CN114028677A

CN114028677A - Breathing machine air pressure adjusting and monitoring system and application thereof

Info

Publication number: CN114028677A
Application number: CN202111453260.0A
Authority: CN
Inventors: 肖奇军; 石荣; 舒畅; 李小明
Original assignee: Guangdong Genial Technology Co ltd
Current assignee: Guangdong Genial Technology Co ltd
Priority date: 2021-12-01
Filing date: 2021-12-01
Publication date: 2022-02-11
Anticipated expiration: 2041-12-01
Also published as: CN114028677B

Abstract

The invention provides a breathing machine air pressure adjusting and monitoring system and application thereof, comprising: the data acquisition end is used for acquiring real-time pressure in the trachea of the respirator and real-time pressure difference between two ends of a throttling element of the respirator and acquiring corresponding real-time flow; the data analysis end is used for obtaining corresponding breathing phase judgment results, abnormal recognition results and breathing analysis results based on the real-time pressure and the real-time flow; the air pressure adjusting end is used for adjusting the output air pressure of the breathing machine in real time based on the abnormity identification result and the breath analysis result; the transmission alarm end is used for transmitting the abnormal recognition result, the breath analysis result and the adjusted output air pressure to the user end and carrying out corresponding alarm reminding; the intelligent breathing machine is used for improving the deviation and the adjustment delay of output pressure, and realizing the functions of reminding, displaying data, monitoring the breathing machine automatically and monitoring the breathing data of a patient based on data integration, thereby improving the intelligence of the breathing machine.

Description

Breathing machine air pressure adjusting and monitoring system and application thereof

Technical Field

The invention relates to the technical field of adjustment and monitoring, in particular to a breathing machine air pressure adjustment and monitoring system and application thereof.

Background

At present, respiratory diseases are modern common and frequent diseases, which cause serious influence on the health of people and even cause death of people. The Obstructive sleep Apnea-Hypopnea Syndrome (OSAHS) refers to excessive daytime sleep caused by no obvious reasons in the daytime, increased fatigue, reduced attention, listlessness, repeated awakening during nighttime sleep with rough or severe wheezing, and the occurrence of 5 or more Obstructive breathing events or other series of sleep disturbance events in each hour of sleep as shown by overnight polysomnography results. In modern clinical medicine, a ventilator has been widely used in respiratory failure due to various reasons, anesthesia and breathing management during major surgery, respiratory support therapy and emergency resuscitation as an effective means for manually replacing the function of spontaneous ventilation, and has a very important position in the modern medical field. The breathing machine is a vital medical device which can prevent and treat respiratory failure, reduce complications and save and prolong the life of a patient.

The respirator is easy to generate deviation between output pressure and set pressure due to external interference during working, so that delay is caused to the adjustment of the output pressure of the respirator, the parameter integration display function is not available, the dependence on the theoretical experience of a clinician is too high, the breathing condition of a patient cannot be monitored, the autonomous monitoring of the respirator cannot be realized, family members cannot be reminded when the respirator or the patient breathes abnormally, and the first-aid time is delayed.

Therefore, the invention provides a breathing machine air pressure adjusting and monitoring system and application thereof.

Disclosure of Invention

The invention provides a breathing machine air pressure regulation monitoring system and application thereof, which are used for improving the deviation and regulation delay of the output pressure of the traditional breathing machine, avoiding the condition deterioration of a patient caused by the fact that emergency measures are not taken timely when the breathing machine breaks down or the breathing of the patient is abnormal, and reminding by arranging a transmission alarm end.

The invention provides a breathing machine air pressure adjusting and monitoring system, which comprises:

the data acquisition end is used for acquiring real-time pressure in the trachea of the breathing machine, acquiring real-time pressure difference at two ends of a throttling element of the breathing machine, and acquiring corresponding real-time flow based on the real-time pressure and the real-time pressure difference;

the data analysis end is used for obtaining a corresponding breathing phase judgment result based on the real-time pressure and the real-time flow, and obtaining an abnormal recognition result and a breathing analysis result;

the air pressure adjusting end is used for adjusting the output air pressure of the breathing machine in real time based on the abnormity identification result and the breath analysis result;

and the transmission alarm end is used for transmitting the abnormal recognition result, the breath analysis result and the adjusted output air pressure to the user end and carrying out corresponding alarm reminding.

Preferably, the ventilator includes: a fan, a throttling element, a differential pressure sensor, a heating humidifier, a mask and an air pipe.

Preferably, the data acquisition end includes:

the acquisition module is used for acquiring real-time pressure in the trachea based on the pressure sensor and acquiring real-time pressure difference at two ends of the throttling element based on the pressure difference sensor;

and the calculation module is used for calculating the real-time flow in the trachea based on the real-time pressure difference.

Preferably, the data analysis terminal includes:

an obtaining module, configured to obtain a current working mode from a main control end of the ventilator, where the current working mode includes: a continuous single-level output mode, an automatic continuous single-level output mode, and a double-level output mode;

a first retrieving module, configured to retrieve corresponding inspiratory phase threshold and expiratory phase threshold based on the current working mode when the current working mode is the continuous single-level output mode or the automatic continuous single-level output mode, where the inspiratory phase threshold includes: an inspiratory phase pressure threshold and an inspiratory phase flow threshold, the expiratory phase threshold comprising: an expiratory phase pressure threshold and an expiratory phase flow threshold;

the first judgment module is used for judging an expiratory phase and an inspiratory phase in a preset period as breathing phase judgment results based on the inspiratory phase threshold and the expiratory phase threshold when the current working mode is the continuous single-level output mode or the automatic continuous single-level output mode;

the second judgment module is used for judging an expiratory phase and an inspiratory phase in a preset period as breathing phase judgment results based on a pressure curve corresponding to real-time pressure and a flow curve corresponding to real-time flow in the preset period when the current working mode is the double-level output mode;

the abnormality identification module is used for judging whether the breathing machine breaks down or not as a first abnormality identification result and judging whether the patient has apnea or not as a second abnormality identification result on the basis of the real-time pressure, the real-time flow and the breathing phase judgment result;

and the breath analysis module is used for obtaining a breath analysis result based on the real-time pressure, the real-time flow and the breath phase judgment result.

Wherein the abnormality recognition result includes: the first abnormality recognition result and the second abnormality recognition result.

Preferably, the air pressure adjusting terminal includes:

the dividing module is used for dividing the pressure curve into a plurality of first sub-line segments based on the breathing phase judgment result, dividing the flow curve into a plurality of second sub-line segments simultaneously, and corresponding the first sub-line segments to the second sub-line segments one by one;

the second calling module is used for calling the pressure threshold and the flow threshold of the corresponding sub-line segment based on the current working mode;

a deviation calculating module, configured to calculate an average pressure corresponding to the first sub-line segment, calculate an average flow corresponding to the second sub-line segment, calculate a first deviation value between the average pressure and the pressure threshold, calculate a second deviation value between the average flow and the flow threshold, obtain a corresponding third deviation value based on the second deviation value and a functional relationship between the flow and the pressure difference, calculate a first rotation speed adjustment value based on the first deviation value and a functional relationship between the first calculation weight and the pressure and the rotation speed, calculate a second rotation speed adjustment value based on the third deviation value and a functional relationship between the second calculation weight and the pressure and the rotation speed, and calculate a rotation speed adjustment value based on the first rotation speed adjustment value and the second rotation speed adjustment value;

and the control module is used for controlling the fan to adjust the rotating speed based on the rotating speed adjusting value.

Preferably, the second determining module includes:

the first fitting unit is used for fitting the real-time pressure in a preset period to obtain a corresponding pressure curve when the current working mode is the double-level output mode, and fitting a corresponding duty ratio waveform according to the real-time pressure in the preset period based on pulse width modulation;

the second fitting unit is used for fitting a corresponding flow curve and a corresponding flow change rate waveform based on real-time flow in a preset period when the current working mode is the double-level output mode;

the alignment unit is used for aligning the pressure curve, the duty ratio waveform, the flow curve and the flow change rate waveform to obtain an alignment curve graph;

a screening unit for screening out the alignment graph so as to satisfy: and (3) taking the time periods of real-time pressure reduction, duty ratio increase, real-time flow increase and flow change rate larger than zero as an inspiratory phase, and simultaneously screening out the time periods which simultaneously satisfy the following conditions from the alignment curve chart: and taking the time periods of real-time pressure rise, duty ratio reduction, real-time flow reduction and flow change rate less than zero as an expiratory phase.

Preferably, the abnormality recognition module includes:

a first judging unit, configured to judge whether an abnormal time period other than the inspiratory phase and the expiratory phase exists in a preset period, if so, judge whether a flow rate waveform segment corresponding to the abnormal time period is constantly zero and a corresponding pressure curve segment is a constant function,

if so, determining that the patient has apnea as the second abnormal recognition result, and taking the corresponding breathing phase as an apnea time period,

otherwise, whether the flow change rate waveform section corresponding to the abnormal time section is constantly zero and the corresponding real-time pressure is constantly less than the maximum real-time pressure corresponding to the previous adjacent breath,

if so, determining that the air leakage fault of the breathing machine occurs as the first abnormal recognition result, and taking the corresponding abnormal time period as the air leakage fault time period,

otherwise, judging that the data acquisition fault of the breathing machine occurs as the first abnormal identification result, and taking the corresponding abnormal time period as the data acquisition fault time period;

the first judging unit is further used for judging whether the duration time of each breathing phase exceeds an apnea judging threshold, if so, the patient is judged to have apnea as the second abnormal recognition result, and the corresponding breathing phase is taken as an apnea time period;

and the second judging unit is used for taking the failure of the breathing machine as the first abnormal identification result and taking the failure of the breathing data as the second abnormal identification result when the abnormal time period does not exist in a preset period and the duration of each breathing phase does not exceed an apnea judging threshold.

Preferably, the breath analysis module includes:

the first calculation unit is used for obtaining a corresponding flow function based on the flow curve corresponding to each breath and calculating the tidal volume corresponding to each breath based on the duration corresponding to each breath and the flow function;

the second calculation unit is used for counting the total number of respiratory processes in a preset period and calculating the real-time respiratory frequency based on the total number of the respiratory processes;

the third calculation unit is used for calculating the real-time breathing ratio based on the corresponding time length of the exhalation phase and the corresponding time length of the inhalation phase in the last breathing process;

a fourth calculation unit for calculating a corresponding minute ventilation based on the tidal volume and the real-time respiratory rate;

and the output unit is used for taking the tidal volume, the real-time respiratory rate, the real-time respiratory ratio and the minute ventilation as a respiratory analysis result.

Preferably, the transmission alarm terminal includes:

the transmission display module is used for transmitting and displaying the abnormal recognition result, the breath analysis result and the adjusted output air pressure to the user side;

the first alarm module is used for sending a corresponding first alarm instruction based on the apnea time period when the second abnormal recognition result is that the patient has apnea, and otherwise, keeping the current working state;

the second alarm module is used for sending a corresponding second alarm instruction based on the air leakage fault time period when the first abnormal recognition result indicates that the air leakage fault occurs in the breathing machine, sending a corresponding third alarm instruction based on the data acquisition fault time period when the first abnormal recognition result indicates that the data acquisition fault occurs in the breathing machine, and otherwise, keeping the current working state;

a third alarm module for analyzing the breath analysis result to obtain a tidal volume, a real-time respiratory rate, a real-time respiratory ratio and a minute ventilation volume, and judging whether the tidal volume, the real-time respiratory rate, the real-time respiratory ratio and the minute ventilation volume meet the requirements,

if not, sending a corresponding fourth alarm instruction to the user side,

otherwise, the current working state is kept.

Preferably, an application method of the system for monitoring and adjusting the pressure of a ventilator based on the above method includes:

step 1: the method comprises the steps of collecting real-time pressure in an air pipe of a breathing machine, collecting real-time pressure difference at two ends of a throttling piece of the breathing machine, and obtaining corresponding real-time flow based on the real-time pressure and the real-time pressure difference;

step 2: based on the real-time pressure and the real-time flow, obtaining a corresponding breathing phase judgment result, and obtaining an abnormal recognition result and a breathing analysis result;

and step 3: adjusting the output air pressure of a breathing machine based on the abnormity identification result and the breathing analysis result;

and 4, step 4: and transmitting the abnormal recognition result, the breath analysis result and the adjusted output air pressure to a user side, and carrying out corresponding alarm reminding.

Additional features and advantages of the invention will be set forth in the description which follows, and in part will be obvious from the description, or may be learned by practice of the invention. The objectives and other advantages of the invention will be realized and attained by the structure particularly pointed out in the written description and claims hereof as well as the appended drawings.

The technical solution of the present invention is further described in detail by the accompanying drawings and embodiments.

Drawings

The accompanying drawings, which are included to provide a further understanding of the invention and are incorporated in and constitute a part of this specification, illustrate embodiments of the invention and together with the description serve to explain the principles of the invention and not to limit the invention. In the drawings:

FIG. 1 is a schematic diagram of a system for regulating and monitoring the pressure of a ventilator according to an embodiment of the present invention;

FIG. 2 is a schematic structural diagram of a ventilator according to an embodiment of the present invention;

FIG. 3 is a schematic diagram of a data collection end according to an embodiment of the present invention;

FIG. 4 is a schematic diagram of a data analysis end according to an embodiment of the present invention;

FIG. 5 is a schematic view of an air pressure adjusting terminal according to an embodiment of the present invention;

FIG. 6 is a diagram illustrating a second determining module according to an embodiment of the present invention;

FIG. 7 is a schematic view of a pressure curve according to an embodiment of the present invention;

FIG. 8 is a schematic diagram of a duty cycle waveform in an embodiment of the present invention;

FIG. 9 is a schematic diagram of a flow curve, a flow rate curve and a respiratory phase determination according to an embodiment of the present invention;

FIG. 10 is a schematic diagram of pressure and flow changes in a continuous single level output mode and an automatic continuous single level output mode in accordance with an embodiment of the present invention;

FIG. 11 is a schematic diagram illustrating a variation of bi-level pressure flow according to an embodiment of the present invention;

FIG. 12 is a schematic diagram of an anomaly identification module according to an embodiment of the present invention;

FIG. 13 is a schematic diagram of a breath analysis module according to an embodiment of the present invention;

FIG. 14 is a schematic diagram of a transmission alarm terminal according to an embodiment of the present invention;

fig. 15 is a schematic diagram of a ventilator system according to an embodiment of the present invention.

Detailed Description

The preferred embodiments of the present invention will be described in conjunction with the accompanying drawings, and it will be understood that they are described herein for the purpose of illustration and explanation and not limitation.

Example 1:

the invention provides a ventilator air pressure regulation monitoring system, referring to fig. 1 and 2, comprising:

In the embodiment, the breathing data is recorded and stored in text form by the respirator through the SD card and the data monitoring terminal.

In this embodiment, the ventilator air pressure adjusting and monitoring system of the present invention is mainly applied to home use.

In this embodiment, the breathing phase determination result is: and judging the time period corresponding to the expiration process and the time period corresponding to the inspiration process in the preset period.

In this embodiment, the anomaly identification result includes: and identifying whether the air leakage fault of the breathing machine occurs or not and whether the patient has apnea or not based on the real-time pressure, the real-time flow and the breathing phase judgment result.

In this embodiment, the respiration analysis result is the respiration data related to the patient obtained based on the real-time pressure, the real-time flow and the respiration phase determination result, and examples thereof include: tidal volume, real-time respiratory rate, real-time tidal ratio, minute flow.

In the embodiment, the user side is a mobile phone side or a PC side of a caregiver or a family member, communication between the breathing machine and the upper computer is achieved through serial port communication, or network communication between the upper computer and the breathing machine is achieved through network communication, the external network can be connected through the Ethernet drive chip, the breathing waveform of the patient is uploaded to the corresponding website, and meanwhile, a doctor can log in the website at any time to know the condition of the patient in time, so that information management is facilitated.

In this embodiment, the output air pressure is the actual output air pressure of the ventilator for assisting the patient to breathe.

The beneficial effects of the above technology are: real-time flow is obtained through real-time pressure in the trachea and real-time pressure difference at two ends of the throttling element which are obtained through collection, the respiratory data are recorded, the respiratory data are helpful for patients and medical workers to know respiratory conditions and treatment effects in time, autonomous monitoring of the respiratory conditions of the patients and autonomous monitoring of the breathing machine can be realized based on the obtained data, deviation and adjustment delay of output pressure of the traditional breathing machine are improved, the situation of the patients is prevented from deteriorating due to the fact that emergency measures are not taken timely when the breathing machine breaks down or the breathing of the patients is abnormal, meanwhile, the obtained data are further calculated, integrated and transmitted to a user side, the respiratory data of the patients are displayed for nursing staff or family members intuitively and simply, the dependence of doctors is reduced, and the intellectualization of a monitoring system of the breathing machine is improved.

Example 2:

on the basis of embodiment 1, the ventilator, with reference to fig. 2, includes: a fan, a throttling element, a differential pressure sensor, a heating humidifier, a mask and an air pipe.

The beneficial effects of the above technology are: the pressure sensor is arranged in the trachea of the respirator and the pressure difference sensors are arranged at the two ends of the throttling element, so that real-time pressure and real-time pressure difference are acquired, a data base is provided for further acquiring real-time flow, and a data base is also provided for the autonomous monitoring of the follow-up respirator, the monitoring of the breathing data of a patient, the detection alarm function and the data display function.

Example 3:

on the basis of the embodiment 2, the data acquisition end, referring to fig. 3, includes:

In this embodiment, calculating the real-time flow rate in the trachea based on the real-time pressure difference includes:

wherein Q is the real-time flow and Δ P is the trueTime pressure difference, C₁Coefficient of relation between real-time flow and real-time differential pressure, C₂Adjustment constants for real-time flow and real-time differential pressure, C₁、C₂Is obtained by fitting according to a delta P-Q experimental curve of a breathing machine;

for example, Δ P is 100, C₁Is 0.1, C₂Is 1, then Q is 2.

The beneficial effects of the above technology are: the real-time flow in the respirator is calculated through the acquired real-time pressure difference, and the acquired real-time pressure is added, so that a data base is provided for the autonomous monitoring of the follow-up respirator, the monitoring of the breathing data of the patient, the detection alarm function and the data display function.

Example 4:

on the basis of the embodiment 3, the data analysis end, referring to fig. 4, includes:

In this embodiment, the current operating mode is the current operating mode of the ventilator and is controlled by an operating mode adjusting knob provided on the ventilator.

In this embodiment, a continuous single level output mode (CPAP) is used, i.e. the pressure in the airway is kept higher than atmospheric pressure during the whole breathing cycle (inspiratory phase and expiratory phase) under spontaneous breathing conditions, and the switching between inspiration and expiration is realized by triggering. The CPAP mode can only be used for patients with normal respiratory center function and spontaneous respiration, the pressure support level and the trigger sensitivity can be set by doctors, when the spontaneous respiration pressure reaches the trigger sensitivity, one-time synchronous ventilation is given according to the set pressure level, the airway pressure reaches the set level and is kept unchanged, when the flow reaches 15% of peak flow, the inspiration phase is finished, the expiration phase is started, and the airway pressure is the set level value during expiration through PI control.

In this embodiment, the automatic continuous single level output mode (APAP) is that the pressure changes with the degree of obstruction of the airway of the patient, i.e. when the degree of obstruction is small, the pressure is small, and when the degree of obstruction is serious, the ventilator will automatically increase the pressure to ensure that the airway is unobstructed. Thus, APAP mode may be preferable to CPAP mode in terms of comfort. But the actual therapeutic effect is not very different in case of no problem in pressure setting.

In this embodiment, the bi-level output mode (BIPAP) is to provide two different positive pressures for the inspiratory phase and the expiratory phase, respectively, and accelerate the increase of the rotational speed of the blower during inspiration, so that the output pressure of the ventilator is rapidly increased from the expiratory pressure (EPAP) to the inspiratory pressure (IPAP); during expiration, the rotating speed of the fan is reduced in an accelerating mode, so that the output pressure of the respirator is rapidly reduced from IPAP to EPAP. Thus, by adjusting the fan speed up, the ventilator output pressure can be quickly increased from the EPAP to the IPAP or quickly decreased from the IPAP to the EPAP within a preset time. The preset time can be set within 0.1S-2S according to the user requirements, so that the user can breathe more smoothly, and the use comfort of the user is improved.

In this embodiment, the inspiratory phase threshold is: an inspiratory phase pressure threshold (LTP) and an inspiratory phase flow threshold (HTF).

In this embodiment, the expiratory phase threshold is: an expiratory phase pressure threshold (HTP) and an expiratory phase flow threshold (HTP).

In this embodiment, the inspiratory phase pressure threshold (LTP) is the maximum pressure value corresponding to inspiration.

In this embodiment, the inspiratory phase flow threshold (HTF) is the minimum flow value corresponding to inspiration.

In this embodiment, the expiratory phase pressure threshold (HTP) is the minimum pressure value corresponding to expiration.

In this embodiment, the expiratory phase flow threshold (LTF) is the maximum flow value corresponding to expiration.

In this embodiment, determining, based on the inspiratory phase threshold and the expiratory phase threshold, an expiratory phase and an inspiratory phase in a preset period as a respiratory phase determination result includes:

when the real-time pressure is smaller than an inspiratory phase pressure threshold (LTP) and the real-time flow is larger than an inspiratory phase flow threshold (HTF), judging that the inspiratory phase enters;

when the real-time pressure is greater than an expiratory phase pressure threshold (HTP) and the real-time flow is less than an expiratory phase flow threshold (LTF), then entry into the expiratory phase is determined.

In this embodiment, based on the real-time pressure and the real-time flow rate in the preset period, the expiratory phase and the inspiratory phase in the preset period are determined as the respiratory phase determination result.

In this embodiment, if the pressure or flow cannot meet the requirement that the real-time pressure be less than the inspiratory phase pressure threshold (LTP) and the real-time flow be greater than the inspiratory phase flow threshold (HTF) or the real-time pressure be greater than the expiratory phase pressure threshold (HTP) and the real-time flow be less than the expiratory phase flow threshold (LTF), then the respiratory phase may be deemed to remain unchanged from the previous state; an apnea condition is considered to be present when the pressure and flow values are in a stable state for an extended period of time such that the inspiratory phase is extended for an extended period of time.

In this embodiment, the pressure curve is a curve obtained based on real-time pressure fitting.

In this embodiment, the flow curve is a curve obtained based on real-time flow fitting.

The beneficial effects of the above technology are: the breathing phase is judged by adopting a flow pressure threshold value method to obtain a breathing phase judgment result, and the breathing phase judgment result in a double-level output mode is obtained based on a flow curve and a pressure curve, so that different levels of airway pressure are output at different breathing phase moments, and a data basis is provided for the subsequent autonomous monitoring of a breathing machine and the judgment process of whether the breathing of a patient is abnormal.

Example 5:

on the basis of embodiment 4, the air pressure adjusting end, referring to fig. 5, includes:

In this embodiment, the first sub-line segment is an expiratory phase pressure curve segment or an inspiratory phase pressure curve segment.

In this embodiment, the second sub-line segment is an expiratory phase flow curve segment or an inspiratory phase flow curve segment.

In this embodiment, the pressure threshold and the flow threshold of the sub-line segment are as follows: and (3) corresponding to the inspiration phase threshold or the expiration phase threshold corresponding to the sub-line segment, if the corresponding sub-line segment is the inspiration phase, the inspiration phase threshold is called, and if the corresponding sub-line segment is the expiration phase, the expiration phase threshold is called.

In this embodiment, the average pressure is a real-time pressure average value corresponding to the first sub-line segment.

In this embodiment, the average flow rate is a real-time flow rate average value corresponding to the second sub-line segment.

In this embodiment, the first deviation value is the absolute value of the difference between the average pressure and the pressure threshold.

In this embodiment, the second deviation value is the absolute value of the difference between the average flow rate and the flow rate threshold.

In this embodiment, the third deviation value is a deviation value obtained based on the second deviation value and a functional relationship between the flow rate and the pressure differential.

In this embodiment, the flow rate and pressure differential are as a function of:

wherein Q is the real-time flow, Δ P is the real-time pressure difference, C₁Coefficient of relation between real-time flow and real-time differential pressure, C₂Adjustment constants for real-time flow and real-time differential pressure, C₁、C₂Is obtained by fitting according to a delta P-Q experimental curve of a breathing machine;

for example, Δ P is 100, C₁Is 0.1, C₂Is 1, then Q is 2.

In this embodiment, the third deviation value is a value obtained based on the second deviation value and a functional relationship between the flow rate and the pressure differential.

In this embodiment, calculating a first speed adjustment value based on the first deviation value and a first calculation weight as well as a functional relationship between pressure and speed, calculating a second speed adjustment value based on the third deviation value and a second calculation weight as well as a functional relationship between pressure difference and speed, and calculating a speed adjustment value based on the first speed adjustment value and the second speed adjustment value includes:

F(S₁)＝C₃S₁+C₄

H(S₂)＝C₅S₂+C₆

wherein Δ V is a rotation speed adjustment value, F (S)₁) As a function of pressure and speed, C₃As a coefficient of pressure vs. rotational speed, C₃Has the unit of r/(min. Pa), C₄As adjustment constants for pressure and speed, C₄Has the unit of r/min, C₅Is a coefficient of relation between differential pressure and rotational speed, C₅Has the unit of r/(min. Pa), C₆As a tuning constant for differential pressure and rotational speed, C₆Has the unit of r/min, S₁First deviation value, alpha, of mean pressure and pressure threshold₁For the first calculation of the weight, H (S)₂) As a function of differential pressure and rotational speed, S₂A third deviation value, alpha, obtained on the basis of the second deviation value and a functional relationship between the flow and the pressure difference₂For the second calculation of the weight, t₁To correspond to the duration of the expiratory phase, t₂T is a preset period corresponding to the duration of the inspiratory phase;

for example, S₁Is 10, alpha₁Is 0.1, S₂Is 10, alpha₂Is 0.1, C₃Is 1, C₄Is 0, C₅Is 1, C₆Is 0, t₁Is 0.5, t₂Is 0.5, T is 10, and Δ V is 0.2.

In this embodiment, the functional relationship F (S) of pressure and rotational speed₁) Representing the functional relationship between speed and pressure, the functional relationship H (S) between pressure difference and speed₂) The functional relationship between the rotating speed and the pressure difference is shown and obtained through experimental calibration and Matlab polynomial fitting.

The beneficial effects of the above technology are: the method is used for obtaining a rotating speed adjusting value corresponding to each breath based on real-time pressure and real-time flow corresponding to each breath and a corresponding flow threshold and a corresponding pressure threshold, and regulating the speed of a fan based on the rotating speed adjusting value, so that the problem of low pressure control precision at present is solved, accurate pressure control of a single-level respirator and a double-level respirator is realized, and the airway pressure of the respirator can be automatically adjusted through a related pressure control strategy to eliminate error fluctuation as much as possible, so that the precision of the pressure control of the respirator is improved.

Example 6:

on the basis of embodiment 4, the second determining module, with reference to fig. 6 to 11, includes:

a first fitting unit, configured to fit a corresponding pressure curve (refer to fig. 7) to the real-time pressure in a preset period when the current operating mode is the bi-level output mode, and fit a corresponding duty cycle waveform (refer to fig. 8) according to the real-time pressure in the preset period based on pulse width modulation;

a second fitting unit, configured to fit a corresponding flow curve (refer to fig. 9) and a flow rate change waveform (refer to fig. 9) based on real-time flow in a preset period when the current operating mode is the bi-level output mode;

In this embodiment, the pressure curve is a curve obtained by fitting the real-time pressure in a preset period.

In this embodiment, the duty cycle waveform is a variation curve of the real-time pressure PWM control duty cycle.

In this embodiment, referring to fig. 7 and 8, when the pressure given input is a step input, slow pressurization during respiration is simulated, fig. 7 shows the change situation of the pressure, it can be seen that the actual pressure can follow the given pressure and can be stabilized around the given pressure under the disturbance of respiration, fig. 8 shows the change of the PWM control duty ratio, it can be seen that as the pressure increases, the PWM control duty ratio increases, the change trend of which is opposite to the pressure change trend, when inhaling, the pressure decreases, and to compensate the change of the pressure, the PWM control duty ratio increases, and when exhaling, the pressure increases, and to compensate the change of the pressure, the PWM control duty ratio decreases.

In this embodiment, the alignment graph is obtained by aligning the pressure curve, the duty cycle waveform, the flow curve, and the flow rate waveform.

In this embodiment, referring to fig. 9, the flow data is data after passing through the band-pass filter, and in order to realize the determination of the respiratory phase, according to the flow data, the flow rate during inspiration is increased and the flow rate during expiration is decreased and the change rate is less than zero, so that the respiratory phase can be determined as the expiratory pressure and inspiratory pressure trigger signal of the bi-level respirator according to the change of the flow rate,

x (k) is the rate of change of flow, f (k) is the current flow data, f (k-1) is the last flow data, and Δ t isAnd sampling time intervals, and performing zero-crossing calculation according to the flow rate change rate to obtain y (k), wherein if x (k) is greater than zero, y (k) is 1, and when x (k) is less than zero, y (k) is 0. The expiratory time (i.e., expiratory phase) is obtained from the duration when y (k) is 1, and the inspiratory time (i.e., inspiratory phase) is obtained from the duration when y (k) is 0.

The beneficial effects of the above technology are: corresponding expiration time and inspiration time are judged through a pressure curve, a duty ratio waveform, a flow curve and a flow change rate curve based on a double-level output mode, and switching of inspiration and expiration processes is automatically identified according to respiration conditions, so that airway pressures of different levels are output at different breathing phase moments, and the problem of low breathing phase judgment precision is solved.

Example 7:

on the basis of embodiment 6, the abnormality identification module, referring to fig. 12, includes:

In this embodiment, the abnormal time period is a time period other than the inhalation phase and the exhalation phase.

In this embodiment, the apnea time period is an abnormal time period that satisfies that the corresponding flow rate waveform segment is constantly zero and the corresponding pressure curve segment is a constant function.

In this embodiment, the air leakage fault time period is an abnormal time period that satisfies whether the corresponding flow rate waveform segment is constantly zero and the corresponding real-time pressure is constantly less than the maximum real-time pressure corresponding to the previous adjacent breath.

In this embodiment, the data collection failure time period is an abnormal time period determined to be neither an apnea time period nor an air leakage failure time period among the abnormal time periods.

In this embodiment, the apnea determining threshold is the longest duration of the normal breathing phase or the shortest duration of the apnea.

In this embodiment, the apnea time period is the breathing phase whose duration exceeds the apnea judgment threshold.

The beneficial effects of the above technology are: whether the breathing machine breaks down or not can be identified and whether the breathing data of the patient is abnormal or not can be identified through comparison of the duration of the breathing phase and the apnea judgment threshold and identification and judgment of the relevant data curves of the real-time pressure and the real-time flow in the abnormal time period, and the autonomous monitoring function of the breathing machine and the monitoring function of the breathing data of the patient are realized.

Example 8:

on the basis of embodiment 4, the breath analysis module, with reference to fig. 13, includes:

In this embodiment, the flow function is a function reflecting real-time flow changes.

In this embodiment, the tidal volume is the volume inhaled or exhaled each time in a calm state, and is obtained by integrating the flow rate at a sampling time interval, or the flow rate of the gas in the gas transmission pipeline is obtained by a flow sensor, and the value of the tidal volume can be indirectly calculated by the product of the pipeline diameter and the inhalation time.

In this embodiment, calculating the tidal volume corresponding to each breath based on the duration and flow function corresponding to each breath is: the integral of the duration corresponding to the breath to the flow function is the corresponding tidal volume.

In this embodiment, the breathing process is an exhalation plus an inhalation phase.

In this embodiment, calculating the real-time respiratory rate based on the total number of respiratory processes is: and f is Tn, wherein f is the breathing frequency, n is the total number of breathing processes, and T is a preset period.

In this embodiment, the real-time inspiratory-expiratory ratio is the ratio of the time duration corresponding to the inspiratory phase to the time duration corresponding to the expiratory phase in the last breath.

In this embodiment, minute ventilation is equal to tidal volume multiplied by respiratory rate.

The beneficial effects of the above technology are: the tidal volume, the real-time respiratory frequency, the real-time breathing ratio and the minute ventilation volume are obtained based on the real-time pressure, the real-time flow and the respiratory phase judgment result, the automatic integration function of respiratory data is realized, a user can monitor the respiratory condition of the patient intuitively without the need of physician theoretical guidance and analysis, and the respiratory condition of the patient can be monitored more comprehensively and intuitively.

Example 9:

on the basis of embodiment 7, the transmission alarm terminal, referring to fig. 14, includes:

if not, sending a corresponding fourth alarm instruction to the user side,

otherwise, the current working state is kept.

In this embodiment, the first alarm instruction is an instruction for alerting the user that the patient has an apnea.

In this embodiment, the second alarm instruction is an instruction for reminding the user of the occurrence of the air leakage fault of the ventilator.

In this embodiment, the third alarm instruction is an instruction for reminding the user that the data acquisition failure occurs in the ventilator.

In this embodiment, determining whether the tidal volume, the real-time respiratory rate, the real-time expiratory ratio, and the minute ventilation meet the requirements includes: the tidal volume TV of the breathing machine is less than or equal to 1.5L, and the minute ventilation F is less than or equal to 60L/min, so after calculating the tidal volume and the flow value, whether the tidal volume and the flow value exceed the limit needs to be judged, if the tidal volume and the flow value exceed the limit, the former starts an alarm instruction that the set gas flow cannot be transmitted, and the latter starts an alarm instruction that the actual breathing ratio value is less than the set value, then the calculation is stopped, and the breathing machine is still controlled by using the original control quantity; whether the real-time respiratory frequency is within a preset respiratory frequency threshold value or not needs to be judged, if yes, the real-time respiratory frequency meets the requirement, and otherwise, the real-time respiratory frequency does not meet the requirement; whether the real-time call-suction ratio is within a preset call-suction ratio threshold value (the real-time call-suction ratio is 1: E, the air suction time is 1, and the range of E is 1.5-2.5.) needs to be judged, if yes, the real-time call-suction ratio meets the requirement, and otherwise, the real-time call-suction ratio does not meet the requirement.

In this embodiment, the fourth alarm instruction is an instruction for reminding that the corresponding respiratory data (tidal volume, real-time respiratory rate, real-time respiratory ratio, minute ventilation) do not meet the requirement.

The beneficial effects of the above technology are: the breathing analysis result and the abnormal recognition result are transmitted to the user side and displayed through the transmission display module, so that the breathing data can be remotely monitored to achieve optimal treatment, further fine judgment and comprehensive monitoring on the breathing data of a patient are realized through further analysis and judgment on the breathing analysis result, and an alarm instruction is sent based on the judgment result and the abnormal recognition result, so that the corresponding alarm instruction is sent to remind the user when the breathing machine has an air leakage fault and a data acquisition fault and the breathing data of the patient is abnormal, the first-aid time of the patient is prevented from being delayed or more serious life risks are avoided, and better user experience is provided.

Example 10:

on the basis of any embodiment 1 to 9, an application method of the ventilator air pressure regulation and monitoring system includes:

The beneficial effects of the above technology are: real-time flow is obtained through real-time pressure in the trachea and real-time pressure difference at two ends of the throttling element which are acquired through collection, autonomous monitoring of breathing conditions of a patient and autonomous monitoring of the breathing machine can be achieved based on the acquired data, deviation and adjustment delay of output pressure of a traditional breathing machine are improved, and a transmission alarm end is arranged to remind the patient that emergency measures are not timely taken when the breathing of the patient is abnormal or the breathing of the patient breaks down, so that the condition of the patient is worsened.

It will be apparent to those skilled in the art that various changes and modifications may be made in the present invention without departing from the spirit and scope of the invention. Thus, if such modifications and variations of the present invention fall within the scope of the claims of the present invention and their equivalents, the present invention is also intended to include such modifications and variations.

Claims

1. A ventilator air pressure regulation monitoring system, comprising:

2. The system of claim 1, wherein the ventilator comprises: a fan, a throttling element, a differential pressure sensor, a heating humidifier, a mask and an air pipe.

3. The system of claim 2, wherein the data collection end comprises:

4. The system of claim 3, wherein the data analysis end comprises:

5. The system of claim 4, wherein the pressure regulating end comprises:

6. The system for monitoring and controlling the adjustment of the air pressure of a ventilator according to claim 4, wherein the second determination module comprises:

7. The system of claim 6, wherein the anomaly identification module comprises:

8. The system of claim 4, wherein the breath analysis module comprises:

9. The system of claim 7, wherein the transmission alarm terminal comprises:

if not, sending a corresponding fourth alarm instruction to the user side,

otherwise, the current working state is kept.

10. A method for using the ventilator air pressure regulation monitoring system according to any one of claims 1 to 9, comprising: