CN116115870A - Pressure control method and system thereof, main control equipment and breathing machine - Google Patents

Pressure control method and system thereof, main control equipment and breathing machine Download PDF

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Publication number
CN116115870A
CN116115870A CN202211731694.7A CN202211731694A CN116115870A CN 116115870 A CN116115870 A CN 116115870A CN 202211731694 A CN202211731694 A CN 202211731694A CN 116115870 A CN116115870 A CN 116115870A
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pressure
pressure value
breathing
flow rate
patient
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潘海洋
祝荣荣
余志刚
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Resvent Medical Technology Co Ltd
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Resvent Medical Technology Co Ltd
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Priority to CN202211731694.7A priority Critical patent/CN116115870A/en
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    • 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. mouth-to-mouth respiration; Tracheal tubes
    • A61M16/0057—Pumps therefor
    • A61M16/0066—Blowers or centrifugal pumps
    • A61M16/0069—Blowers or centrifugal pumps the speed thereof being controlled by respiratory parameters, e.g. by inhalation
    • 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. mouth-to-mouth respiration; Tracheal tubes
    • A61M16/021—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes operated by electrical means
    • A61M16/022—Control means therefor
    • A61M16/024—Control means therefor including calculation means, e.g. using a processor
    • 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. mouth-to-mouth respiration; Tracheal tubes
    • A61M16/06—Respiratory or anaesthetic masks
    • 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. mouth-to-mouth respiration; Tracheal tubes
    • A61M16/0003—Accessories therefor, e.g. sensors, vibrators, negative pressure
    • A61M2016/0027—Accessories therefor, e.g. sensors, vibrators, negative pressure pressure meter
    • 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. mouth-to-mouth respiration; Tracheal tubes
    • A61M16/0003—Accessories therefor, e.g. sensors, vibrators, negative pressure
    • A61M2016/003—Accessories therefor, e.g. sensors, vibrators, negative pressure with a flowmeter
    • A61M2016/0033—Accessories therefor, e.g. sensors, vibrators, negative pressure with a flowmeter electrical
    • A61M2016/0039—Accessories therefor, e.g. sensors, vibrators, negative pressure with a flowmeter electrical in the inspiratory circuit
    • 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
    • A61M2205/00—General characteristics of the apparatus
    • A61M2205/33—Controlling, regulating or measuring
    • A61M2205/3331—Pressure; Flow
    • A61M2205/3334—Measuring or controlling the flow rate
    • 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
    • A61M2205/00—General characteristics of the apparatus
    • A61M2205/33—Controlling, regulating or measuring
    • A61M2205/3379—Masses, volumes, levels of fluids in reservoirs, flow rates
    • Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y02—TECHNOLOGIES OR APPLICATIONS FOR MITIGATION OR ADAPTATION AGAINST CLIMATE CHANGE
    • Y02B—CLIMATE CHANGE MITIGATION TECHNOLOGIES RELATED TO BUILDINGS, e.g. HOUSING, HOUSE APPLIANCES OR RELATED END-USER APPLICATIONS
    • Y02B30/00—Energy efficient heating, ventilation or air conditioning [HVAC]
    • Y02B30/70—Efficient control or regulation technologies, e.g. for control of refrigerant flow, motor or heating

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  • Health & Medical Sciences (AREA)
  • Emergency Medicine (AREA)
  • Pulmonology (AREA)
  • Engineering & Computer Science (AREA)
  • Anesthesiology (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Hematology (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Percussion Or Vibration Massage (AREA)

Abstract

The application provides a pressure control method, is applied to the breathing machine, and the breathing machine includes turbo fan, breathing pipeline and face guard, and the breathing pipeline includes machine end and the face guard end that is on the back of the body, and the machine end is connected in turbo fan, and the face guard end is connected in the face guard, and pressure control method includes: detecting the air flow in the breathing circuit to obtain flow rate data of the breathing circuit and a patient pressure value at the mask end; correcting the current machine control pressure value according to the flow rate data and the patient pressure value of the previous respiratory cycle, the set target pressure of the patient end and the real-time flow rate data of the current respiratory cycle, so as to obtain a real-time corrected pressure value; and controlling the turbine fan to output air flow to the breathing pipeline according to the corrected pressure value. In addition, the application also provides a pressure control side system, a main control device and a breathing machine. The pressure control method provided by the application can dynamically correct the fluctuation of pressure control caused by active breathing of the patient, and ensure the treatment effect of the breathing machine.

Description

Pressure control method and system thereof, main control equipment and breathing machine
Technical Field
The application relates to the technical field of respirators, in particular to a pressure control method and system, main control equipment and a respirator.
Background
With the increasing development of medical technology, more and more people are aware of the hazards of respiratory diseases. As a medical device for treating a part of respiratory diseases, a ventilator is required to have high reliability. The breathing machine is provided with an inhalation end pressure sensor, a mask end pressure sensor and a flow rate sensor which are used for controlling the pressure of the airflow in the breathing pipeline. Among them, the inspiratory-end pressure sensor and the flow-rate sensor are generally used as control sensors, and the mask-end pressure sensor is generally used as a detection sensor. Ventilators are also commonly provided with a flow sensor for acquiring flow rate data of the flow of gas in the breathing circuit. The pressure drop of the flow in the breathing circuit is typically calculated from flow rate data by a statically calibrated empirical formula. However, in practical use, the flow rate of the gas in the respiratory pipeline is dynamically changed, and a certain dynamic deviation exists by adopting a static calibration empirical formula to calculate.
Disclosure of Invention
In view of the foregoing, it is desirable to provide a pressure control method and system, a main control device, and a ventilator that can dynamically correct pressure control fluctuations caused by active breathing of a patient, and ensure therapeutic effects of the ventilator.
In a first aspect, an embodiment of the present application provides a pressure control method applied to a breathing machine, the breathing machine including a turbo blower, a breathing circuit, and a mask, the breathing circuit including a machine end and a mask end that are opposite, the machine end being connected to the turbo blower, the mask end being connected to the mask, the pressure control method including:
detecting the flow of gas in the respiratory line to obtain flow rate data of the respiratory line and a patient pressure value at the mask end;
correcting the current machine control pressure value according to the flow rate data and the patient pressure value of the previous respiratory cycle, the set target pressure of the patient end and the real-time flow rate data of the current respiratory cycle, so as to obtain a real-time corrected pressure value; and
and controlling the turbine fan to output air flow to the breathing pipeline according to the corrected pressure value.
In a second aspect, an embodiment of the present application provides a master device, including:
a memory for storing program instructions; and
and a processor for executing the program instructions to implement the pressure control method as described above.
In a third aspect, embodiments of the present application provide a ventilator, the ventilator includes a turbo fan, a breathing circuit, a mask, and a master control device as described above, the breathing circuit includes a machine end and a mask end that are opposite, the machine end is connected to the turbo fan, the mask end is connected to the mask, and the master control device is electrically connected to the turbo fan.
In a fourth aspect, embodiments of the present application provide a pressure control system for a ventilator, the ventilator including a turbo fan, a breathing circuit, and a mask, the breathing circuit including a machine end and a mask end opposite each other, the machine end connected to the turbo fan, the mask end connected to the mask, the pressure control system comprising:
the detection module is used for detecting the air flow in the breathing pipeline to obtain flow rate data of the breathing pipeline and a patient pressure value of the mask end;
the correction module is used for correcting the current machine control pressure value according to the flow rate data and the patient pressure value of the previous respiratory cycle, the set patient end target pressure and the real-time flow rate data of the current respiratory cycle, so as to obtain a real-time corrected pressure value; and
and the control module is used for controlling the turbine fan to output air flow to the breathing pipeline according to the corrected pressure value.
The pressure control method and the system thereof, the main control equipment and the breathing machine detect the flow velocity data of the breathing pipeline and the pressure value of the patient, update the pressure correction value is divided according to the breathing cycle, and the current machine control pressure value is corrected according to the flow velocity data of the last breathing cycle, the pressure value of the patient, the set target pressure of the patient end and the real-time flow velocity data of the current breathing cycle, so that the pressure value of the airflow which the turbofan should output in real time, namely the real-time correction pressure value, is obtained. The pressure value at the machine end is dynamically compensated based on the flow speed data and the patient pressure value, and the problem that the pressure drop of the breathing pipeline of the turbine fan is subjected to leakage compensation or overcompensation in the dynamic gas transmission process can be solved, so that the influence of the pressure drop of the breathing pipeline on the pressure control precision of the output gas flow of the turbine fan of the dynamic control of the breathing machine is reduced, the pressure control precision is improved, and the treatment effect of the breathing machine is effectively improved.
Drawings
In order to more clearly illustrate the embodiments of the present application or the technical solutions in the prior art, the drawings that are required in the embodiments or the description of the prior art will be briefly described below, and it is obvious that the drawings in the following description are only some embodiments of the present application, and that other drawings may be obtained from the structures shown in these drawings without inventive effort to a person of ordinary skill in the art.
Fig. 1 is a flowchart of a pressure control method according to an embodiment of the present application.
Fig. 2 is a first sub-flowchart of a pressure control method according to an embodiment of the present application.
Fig. 3 is a second sub-flowchart of the pressure control method according to the embodiment of the present application.
Fig. 4 is a third sub-flowchart of the pressure control method according to the embodiment of the present application.
Fig. 5 is a fourth sub-flowchart of the pressure control method according to the embodiment of the present application.
Fig. 6 is a schematic diagram of an internal structure of a master control device according to an embodiment of the present application.
Fig. 7 is a schematic diagram of a ventilator according to an embodiment of the present application.
Fig. 8 is a schematic diagram of an internal structure of a ventilator according to an embodiment of the present disclosure.
Fig. 9 is a schematic diagram of an internal structure of a pressure control system according to an embodiment of the present application.
Fig. 10 is a waveform diagram of the patient pressure values shown in fig. 1 before and after correction.
The realization, functional characteristics and advantages of the present application will be further described with reference to the embodiments, referring to the attached drawings.
Detailed Description
In order to make the objects, technical solutions and advantages of the present application more apparent, the present application will be further described in detail with reference to the accompanying drawings and examples. It should be understood that the specific embodiments described herein are for purposes of illustration only and are not intended to limit the present application. All other embodiments, which can be made by one of ordinary skill in the art without undue burden from the present disclosure, are within the scope of the present disclosure.
The terms "first," "second," "third," "fourth" and the like in the description and in the claims of this application and in the above-described figures, if any, are used for distinguishing between similar elements of a plan and not necessarily for describing a particular sequential or chronological order. It is to be understood that the data so used may be interchanged under appropriate circumstances, or in other words, the described embodiments may be implemented in other sequences than those illustrated or otherwise described herein. Furthermore, the terms "comprises," "comprising," and "having," and any variations thereof, may also include other items, such as processes, methods, systems, articles, or apparatus that include a series of steps or elements, are not necessarily limited to only those steps or elements explicitly listed, but may include other steps or elements not explicitly listed or inherent to such processes, methods, articles, or apparatus.
It should be noted that the description herein of "first," "second," etc. is for descriptive purposes only and is not to be construed as indicating or implying a relative importance or implying an indication of the number of technical features being indicated. Thus, a feature defining "a first" or "a second" may explicitly or implicitly include one or more such feature. In addition, the technical solutions of the embodiments may be combined with each other, but it is necessary to base that the technical solutions can be realized by those skilled in the art, and when the technical solutions are contradictory or cannot be realized, the combination of the technical solutions should be regarded as not exist and not within the protection scope of the present application.
Referring to fig. 1 and fig. 7 in combination, fig. 1 is a flowchart of a pressure control method according to an embodiment of the present application, and fig. 7 is a schematic diagram of a ventilator according to an embodiment of the present application. The ventilator 1 comprises a turbo blower 10, a breathing circuit 20 and a mask 30. In this embodiment, the breathing circuit 20 includes a machine end 21 and a mask end 22 that are opposite, the machine end 21 being connected to the turbo-fan 10 and the mask end 22 being connected to the mask 30. It will be appreciated that the turbo blower 10, the breathing circuit 20 and the mask 30 are connected in sequence. The turbo blower 10 is used to generate an air flow for providing a breathing air flow for a user of the ventilator 1. Wherein the air flow generated by the turbo fan 10 passes through the breathing circuit 20 and the mask 30 in sequence for the user to inhale.
The pressure control method is applied to the ventilator 1 for controlling the operation of the turbo fan 10 to adjust the magnitude of the air flow to the mask end 22. The pressure control method specifically comprises the following steps.
Step S102, detecting the air flow in the breathing circuit to obtain flow rate data of the breathing circuit and a patient pressure value at the mask end.
The ventilator 1 detects the flow velocity of the air flow in the breathing circuit 20 in real time, so as to obtain flow velocity data; the pressure of the flow of gas through the mask end 22 is sensed to obtain a patient pressure value. In the present embodiment, the ventilator 1 performs flow rate detection on the airflow passing through the machine end 21, thereby obtaining flow rate data. Specifically, ventilator 1 may control flow rate sensor detection flow rate data provided to respiratory line 20, and may control pressure sensor detection patient pressure value provided to mask end 22. Preferably, the flow rate sensor is provided at the machine end 21 of the breathing circuit 22.
In this embodiment, ventilator 1 detects both the machine end 21 and the mask end 22 to obtain synchronized flow rate data and patient pressure values. It will be appreciated that both the flow rate data and the patient pressure values are time series data. After the flow rate data and the patient pressure value are detected, the ventilator 1 divides the flow rate data and the patient pressure value according to the respiratory cycle, thereby obtaining the flow rate data and the patient pressure value corresponding to each respiratory cycle.
Step S104, correcting the current machine control pressure value according to the flow rate data and the patient pressure value of the previous respiratory cycle, the set target pressure of the patient end and the real-time flow rate data of the current respiratory cycle, so as to obtain a real-time corrected pressure value.
The ventilator 1 corrects the current machine control pressure value of the machine end 21 according to the flow rate data and the patient pressure value of the previous breathing cycle, the set target pressure of the patient end and the real-time flow rate data of the current breathing cycle, so as to obtain a real-time corrected pressure value.
How to correct the current machine control pressure value according to the flow rate data and the patient pressure value of the previous breathing cycle, the set target pressure at the patient end and the real-time flow rate data of the current breathing cycle, so as to obtain the real-time corrected pressure value is described in detail below.
And S106, controlling the turbine fan to output air flow to the breathing pipeline according to the corrected pressure value.
The ventilator 1 controls the operation power of the turbo fan 10 according to the corrected pressure value, thereby adjusting the pressure of the air flow output to the breathing circuit 20. Specifically, the ventilator 1 controls the pressure of the air flow output by the turbofan 10 according to the corrected pressure value calculated in real time.
In this embodiment, the pressure of the air flow reaching the mask end 22 is lower than the pressure of the air flow at the machine end 21 because the air flow is compressed by the breathing circuit 20 when flowing in the breathing circuit 20. Therefore, by correcting the machine pressure value at the machine end 21, the pressure of the air flow output from the turbo fan 10 is dynamically adjusted so that the pressure of the air flow reaching the mask end 22 is maintained at a certain level. A waveform diagram of the patient pressure value of the corrected front mask end 22 and a waveform diagram of the patient pressure value of the corrected rear mask end 22 are shown in fig. 10.
The specific process of controlling the turbine fan to output an airflow to the breathing circuit based on the corrected pressure value will be described in detail below.
In the above embodiment, the flow rate data of the respiratory line and the pressure value of the patient are detected, the update of the pressure correction value is divided according to the respiratory cycle, and the current machine control pressure value is corrected according to the flow rate data of the previous respiratory cycle, the pressure value of the patient, the set target pressure of the patient end and the real-time flow rate data of the current respiratory cycle, so as to obtain the pressure value of the air flow which should be output by the turbofan in real time, namely, the real-time corrected pressure value. The pressure value at the machine end is dynamically compensated based on the flow speed data and the patient pressure value, and the problem that the pressure drop of the breathing pipeline of the turbine fan is subjected to leakage compensation or overcompensation in the dynamic gas transmission process can be solved, so that the influence of the pressure drop of the breathing pipeline on the pressure control precision of the output gas flow of the turbine fan of the dynamic control of the breathing machine is reduced, the pressure control precision is improved, and the treatment effect of the breathing machine is effectively improved.
Referring to fig. 2 in combination, a first sub-flowchart of a pressure control method according to an embodiment of the present application is shown. Step S104 specifically includes the following steps.
Step S202, calculating a correction coefficient according to the flow rate data of the previous respiratory cycle, the pressure value of the patient and the target pressure of the patient end.
The ventilator 1 calculates a correction factor based on the flow rate data of the previous breathing cycle and the corresponding patient pressure value and the set patient-side target pressure.
The specific process of how the correction factor is calculated based on the flow rate data and the patient pressure value for the last respiratory cycle, and the patient end target pressure, is described in detail below.
Step S204, calculating a corrected pressure value according to the preset coefficient, the corrected coefficient and the real-time flow rate data of the current respiratory cycle.
The ventilator 1 calculates a real-time corrected pressure value from the real-time flow rate data of the current respiratory cycle, the preset coefficient and the correction coefficient. The preset coefficient is obtained through static flow rate calibration.
The specific process of how the corrected pressure value is calculated from the preset coefficients, the correction coefficients, and the real-time flow rate data for the current respiratory cycle will be described in detail below.
Please refer to fig. 3 in combination, which is a second sub-flowchart of the pressure control method provided in the embodiment of the present application. Step S202 specifically includes the following steps.
Step S302, calculating a pressure deviation value according to the target pressure of the patient end and the pressure value of the patient in the previous respiratory cycle.
The ventilator 1 calculates a pressure deviation value based on the patient end target pressure and the patient pressure value of the previous breathing cycle. In this embodiment, the ventilator 1 calculates the difference between the patient end target pressure and the patient pressure value of the previous breathing cycle as the pressure deviation value. Where the patient side target pressure is the pressure value that the flow of gas through mask end 22 should have.
Step S304, calculating a correction coefficient according to the flow velocity data and the pressure deviation value of the previous respiratory cycle.
The ventilator 1 calculates a correction coefficient based on the flow rate data and the pressure deviation value of the previous respiratory cycle. In this embodiment, calculating the correction coefficient based on the flow rate data and the pressure deviation value of the previous respiratory cycle specifically includes: the ventilator 1 fits the flow rate data and the pressure deviation value of the previous respiratory cycle according to the least square method to obtain a correction coefficient. Specifically, the ventilator 1 uses a least squares fit to obtain a first equation based on an empirical equation of flow rate and tube pressure drop. The first formula is specifically: p_error=k_error flow_ex 2 . Where p_error represents the pressure deviation value, k_error represents the correction factor, and flow_ex represents the flow rate data of the previous respiratory cycle.
In the above embodiment, the pressure deviation value in the previous respiratory cycle is calculated according to the actual patient pressure value and the preset target pressure at the patient end, and the pressure deviation value in the previous respiratory cycle and the flow rate data in the previous respiratory cycle are fitted into an exponential curve of the flow rate data and the pressure deviation value by means of least square curve fitting, so as to obtain a correction coefficient, and the machine pressure value can be corrected better in combination with the flow rate condition of the actual airflow.
Referring to fig. 4 in combination, a third sub-flowchart of the pressure control method according to the embodiment of the present application is shown. Step S204 specifically includes the following steps.
Step S402, calculating a machine control pressure value according to the preset coefficient and the real-time flow rate data of the current respiratory cycle.
The ventilator 1 is based on the preset coefficient in real time for the current breathing cycleThe flow rate data calculates a machine control pressure value. In the present embodiment, the ventilator 1 calculates the machine control pressure value according to the second formula. Specifically, the second formula is: p_insp=p_set+k flow 2 . Where p_insp represents the machine control pressure value, p_set represents the patient pressure value, K represents a preset coefficient, and flow represents the real-time flow rate data for the current respiratory cycle.
Step S404, calculating a corrected respiratory pipeline pressure drop value according to the correction coefficient and the real-time flow rate data of the current respiratory cycle.
The ventilator 1 calculates a corrected breathing conduit pressure drop value based on the correction factor and the real-time flow rate data for the current breathing cycle. In this embodiment, ventilator 1 calculates a corrected airway pressure drop value according to a third formula. Specifically, the third formula is: p_error=k_error flow 2 . Where p_error represents the corrected respiratory tubing pressure drop value, k_error represents the correction factor, and flow represents the real-time flow rate data for the current respiratory cycle.
Step S406, calculating a corrected pressure value according to the machine control pressure value and the corrected respiratory tract pressure drop value.
The ventilator 1 calculates a corrected pressure value from the machine control pressure value and the corrected airway pressure drop value. In the present embodiment, the ventilator 1 calculates the sum of the machine control pressure value and the corrected respiratory tract pressure drop value as the corrected pressure value. Specifically, the ventilator 1 calculates the corrected pressure value according to the fourth formula. The fourth formula is: p=p_insp+p_error. Where p represents the corrected pressure value, p_insp represents the machine control pressure value, and p_error represents the corrected airway pressure drop value.
In the above embodiment, the real-time and dynamic compensation value of the pressure drop of the breathing pipeline is obtained according to the real-time flow rate data of the current breathing cycle and the correction coefficient, that is, the pressure drop value of the breathing pipeline is corrected, and the machine control pressure value is corrected according to the corrected pressure drop value of the breathing pipeline to obtain the corrected pressure value, so that the machine control pressure value is corrected, the accuracy and stability of the pressure control of the turbine fan by the breathing machine are improved, and the positive effect on the treatment of the user can be achieved.
Referring to fig. 5 in combination, a fourth sub-flowchart of the pressure control method according to the embodiment of the present application is shown. Step S106 specifically includes the following steps.
Step S502, calculating the turbine rotating speed according to the corrected pressure value.
The ventilator 1 calculates the turbine rotational speed from the corrected pressure value according to a preset algorithm. The preset algorithm may be set according to an actual situation of the turbo fan, which is not limited herein.
Step S504, controlling the output airflow of the turbine fan according to the rotation speed of the turbine.
The ventilator 1 controls the turbine fan 10 to output an air flow according to the turbine rotation speed so that the pressure value of the air flow at the machine end 21 is a corrected pressure value.
In the above embodiment, the turbine rotational speed is calculated according to the corrected pressure value, and the operation of the turbine fan is controlled, so that the delivery of the target gas is completed, and the pressure of the gas flow delivered to the mask end is maintained at a certain level, without generating large fluctuation.
Please refer to fig. 6 in combination, which is a schematic diagram illustrating an internal structure of a master control device according to an embodiment of the present application. The master device 40 includes a memory 41 and a processor 42. The memory 41 is used for storing program instructions and the processor 42 is used for executing the program instructions to implement the pressure control method described above.
The processor 42 may be a central processing unit (Central Processing Unit, CPU), controller, microcontroller, microprocessor or other data processing chip in some embodiments for executing program instructions stored in the memory 41.
The memory 41 includes at least one type of readable storage medium including flash memory, a hard disk, a multimedia card, a card memory (e.g., SD or DX memory, etc.), magnetic memory, magnetic disk, optical disk, etc. The memory 41 may in some embodiments be an internal storage unit of a computer device, such as a hard disk of the computer device. The memory 41 may also be an external storage device of the computer device in other embodiments, such as a plug-in hard disk, a Smart Media Card (SMC), a Secure Digital (SD) Card, a Flash memory Card (Flash Card) or the like, which are provided on the computer device. Further, the memory 41 may also include both an internal storage unit and an external storage device of the computer device. The memory 41 may be used not only for storing application software installed in a computer device and various types of data, such as a code or the like for realizing a pressure control method, but also for temporarily storing data that has been output or is to be output.
Referring to fig. 7 and fig. 8 in combination, fig. 7 is a schematic diagram of a ventilator according to an embodiment of the present application, and fig. 8 is a schematic diagram of an internal structure of a ventilator according to an embodiment of the present application. The breathing machine 1 comprises a turbine fan 10, a breathing pipeline 20, a mask 30 and a main control device 40, wherein the main control device 40 is electrically connected with the turbine fan 10. Wherein the specific structure of the master device 40 refers to the above-described embodiment.
The breathing circuit 20 includes an opposite machine end 21 and a mask end 22, the machine end 21 being connected to the turbo-fan 10 and the mask end 22 being connected to the mask 30. It will be appreciated that the turbo blower 10, the breathing circuit 20 and the mask 30 are connected in sequence. The turbo blower 10 is used to generate an air flow for providing a breathing air flow for a user of the ventilator 1. Wherein the flow of air generated by the turbo blower 10 passes through the breathing circuit 20 and the mask 30 in sequence to the patient's breathing airways and maintains the desired airway pressure. The ventilator 1 further comprises a flow rate sensor 50 and a pressure sensor 60. Specifically, a flow rate sensor 50 is mounted to the breathing circuit 20 for acquiring flow rate data of the breathing circuit 20. A pressure sensor 60 is mounted to the mask end 22 of the breathing circuit 20 for acquiring patient pressure values at the mask end 22. In the present embodiment, the flow rate sensor 50 is mounted to the machine end 21. The main control device 40 is electrically connected with the flow rate sensor 50 and the pressure sensor 60, the flow rate sensor 50 transmits the acquired flow rate data to the main control device 40, and the pressure sensor 60 transmits the acquired patient pressure value to the main control device 40.
Please refer to fig. 9 in combination, which is a schematic diagram illustrating an internal structure of a pressure control system according to an embodiment of the present application. The pressure control system 90 is applied to the above-described ventilator 1. The pressure control system 90 includes a detection module 91, a correction module 92, and a control module 93.
A detection module 91 for detecting the flow of air in the breathing circuit to obtain flow rate data of the breathing circuit and a patient pressure value at the mask end.
The detection module 91 detects the flow velocity of the air flow in the respiratory pipeline 20 in real time, so as to obtain flow velocity data; the pressure of the flow of gas through the mask end 22 is sensed to obtain a patient pressure value. In the present embodiment, the detection module 91 performs flow rate detection on the air flow passing through the machine end 21, thereby obtaining flow rate data. Specifically, the detection module 91 may control the flow sensor 50 disposed on the breathing circuit 20 to detect flow data, and may control the pressure sensor 60 disposed on the mask end 22 to detect patient pressure. Preferably, the flow sensor 50 is provided at the machine end 21 of the breathing circuit 22.
In this embodiment, the detection module 91 detects both the machine end 21 and the mask end 22 to obtain synchronized flow rate data and patient pressure values. It will be appreciated that both the flow rate data and the patient pressure values are time series data. After detecting the flow rate data and the patient pressure value, the detection module 91 divides the flow rate data and the patient pressure value according to the respiratory cycle, thereby obtaining the flow rate data and the patient pressure value corresponding to each respiratory cycle.
The correction module 92 is configured to correct the current machine control pressure value according to the flow rate data and the patient pressure value of the previous respiratory cycle, the set target pressure at the patient end, and the real-time flow rate data of the current respiratory cycle, so as to obtain a real-time corrected pressure value.
The correction module 92 corrects the current machine control pressure value of the machine end 21 according to the flow rate data and the patient pressure value of the previous breathing cycle, the set target pressure of the patient end and the real-time flow rate data of the current breathing cycle, so as to obtain a real-time corrected pressure value.
The control module 93 is used for controlling the turbine fan to output air flow to the breathing pipeline according to the corrected pressure value.
The control module 93 controls the operating power of the turbo fan 10 according to the corrected pressure value, thereby adjusting the pressure of the output air flow to the breathing circuit 20. Specifically, the control module 93 controls the pressure of the air flow output by the turbo fan 10 according to the corrected pressure value calculated in real time.
In this embodiment, the pressure of the air flow reaching the mask end 22 is lower than the pressure of the air flow at the machine end 21 because the air flow is compressed by the breathing circuit 20 when flowing in the breathing circuit 20. Therefore, by correcting the machine pressure value at the machine end 21, the pressure of the air flow output from the turbo fan 10 is dynamically adjusted so that the pressure of the air flow reaching the mask end 22 is maintained at a certain level.
It will be apparent to those skilled in the art that various modifications and variations can be made in the present application without departing from the spirit or scope of the application. Thus, if and when such modifications and variations of the present application fall within the scope of the claims and their equivalents, the present application is intended to cover such modifications and variations.
The foregoing list of preferred embodiments of the present application is, of course, not intended to limit the scope of the claims hereof, and therefore, equivalent changes as set forth in the claims hereof are intended to fall within the scope of the present application.

Claims (10)

1. The utility model provides a pressure control method, characterized in that is applied to the breathing machine, the breathing machine includes turbo fan, breathing circuit and face guard, the breathing circuit includes machine end and the face guard end that are opposite, the machine end connect in turbo fan, the face guard end connect in the face guard, the pressure control method includes:
detecting the flow of gas in the respiratory line to obtain flow rate data of the respiratory line and a patient pressure value at the mask end;
correcting the current machine control pressure value according to the flow rate data and the patient pressure value of the previous respiratory cycle, the set target pressure of the patient end and the real-time flow rate data of the current respiratory cycle, so as to obtain a real-time corrected pressure value; and
and controlling the turbine fan to output air flow to the breathing pipeline according to the corrected pressure value.
2. The method of claim 1, wherein correcting the current machine control pressure value based on the flow rate data and the patient pressure value of the previous breathing cycle and the set patient end target pressure, real-time flow rate data of the current breathing cycle, thereby obtaining the real-time corrected pressure value comprises:
calculating a correction coefficient according to the flow rate data of the previous respiratory cycle, the pressure value of the patient and the target pressure of the patient end; and
and calculating the corrected pressure value according to a preset coefficient, the correction coefficient and the real-time flow rate data of the current respiratory cycle.
3. The pressure control method of claim 2, wherein calculating a correction factor based on the flow rate data and the patient pressure value for the previous breathing cycle, the patient side target pressure, specifically comprises:
calculating a pressure deviation value according to the target pressure of the patient end and the pressure value of the patient in the previous respiratory cycle; and
and calculating the correction coefficient according to the flow rate data of the previous respiratory cycle and the pressure deviation value.
4. A pressure control method according to claim 3, wherein calculating the correction factor from the flow rate data of the previous respiratory cycle and the pressure deviation value specifically includes:
and fitting the flow velocity data of the previous respiratory cycle and the pressure deviation value according to a least square method to obtain the correction coefficient.
5. The pressure control method of claim 2, wherein calculating the corrected pressure value based on a preset coefficient, the correction coefficient, and real-time flow rate data for the current respiratory cycle comprises:
calculating the machine control pressure value according to the preset coefficient and the real-time flow rate data of the current respiratory cycle;
calculating a corrected respiratory pipeline pressure drop value according to the correction coefficient and the real-time flow rate data of the current respiratory cycle; and
the corrected pressure value is calculated from the machine control pressure value and the corrected respiratory tract pressure drop value.
6. The pressure control method of claim 1, wherein controlling the turbine fan to output a flow of gas to the breathing circuit based on the corrected pressure value comprises:
calculating the turbine rotational speed according to the corrected pressure value; and
and controlling the output airflow of the turbine fan according to the turbine rotating speed.
7. A master device, the master device comprising:
a memory for storing program instructions; and
a processor for executing the program instructions to implement the pressure control method of any one of claims 1 to 6.
8. A respirator comprising a turbo blower, a breathing circuit, a mask and the master control device of claim 7, wherein the breathing circuit comprises a machine end and a mask end which are opposite to each other, the machine end is connected to the turbo blower, the mask end is connected to the mask, and the master control device is electrically connected to the turbo blower.
9. The ventilator of claim 8, further comprising a flow sensor mounted to the breathing circuit for collecting flow data from the breathing circuit and a pressure sensor mounted to a mask end of the breathing circuit for collecting patient pressure values from the mask end.
10. The utility model provides a pressure control system, its characterized in that is applied to the breathing machine, the breathing machine includes turbo fan, breathing circuit and face guard, the breathing circuit includes machine end and the face guard end that is opposite, machine end connect in turbo fan, the face guard end connect in the face guard, pressure control system includes:
the detection module is used for detecting the air flow in the breathing pipeline to obtain flow rate data of the breathing pipeline and a patient pressure value of the mask end;
the correction module is used for correcting the current machine control pressure value according to the flow rate data and the patient pressure value of the previous respiratory cycle, the set patient end target pressure and the real-time flow rate data of the current respiratory cycle, so as to obtain a real-time corrected pressure value; and
and the control module is used for controlling the turbine fan to output air flow to the breathing pipeline according to the corrected pressure value.
CN202211731694.7A 2022-12-30 2022-12-30 Pressure control method and system thereof, main control equipment and breathing machine Pending CN116115870A (en)

Priority Applications (1)

Application Number Priority Date Filing Date Title
CN202211731694.7A CN116115870A (en) 2022-12-30 2022-12-30 Pressure control method and system thereof, main control equipment and breathing machine

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
CN202211731694.7A CN116115870A (en) 2022-12-30 2022-12-30 Pressure control method and system thereof, main control equipment and breathing machine

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CN116115870A true CN116115870A (en) 2023-05-16

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