施例中仪表运算放大器U3采用AD623芯片，具有高输入阻抗、高共模抑制比、低噪声、低漂移、温度稳定性好、放大频带宽、噪声系数小的特点，运算放大器放大35倍。通过信号放大电路114对检测信号进行放大后传输至控制装置120，可提高数据采集准确度。
进一步地，压力检测装置110还可包括信号过滤电路116，信号过滤电路116连接信号放大电路114和控制装置120，用于对信号放大电路114输出的信号进行滤波处理后传输至控制装置120。
具体地，信号过滤电路116可包括第二运算放大器U1B、第五电阻R190、第六电阻R191和第七电阻R192，第五电阻R190和第六电阻R191串联，第五电阻R190的另一端连接信号放大电路124，具体连接第四电阻R193。第六电阻R191的另一端连接第二运算放大器U1B的同相输入端，第二运算放大器U1B的反相输入端连接第二运算放大器U1B的输出端，第二运算放大器U1B的输出端通过第七电阻R192与控制装置120连接，具体可经端口ADC_Pressure与控制装置120连接。
信号过滤电路116还可包括电容C176、电容C178和电容C187。电容C176一端连接第六电阻R191与第二运算放大器U1B的公共端，另一端接地。电容C178一端连接第五电阻R190和第六电阻R191的公共端，另一端连接第二运算放大器U1B的输出端。电容C187一端连接第七电阻R192远离第二运算放大器U1B的一端，电容C187另一端接地。
第二运算放大器U1B可采用TLC2272ACDR芯片，本实施例中利用二阶有源滤波电路对信号放大电路114输出的信号进行滤波处理后传输至控制装置120，可进一步提高数据检测的准确度。
在其中一个实施例中，控制装置120计算得到第一检测数据和第二检测数据后，还用于对第一检测数据和第二检测数据进行滤波处理，得到第一压力数据和第二压力数据；控制装置120根据第一压力数据和第二压力数据计算得到病人端气道压力值并输出。
本实施例中控制装置120分别对第一检测数据和第二检测数据进行滤波得到50Hz的压力数据，通过对第一检测数据和第二检测数据进行滤波处理使滤波后得到的压力数据更稳定、精度高，控制装置120根据滤波后得到的压力数据计算病人端气道压力值，同样可提高数据检测准确度。
在其中一个实施例中，如图3所示，经鼻高流量氧疗压力监测系统还包括校零装置130，校零装置130连接压力检测装置110和控制装置120，并与呼吸管路的气体输入端口连通。控制装置120定时控制校零装置130对压力检测装置110进行校准，接收压力检测装置110发送的校准信号并计算得到校准数据。
控制装置120计算得到第一压力数据和第二压力数据后，还用于根据校准数据分别对第一压力数据和第二压力数据进行校准处理，得到第一校正数据和第二校正数据；控制装置120根据第一校正数据和第二校正数据计算得到病人端气道压力值并输出。
本实施例中即是还定时对压力检测装置110进行校准处理并计算得到校准数据。根据校准数据对第一压力数据和第二压力数据进行校准处理得到对应的校正数据，然后根据校正数据计算病人端气道压力值。对第一压力数据和第二压力数据进行校准，修正压力检测装置110温度漂移及零点漂移带来的影响，可提高数据监测精确度。进一步地，控制装置120还可将计算得到的第一校正数据和第二校正数据通过显示界面显示，以便医护人员查看记录。
在其中一个实施例中，如图4和图5所示，校零装置130包括校零阀132和校零控制电路134。
校零阀132用于对压力检测装置110进行零点信号校准，本实施例中校零阀132采用三通阀，属于2位3通型阀门，通过三通阀对传感器校零，能解决温漂、重复性等导致压力监测精度低、误差大的问题。
具体地，校零阀132包括采样端3、大气端1和输出端2，校零阀132的采样端3与呼吸管路的气体输入端口连通，校零阀132的大气端1用于接入环境气体，环境气体具体指经鼻高流量氧疗压力监测系统所处环境的气体，本实施例中大气端1接入大气，压力输入为0。校零阀132的输出端2连接压力检测装置110。
压力检测装置110正常工作，对呼吸管道内的气道压力进行检测时，采样端3与输出端2连通，对压力检测装置110校零时，采样端3关闭，输出端2与大气端1连通，压力检测装置110根据接入的环境气体生成对应的校准信号发送至控制装置120。控制装置120根据校准信号计算得到校准数据后，同样也可对校准数据进行滤波处理，提高数据准确性。控制装置120可以是每半小时、一小时或两小时发送一次校零指令，校零指令可以是高电平也可以是低电平。
校零控制电路134连接校零阀132和控制装置120，控制装置120还用于定时发送校零指令至校零控制电路134；校零控制电路134在未接收到校零指令时控制校零阀132的采样端3与输出端2连通，在接收到校零指令时控制校零阀132的大气端1与输出端2连通。
在其中一个实施例中，校零控制电路134包括开关管Q17、第八电阻R1和第九电阻R2。开关管Q17的输入端通过连接端口SOLVALVE的管脚2与校零阀132连接，电源接入端POWER通过连接端口SOLVALVE的管脚1连接校零阀132。开关管Q17的控制端通过第九电阻R2连接开关管Q17的输出端，并通过第八电阻R1连接控制装置120，具体经端口CTRL_VALVE与控制装置120连接；开关管Q17的输出端接地。开关管Q17具体可以是三极管或MOS管，本实施例中开关管Q17为IRLML2502TRPBF型号的N沟道MOS管。
开关管Q17在其控制端为高电平时导通，在其控制端为低电平时关断。校零阀132根据开关管Q17的通断状态改变具体的连通状态。以校零指令为高电平为例，开关管Q17在其控制端接收到校零指令时导通，校零阀132的大气端1与输出端2连通，以便对压力检测装置110进行校准处理。开关管Q17在其控制端未接收到校零指令时关断，校零阀132的采样端3与输出端2连通，以便压力检测装置110对呼吸管路内的气道压力进行检测。
此外，校零控制电路134还可包括二极管D1、电容C1、电容C2、电阻R3、电阻R4和电阻R5。二极管D1的阴极与连接端口SOLVALVE的管脚1连接，阳极与连接端口SOLVALVE的管脚2连接。电容C1一端与连接端口SOLVALVE的管脚1连接，另一端与连接端口SOLVALVE的管脚2连接。电阻R3和电阻R4串联且公共端通过电阻R5连接控制装置120，具体经端口TEST_VALVE与控制装置120连接。电阻R3的另一端与连接端口SOLVALVE的管脚2连接，电阻R4的另一端接地。电容C2一端连接电阻R5与控制装置120的公共端，另一端接地。
通过电阻R3和电阻R4对校零阀132的状态进行检测生成采样信号发送至控制装置120。控制装置120还可根据采样信号判断校零阀132是否出现异常，如当校零控制电路134控制校零阀132的采样端3与输出端2连通时，若根据采样信号判断采样端3与输出端2未连通或未完全连通，则判定校零阀132出现异常。控制装置120可输出提醒信息以告知监护人员及时进行检修，避免硬件故障对数据检测造成影响，提高经鼻高流量氧疗压力监测系统的可靠性。
一种经鼻高流量氧疗压力监测系统，用于对经鼻高流量氧疗设备的病人端气道压力进行监控。经鼻高流量氧疗设备将配置好氧浓度和流量的新鲜空气经呼吸管道传输至鼻氧管，供病人呼吸。经鼻高流量氧疗压力监测系统包括压力检测装置和控制装置，压力检测装置连接控制装置。
压力检测装置用于分别在不接入病人和接入病人时对经鼻高流量氧疗设备的呼吸管路内的气道压力进行检测，分别获取不接入病人时的第一检测信号和接入病人时的第二检测信号并发送至控制装置；控制装置用于分别对第一检测信号和第二检测信号进行模数转换得到第一检测数据和第二检测数据，并根据第一检测数据和第二检测数据计算得到病人端气道压力值并输出。
压力检测装置进行压力检测以及控制装置进行数据处理的具体方式及对应的硬件结构在前文中已进行了详细的解释说明，在此不再赘述。
上述经鼻高流量氧疗压力监测系统，针对经鼻高流量氧疗设备的鼻氧管附件体积小且柔软不能监测病人端压力的问题，通过对呼吸管路内的气道压力进行检测进而测得病人端气道压力，实现在经鼻高流量氧疗的同时为医护人员提供压力监测参考，降低了临床使用风险。装置结构简单易操作、成本低，且不需要增加额外的管路等装置而导致对新生儿鼻腔损伤加大。
在其中一个实施例中，经鼻高流量氧疗压力监测系统还包括校零装置，校零装置连接压力检测装置和控制装置，并与呼吸管路的气体输入端口连通。控制装置定时控制校零装置对压力检测装置进行校准，接收压力检测装置发送的校准信号并计算得到校准数据。
校零装置对压力检测装置进行校零的具体方式及对应的硬件结构在上文中进行了详细的解释说明，在此不再赘述。对第一压力数据和第二压力数据进行校准，修正压力检测装置温度漂移及零点漂移带来的影响，可提高数据监测精确度。进一步地，控制装置还可将计算得到的第一校正数据和第二校正数据通过显示界面显示，以便医护人员查看记录。
本发明还提供了一种经鼻高流量氧疗压力监测系统的监测方法，基于上述经鼻高流量氧疗压力监测系统实现，用于对经鼻高流量氧疗设备的病人端气道压力进行监控。经鼻高流量氧疗设备将配置好氧浓度和流量的新鲜空气经呼吸管道传输至鼻氧管，供病人呼吸。如图6所示，经鼻高流量氧疗压力监测系统的监测方法包括以下步骤：
步骤S110：压力检测装置对经鼻高流量氧疗设备的呼吸管路内的气道压力进行检测，获取检测信号并发送至控制装置。
具体地，可在呼吸管路的气体输入口处设计压力采样端口，将压力检测装置与压力采样端口连接，对压力采样端口输出的气体进行检测，实时监测呼吸管路内的气道压力。压力检测装置可采用高精度差压式压力传感器，测量范围为1PSI，输出信号为差分信号。
步骤S120：控制装置在接收到第一采集指令后，接收压力检测装置发送的检测信号得到第一检测信号。
可在控制装置的显示界面设置通气模式按钮，对输入呼吸管路的新鲜气体的氧浓度和流量进行设置。在呼吸管路与鼻氧管连接后不连接病人，当气体的流量输出达到设定值后，医护人员可通过控制装置的显示界面输入第一采集指令，控制装置接收到第一采集指令后将压力检测装置发送的检测信号作为第一检测信号。
步骤S130：控制装置在接收到第二采集指令后，接收压力检测装置发送的检测信号得到第二检测信号。
将鼻氧管连接病人后，医护人员通过控制装置的显示界面输入第二采集指令，控制装置接收到第二采集指令后将压力检测装置发送的检测信号作为第二检测信号。
步骤S140：控制装置分别对第一检测信号和第二检测信号进行模数转换得到第一检测数据和第二检测数据。
控制装置分对第一检测信号进行模数转换得到第一检测数据，此时测得的压力为呼吸管路和鼻氧管的阻力所产生的压力，作为基础压力。控制装置对第二检测信号进行模数转换得到第二检测数据，此时测得的压力为管路和鼻氧管的阻力所产生的压力与病人端产生的气道压力之和。
步骤S150：控制装置根据第一检测数据和第二检测数据计算得到病人端气道压力值并输出。
根据步骤S140中得到的第一检测数据和第二检测数据，可以计算出病人端的气道压力为第二检测数据与第一检测数据之差，从而得到病人端气道压力值并通过显示界面输出，实现病人端气道压力监测。
以上步骤的具体实施方式在上述经鼻高流量氧疗压力监测系统中进行了详细的解释说明，在此不再赘述。
上述经鼻高流量氧疗压力监测系统的监测方法，针对经鼻高流量氧疗设备的鼻氧管附件体积小且柔软不能监测病人端压力的问题，通过对呼吸管路内的气道压力进行检测进而测得病人端气道压力，实现在经鼻高流量氧疗的同时为医护人员提供压力监测参考，降低了临床使用风险。
在其中一个实施例中，步骤S150具体包括步骤152和步骤154。
步骤152：控制装置对第一检测数据和第二检测数据进行滤波处理，得到第一压力数据和第二压力数据。
步骤154：控制装置根据第一压力数据和第二压力数据计算得到病人端气道压力值并输出。
本实施例中分别对第一检测数据和第二检测数据进行滤波，得到50Hz的压力数据，通过对第一检测数据和第二检测数据进行滤波处理使滤波后得到的压力数据更稳定、精度高，控制装置根据滤波后得到的压力数据计算病人端气道压力值，可提高数据检测准确度。
进一步地，在其中一个实施例中，经鼻高流量氧疗压力监测系统的监测方法还包括控制装置定时控制校零装置对压力检测装置进行校准，接收压力检测装置发送的校准信号并计算得到校准数据的步骤。
步骤154包括步骤1542和步骤1544。
步骤1542：控制装置根据校准数据分别对第一压力数据和第二压力数据进行校准处理，得到第一校正数据和第二校正数据。
步骤1544：控制装置根据第一校正数据和第二校正数据计算得到病人端气道压力值并输出。
本实施例中即是还定时对压力检测装置进行校准处理并计算得到校准数据。具体校准方式在上述经鼻高流量氧疗压力监测系统中进行了详细的解释说明，在此不再赘述。
根据校准数据对第一压力数据和第二压力数据进行校准处理得到对应的校正数据，然后根据校正数据计算病人端气道压力值。对第一压力数据和第二压力数据进行校准，修正压力检测装置温度漂移及零点漂移带来的影响，可提高数据监测精确度。进一步地，步骤1542之后，还可包括控制装置将计算得到的第一校正数据和第二校正数据通过显示界面显示的步骤，以便医护人员查看记录。
以上所述实施例仅表达了本发明的几种实施方式，其描述较为具体和详细，但并不能因此而理解为对本发明专利范围的限制。应当指出的是，对于本领域的普通技术人员来说，在不脱离本发明构思的前提下，还可以做出若干变形和改进，这些都属于本发明的保护范围。因此，本发明专利的保护范围应以所附权利要求为准。

Claims (10)

  1. 一种经鼻高流量氧疗压力监测系统，其特征在于，包括压力检测装置和控制装置，所述压力检测装置连接所述控制装置，
    所述压力检测装置用于对经鼻高流量氧疗设备的呼吸管路内的气道压力进行检测，获取检测信号并发送至所述控制装置；所述控制装置用于在接收到第一采集指令后，接收所述压力检测装置发送的检测信号得到第一检测信号，以及在接收到第二采集指令后，接收所述压力检测装置发送的检测信号得到第二检测信号；所述控制装置分别对所述第一检测信号和第二检测信号进行模数转换得到第一检测数据和第二检测数据，并根据所述第一检测数据和第二检测数据计算得到病人端气道压力值并输出。
  2. 根据权利要求1所述的经鼻高流量氧疗压力监测系统，其特征在于，所述压力检测装置包括检测电路，所述检测电路包括第一运算放大器、第一电阻和压力检测器，所述第一运算放大器的同相输入端连接恒压源接入端，反相输入端连接所述压力检测器，并通过所述第一电阻接地，所述第一运算放大器的输出端连接所述压力检测器，所述压力检测器连接所述控制装置；所述压力检测器用于对经鼻高流量氧疗设备的呼吸管路内的气道压力进行检测，获取检测信号并发送至所述控制装置。
  3. 根据权利要求2所述的经鼻高流量氧疗压力监测系统，其特征在于，所述压力检测装置还包括信号放大电路，所述信号放大电路连接所述压力检测器和控制装置，用于对所述压力检测器发送的检测信号进行放大后传输至所述控制装置。
  4. 根据权利要求3所述的经鼻高流量氧疗压力监测系统，其特征在于，所述信号放大电路包括仪表运算放大器、第二电阻、第三电阻和第四电阻，所述仪表运算放大器的同相输入端通过所述第二电阻与所述压力检测器连接，所述仪表运算放大器的反相输入端通过所述第三电阻与所述压力检测器连接，所述仪表运算放大器的输出端通过所述第四电阻连接所述控制装置，所述仪表运算放大器的反馈端接入恒定电压。
  5. 根据权利要求3所述的经鼻高流量氧疗压力监测系统，其特征在于，所述压力检测装置还包括信号过滤电路，所述信号过滤电路包括第二运算放大器、第五电阻、第六电阻和第七电阻，所述第五电阻和第六电阻串联，所述第五电阻的另一端连接所述信号放大电路，所述第六电阻的另一端连接所述第二运算放大器的同相输入端，所述第二运算放大器的反相输入端连接所述第二运算放大器的输出端，所述第二运算放大器的输出端通过所述第七电阻与所述控制装置连接。
  6. 根据权利要求1所述的经鼻高流量氧疗压力监测系统，其特征在于，所述控制装置计算得到所述第一检测数据和第二检测数据后，还用于对所述第一检测数据和第二检测数据进行滤波处理，得到第一压力数据和第二压力数据；所述控制装置根据所述第一压力数据和第二压力数据计算得到病人端气道压力值并输出。
  7. 根据权利要求6所述的经鼻高流量氧疗压力监测系统，其特征在于，还包括校零装置，所述校零装置连接所述压力检测装置和控制装置，并与所述呼吸管路的气体输入端口连通；所述控制装置定时控制所述校零装置对所述压力检测装置进行校准，接收所述压力检测装置发送的校准信号并计算得到校准数据；
    所述控制装置计算得到所述第一压力数据和第二压力数据后，还用于根据所述校准数据分别对所述第一压力数据和第二压力数据进行校准处理，得到第一校正数据和第二校正数据；所述控制装置根据第一校正数据和第二校正数据计算得到病人端气道压力值并输出。
  8. 根据权利要求7所述的经鼻高流量氧疗压力监测系统，其特征在于，所述校零装置包括校零阀和校零控制电路，
    所述校零阀包括采样端、大气端和输出端，所述校零阀的采样端与所述呼吸管路的气体输入端口连通，所述校零阀的大气端用于接入环境气体，所述校零阀的输出端连接所述压力检测装置；
    所述校零控制电路连接所述校零阀和控制装置，所述控制装置还用于定时发送校零指令至所述校零控制电路；所述校零控制电路在未接收到所述校零指令时控制所述校零阀的采样端与输出端连通，在接收到所述校零指令时控制所述校零阀的大气端与输出端连通。
  9. 一种经鼻高流量氧疗压力监测系统的监测方法，其特征在于，包括以下步骤：
    压力检测装置对经鼻高流量氧疗设备的呼吸管路内的气道压力进行检测，获取检测信号并发送至控制装置；
    所述控制装置在接收到第一采集指令后，接收所述压力检测装置发送的检测信号得到第一检测信号；
    所述控制装置在接收到第二采集指令后，接收所述压力检测装置发送的检测信号得到第二检测信号；
    所述控制装置分别对所述第一检测信号和第二检测信号进行模数转换得到第一检测数据和第二检测数据；
    所述控制装置根据所述第一检测数据和第二检测数据计算得到病人端气道压力值并输出。
  10. 一种经鼻高流量氧疗压力监测系统，其特征在于，包括压力检测装置和控制装置，所述压力检测装置连接所述控制装置，
    所述压力检测装置用于分别在不接入病人和接入病人时对经鼻高流量氧疗设备的呼吸管路内的气道压力进行检测，分别获取不接入病人时的第一检测信号和接入病人时的第二检测信号并发送至所述控制装置；所述控制装置用于分别对所述第一检测信号和第二检测信号进行模数转换得到第一检测数据和第二检测数据，并根据所述第一检测数据和第二检测数据计算得到病人端气道压力值并输出。
PCT/CN2015/099837 2015-03-02 2015-12-30 经鼻高流量氧疗压力监测系统及其监测方法 Ceased WO2016138792A1 (zh)

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