WO2016155392A1 - Ventilateur et son système de circuit d'air d'élimination d'humidité - Google Patents

Ventilateur et son système de circuit d'air d'élimination d'humidité Download PDF

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Publication number
WO2016155392A1
WO2016155392A1 PCT/CN2015/099925 CN2015099925W WO2016155392A1 WO 2016155392 A1 WO2016155392 A1 WO 2016155392A1 CN 2015099925 W CN2015099925 W CN 2015099925W WO 2016155392 A1 WO2016155392 A1 WO 2016155392A1
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WO
WIPO (PCT)
Prior art keywords
differential pressure
gas
air
monitoring
pipe
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Application number
PCT/CN2015/099925
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English (en)
Chinese (zh)
Inventor
成其新
赵晨
马建新
Original Assignee
深圳市科曼医疗设备有限公司
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Filing date
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Application filed by 深圳市科曼医疗设备有限公司 filed Critical 深圳市科曼医疗设备有限公司
Publication of WO2016155392A1 publication Critical patent/WO2016155392A1/fr

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. 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

Definitions

  • the invention relates to the field of medical equipment, in particular to a ventilator and a gas path system thereof.
  • Ventilator used in medical treatment often uses an external differential pressure flow sensor for near-patient flow and pressure monitoring.
  • the external differential pressure flow sensor can accurately monitor the patient's inhaled and exhaled tidal volume, with high reliability and relatively high cost. Wire flow sensors are low and therefore widely used in ventilators.
  • the existing ventilator using the differential pressure sensor Since the existing ventilator using the differential pressure sensor is in use, the gas exhaled by the patient enters the two monitoring pipes of the flow sensor, and the exhaled gas carries a large amount of water vapor, which easily generates condensed water in the monitoring pipe. Over time, the condensate will stay in the monitoring pipeline, causing inaccurate monitoring of the flow sensor, or even damage to the flow sensor monitoring, resulting in equipment failure.
  • there is a method of removing water vapor by heating to prevent the generation of condensed water and a method of blowing the condensed water by using a high-pressure high-speed air stream.
  • the above two methods have deficiencies.
  • the method of heating and removing water vapor needs to add a heating device, which has the characteristics of high cost and complicated process, and is prone to high temperature danger.
  • the high-pressure high-speed airflow is used to blow away the condensed water. It needs to use a high-pressure gas source. It must also use a pressure-reducing valve to adjust the pressure. Once the water-switching solenoid valve fails, it is equivalent to the patient and the high-pressure gas source. Connecting together to direct a high-pressure source to the patient is very dangerous.
  • a ventilator including the above-described gas path system for removing moisture is also provided.
  • a gas path system for removing moisture from a ventilator comprising:
  • a gas source device for providing a gas source
  • differential pressure generating device for generating a gas flow pressure difference
  • the differential pressure generating device is connected to the gas source device through a pipe, and the differential pressure generating device is further connected with a breathing pipe for breathing of the patient and an air outlet communicating with the outside pipeline;
  • a first electromagnetic valve is mounted on the air outlet pipe for controlling communication between the air outlet pipe and the outside;
  • Differential pressure flow sensor for monitoring the flow of gas when the patient breathes
  • a first monitoring pipeline the two ends being respectively connected to the differential pressure generating device and the differential pressure flow sensor;
  • a second monitoring pipeline wherein the two ends are respectively connected to the differential pressure generating device and the differential pressure flow sensor;
  • a gas capacity communicating with the first monitoring pipe through a first connecting pipe, communicating with the second monitoring pipe through a second connecting pipe, and communicating with the gas source device through a third connecting pipe;
  • a second electromagnetic valve disposed on the third connecting pipe for controlling communication and blocking of the third connecting pipe
  • a pressure sensor disposed on the first monitoring pipe or the second monitoring pipe, wherein the pressure sensor is configured to detect a gas pressure value in the differential pressure generating device;
  • circuit control unit electrically connected to the differential pressure flow sensor, the first electromagnetic valve, the second electromagnetic valve, and the pressure sensor, the circuit control unit controlling the first electromagnetic valve and the a second solenoid valve is opened and closed, and the circuit control unit is provided with a preset air pressure value that is compared with a pressure value detected by the pressure sensor;
  • the second electromagnetic valve when the air pressure value detected by the pressure sensor reaches the preset air pressure value, the second electromagnetic valve is closed; when the patient exhales, the air volume is deflated to prevent the gas exhaled by the patient from flowing to the The first monitoring pipe and the second monitoring pipe are described.
  • the method further includes:
  • first restrictor and the second restrictor are used to limit the rate of deflation of the gas volume.
  • the first restrictor is a gas barrier or a throttle.
  • the second restrictor is a gas barrier or a throttle.
  • a third solenoid valve and a fourth solenoid valve for calibrating the differential pressure flow sensor, the third solenoid valve being disposed on the first monitoring conduit and The circuit control unit is electrically connected; the fourth electromagnetic valve is disposed on the second monitoring pipeline and electrically connected to the circuit control unit.
  • the pressure sensor is located between the first connecting pipe and the differential pressure flow sensor; or the pressure sensor is located at the second connecting pipe and the differential pressure flow sensor between.
  • the gas source device is a turbofan or a high pressure gas source assembly.
  • the method further includes a gas pressure control member disposed on the pipe connecting the gas source device and the differential pressure generating device, and the gas pressure control member is located at the gas source device and the differential pressure occurs Between devices.
  • the air pressure control member is a pressure limiting valve or a free suction valve.
  • a ventilator includes a gas path system for removing moisture from the ventilator.
  • the patient inhales through the breathing pipe.
  • the first electromagnetic valve is closed, the second electromagnetic valve is opened, and the gas source device supplies a gas source to the patient, and the gas source is provided by the gas source device.
  • the air source device After the differential pressure generating device is delivered to the patient, at the same time, since the second electromagnetic valve is opened, the air source device also enters the air volume through the third connecting pipe, and inflates the air capacity, and the air pressure value in the differential pressure generating device reaches When the air pressure value is set, the second electromagnetic valve is closed; when the patient exhales, the first electromagnetic valve is opened, and the air outlet pipe communicates with the outside, and as the patient exhales, the airflow in the differential pressure generating device flows from the air outlet pipe to the outside, making the difference The air pressure value in the pressure generating device becomes smaller.
  • the air pressure value in the differential pressure generating device When the air pressure value in the differential pressure generating device is smaller than the air pressure value in the air volume, the air volume starts to deflate, and the gas in the air volume passes through the first connecting pipe and the second connecting pipe, and then Flowing through the first monitoring pipeline and the second monitoring pipeline to the differential pressure generating device respectively, that is, respectively forming the airflow from the first monitoring pipeline to the differential pressure generating device and from the second monitoring pipeline to the differential pressure generating
  • the airflow of the device prevents the airflow in the differential pressure generating device from flowing to the first monitoring pipeline and the second monitoring pipeline, that is, the process of removing water is the patient's exhalation while preventing the patient from exhaling the water vapor and the differential pressure generating device.
  • the condensed water enters the first monitoring pipeline and the second monitoring pipeline, effectively avoiding the problem of forming condensed water in the first monitoring pipeline and the second monitoring pipeline, and the method of removing water vapor by using the heating method and using high voltage Compared with the way in which the high-speed airflow blows away the condensed water, the water removal process of the above-mentioned water vapor system is adapted to the patient's breathing process, and the patient's breathing control is adopted, which is more safe and reliable.
  • Fig. 1 is a schematic view showing the structure of a gas path system for removing water vapor of a ventilator according to an embodiment.
  • a ventilator of an embodiment includes a pneumatic system 100 for removing moisture.
  • the water vapor removal system 100 includes a gas source device 110, a differential pressure generating device 120, a first electromagnetic valve 130, a differential pressure flow sensor 140, a first monitoring conduit 150, a second monitoring conduit 160, a gas volume 170, and a Two solenoid valves 180, a pressure sensor 190 and a circuit control unit (not shown).
  • the air source device 110 is used to provide a source of air.
  • the air source device 110 is a turbo fan or a high pressure gas source assembly.
  • the air supply device 110 is a turbofan
  • the turbofan draws air into the ventilator.
  • the gas source device 110 is a high-pressure gas source assembly
  • the high-pressure gas source assembly includes a gas cylinder equipped with a high-pressure gas source and a flow control solenoid valve connected to the high-pressure gas cylinder, and the flow rate controlled by the flow control solenoid valve is controlled to enter the gas source. .
  • the differential pressure generating device 120 is for generating a gas flow pressure difference.
  • the differential pressure generating device 120 is in communication with the air source device 110 through a pipe.
  • the differential pressure generating device 120 is connected to a breathing duct 122 for breathing by the patient and an air outlet duct 124 communicating with the outside.
  • the air outlet duct 124 is disposed on the duct connecting the differential pressure generating device 120 and the air source device 110.
  • the differential pressure generating device 120 can be a differential pressure type flow sensor, that is, an external differential pressure type flow sensor.
  • the air outlet duct 124 is disposed in the pipeline connecting the differential pressure generating device 120 and the air source device 110. on.
  • the water vapor system 100 other than the water vapor further includes a gas pressure control member 210 disposed on the pipeline connecting the gas source device 110 and the differential pressure generating device 120, and the air pressure control member 210 is located at the gas source device 110 and the differential pressure generating device 120. between.
  • the air pressure control member 210 is for controlling the air pressure on the pipes of the air source device 110 and the differential pressure generating device 120.
  • the air pressure control member 210 is a pressure limiting valve or a free suction valve.
  • the first solenoid valve 130 is mounted on the air outlet duct 124 for controlling the communication between the air outlet duct 124 and the outside. Wherein, when the patient inhales, the first electromagnetic valve 130 is closed, so that the airflow in the pneumatic system cannot flow to the outside; when the patient exhales, the first electromagnetic valve 130 is opened, and at this time, the outlet conduit 124 communicates with the outside, and the airflow The differential pressure generating device 120 flows to the outside of the air outlet duct 124.
  • the differential pressure flow sensor 140 is used to monitor the flow of gas when the patient is breathing.
  • Both ends of the first monitoring pipe 150 are in communication with the differential pressure generating device 120 and the differential pressure flow sensor 140, respectively.
  • Both ends of the second monitoring pipe 160 are in communication with the differential pressure generating device 120 and the differential pressure flow sensor 140, respectively.
  • the differential pressure flow sensor 140 monitors the gas flow rate of the patient when breathing by monitoring the airflow pressure difference in the first monitoring conduit 150 and the second monitoring conduit 160.
  • the moisture removal system 100 further includes a third solenoid valve 220 and a fourth solenoid valve 230 for calibrating the differential pressure flow sensor 140.
  • the third solenoid valve 220 is disposed on the first monitoring conduit 150;
  • the solenoid valve 230 is disposed on the second monitoring pipe 160.
  • the third electromagnetic valve 220 and the fourth electromagnetic valve 230 are disposed on the first monitoring pipe 150 and the second monitoring pipe 160 respectively to: when the differential pressure type flow sensor 140 drifts, the third electromagnetic valve 220 and the fourth electromagnetic The valve 230 disconnects the differential pressure type flow sensor 140 from the first monitoring pipe 150 and the second monitoring pipe 160 to communicate with the atmosphere, thereby performing zero calibration of the differential pressure type flow sensor 140 to ensure the differential pressure type flow sensor. 140 accuracy and reliability.
  • the air volume 170 is in communication with the first monitoring conduit 150 through the first connecting conduit 240, with the second monitoring conduit 160 through the second connecting conduit 250, and with the gas source device 110 through the third connecting conduit 260.
  • the plenum 170 deflates to prevent the patient's exhaled gas from flowing to the first monitoring conduit 150 and the second monitoring conduit 160.
  • the third electromagnetic valve 220 is located between the second connecting pipe 250 and the differential pressure flow sensor 140; the fourth electromagnetic valve 230 is located between the first connecting pipe 240 and the differential pressure flow sensor 140.
  • the second solenoid valve 180 is disposed on the third connecting pipe 260 for controlling the communication and blocking of the third connecting pipe 260.
  • the air source device 110 inflates the air volume 170. That is, when the second solenoid valve 180 is opened, the air source device 110 and the air volume 170 are in communication, and the air source device 110 supplies air to the air volume 170 through the third connecting pipe 260 to inflate the air volume 170.
  • the second solenoid valve 180 is opened.
  • the water vapor system 100 in addition to water vapor also includes a first restrictor 270 and a second restrictor 280 for limiting the rate at which the plenum 170 is deflated.
  • the first restrictor 270 is disposed on the first connecting pipe 240
  • the second restrictor 280 is disposed on the second connecting pipe 250. That is, when the gas in the air volume 170 passes through the first connecting pipe 240 and the second connecting pipe 250, respectively, after being restricted by the first restrictor 270 and the second restrictor 280, respectively, the gas enters the first monitoring pipe 150 and respectively.
  • the second monitoring pipe 160 is
  • the first restrictor 270 and the second restrictor 280 are disposed to control the rate at which the air volume 170 is deflated, so that the air flow is slow, thereby reducing the speed of water removal, increasing the time of removing water vapor, and reducing the airflow to the patient. The impact.
  • the first restrictor 270 is a gas barrier or a throttle valve.
  • the second restrictor 280 is a gas barrier or a throttle valve.
  • the pressure sensor 190 is disposed on the first monitoring conduit 150 or the second monitoring conduit 160.
  • the pressure sensor 190 is used to detect the air pressure value in the differential pressure generating device 120. Further, the pressure sensor 190 is located between the first connecting pipe 240 and the differential pressure flow sensor 140; or the pressure sensor 190 is located between the second connecting pipe 250 and the differential pressure flow sensor 140. Specifically in the illustrated embodiment, the pressure sensor 190 is disposed on the first monitoring conduit 160 and the pressure sensor 190 is located between the first connecting conduit 250 and the differential pressure flow sensor 140.
  • the circuit control unit controls the circuitry of the entire ventilator and processes the electrical signals.
  • the circuit control unit is electrically connected to the differential pressure flow sensor 140, the first electromagnetic valve 130, the second electromagnetic valve 180, and the pressure sensor 190.
  • the circuit control unit controls opening and closing of the first solenoid valve 130 and the second solenoid valve 180.
  • the circuit control unit controls the opening and closing of the first solenoid valve 130 in accordance with the patient's exhalation and inhalation. For example, by terminating a circuit control unit with an expiratory time and an inspiratory time that match the patient, then controlling the first solenoid valve 130 to close during the inspiratory time, the first solenoid valve 130 is controlled to open during the exhalation time.
  • the circuit control unit is provided with a preset air pressure value that is compared with the air pressure value detected by the pressure sensor 190. When the air pressure value detected by the pressure sensor 190 reaches the preset air pressure value, the circuit control unit controls the second electromagnetic valve 180 to be closed. The air source device 110 stops inflating the air volume 170.
  • the circuit control unit controls the second solenoid valve 180 to be opened, and the first solenoid valve 130 is closed; when the patient exhales, the circuit control unit controls the first solenoid valve 130 to be opened, and at this time, the air volume 170
  • the gas in the gas container 170 enters the first monitoring pipe 150 and the second monitoring pipe 160 through the first connecting pipe 240 and the second connecting pipe 250, respectively, and then flows out of the gas outlet pipe 124 through the differential pressure generating device 120.
  • the circuit control unit is also electrically connected to both the third electromagnetic valve 220 and the fourth electromagnetic valve 230.
  • the air source device 110 is also electrically connected to the circuit control unit.
  • the circuit control unit controls the second solenoid valve 180 to open, the air source device 110 supplies air to the patient, and the gas supplied from the air source device 110 is supplied to the patient via the respiratory tube 122 via the differential pressure generating device 120.
  • the air source device 110 supplies air to the air volume 170 through the third connecting duct 260, that is, inflates the air volume 170.
  • the second solenoid valve 180 is closed.
  • the first solenoid valve 130 When the patient exhales, the first solenoid valve 130 is opened, and at the same time, due to the patient exhaling, the gas exhaled by the patient flows from the air outlet duct 124 to the outside through the differential pressure generating device 120, so that the air pressure value in the differential pressure generating device 120 becomes small, when the difference is made.
  • the air pressure value in the pressure generating device 120 is less than the air pressure value in the air volume 170, the air volume 170 begins to deflate, and the gas in the air volume 170 enters the first monitoring pipe 150 through the first connecting pipe 240 and the second connecting pipe 250 and The second monitoring pipe 160 is then flowed from the air outlet pipe 124 to the outside through the differential pressure generating device 120.
  • both the first monitoring conduit 150 and the second monitoring conduit 160 have a flow of air to the differential pressure generating device 120, preventing the gas exhaled by the patient from entering the first monitoring conduit 150.
  • the second monitoring pipe 160 and also prevents the condensed water in the differential pressure generating device 120 from entering the first monitoring pipe 150 and the second monitoring pipe 160, effectively avoiding the first monitoring pipe 150 and the second monitoring pipe
  • the problem of condensed water is formed in 160.
  • the gas discharged from the air volume 170 passes through the first connecting pipe 240 and the second connecting pipe 250.
  • the first monitoring pipe 150 and the second monitoring pipe 160 are respectively entered.
  • the patient inhales through the breathing duct 122.
  • the first electromagnetic valve 130 is closed, the second electromagnetic valve 180 is opened, and the air source device 110 supplies a gas source to the patient.
  • the air source provided by the device 110 is delivered to the patient through the differential pressure generating device 120.
  • the air source device 110 since the second electromagnetic valve 180 is opened, the air source device 110 also enters the air volume 170 through the third connecting pipe 260, and the air supply 170 is provided.
  • the second electromagnetic valve 180 When the air pressure value in the differential pressure generating device 120 reaches the preset air pressure value, the second electromagnetic valve 180 is closed; when the patient exhales, the first electromagnetic valve 130 is opened, and the air outlet pipe 124 communicates with the outside, as the patient exhales
  • the airflow in the differential pressure generating device 120 flows from the air outlet duct 124 to the outside, so that the air pressure value in the differential pressure generating device 120 becomes small, and when the air pressure value in the differential pressure generating device 120 is smaller than the air pressure value in the air volume 170, the air volume 170 begins to deflate, and the gas in the air volume 170 passes through the first connecting pipe 240 and the second connecting pipe 250, and then flows through the first monitoring pipe 150 and the second monitoring pipe 160 to the differential pressure generating device 120, that is, respectively.
  • a flow of the monitoring conduit 150 to the differential pressure generating device 120 and an air flow from the second monitoring conduit 160 to the differential pressure generating device 120 prevent the flow of air in the differential pressure generating device 120 from flowing to the first monitoring conduit 150 and the second monitoring conduit 160. That is, the process of removing water is the same as the patient exhaling, so as to prevent the water vapor in the exhaled by the patient and the condensed water in the differential pressure generating device 120 from entering the first monitoring pipe 150 and the second monitoring pipe 160, effectively avoiding
  • the problem of forming condensed water in the first monitoring pipe 150 and the second monitoring pipe 160 is compared with the conventional method of removing water vapor by heating and the method of blowing the condensed water by using a high-pressure high-speed air stream.
  • the system's water removal process is adapted to the patient's breathing process, and the patient's breathing control is used, which is more safe and reliable.
  • the third electromagnetic valve 220 is disposed between the second connecting pipe 250 and the differential pressure flow sensor 140
  • the fourth electromagnetic valve 230 is disposed between the first connecting pipe 240 and the differential pressure flow sensor 140 to prevent moisture from entering the first
  • the third solenoid valve 220 and the fourth solenoid valve 230 function to protect the third solenoid valve 220 and the fourth solenoid valve 230.
  • the pressure sensor 190 is disposed between the first connecting pipe 240 and the differential pressure flow sensor 140, or is disposed between the second connecting pipe 250 and the differential pressure flow sensor 140, and can prevent moisture from entering the pressure sensor 190. It functions to protect the pressure sensor 190.
  • the ventilator described above contains the above-described gas path system 100 for removing moisture, the ventilator has a longer life and is more secure.

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

Abstract

L'invention concerne un ventilateur et son système de circuit d'air d'élimination d'humidité (100). Une première électrovanne (130) du système de circuit d'air d'élimination d'humidité (100) est montée sur une conduite de sortie d'air (124) reliée à l'extérieur ; les deux extrémités d'une première conduite de surveillance (150) et d'une seconde conduite de surveillance (160) sont respectivement en communication avec un appareil de génération de pression différentielle (120) utilisé pour produire une pression de flux d'air différentielle et un capteur de débit de type pression différentielle (140) ; un condensateur d'air (170) est en communication avec la première conduite de surveillance (150) au moyen d'une première conduite de liaison (240), est en communication avec la seconde conduite de surveillance (160) au moyen d'une deuxième conduite de liaison (250), et est en communication avec un appareil d'alimentation en air (110) au moyen d'une troisième conduite de liaison (260) ; une seconde électrovanne (180) est installée sur la troisième conduite de liaison (260) ; lorsque la valeur de pression d'air détectée par un capteur de pression (190) atteint une valeur de pression d'air prédéfinie, la seconde électrovanne (180) se ferme ; lorsqu'un patient expire, le condensateur d'air (170) évacue l'air pour empêcher l'air expiré par le patient de s'écouler vers la première conduite de surveillance (150) et la seconde conduite de surveillance (160). Le présent circuit d'air d'élimination d'humidité (100) peut empêcher efficacement le problème de condensation se formant dans les conduites de surveillance, et le processus d'élimination d'humidité est plus sûr.
PCT/CN2015/099925 2015-04-03 2015-12-30 Ventilateur et son système de circuit d'air d'élimination d'humidité WO2016155392A1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
CN201510158968.1A CN104784792B (zh) 2015-04-03 2015-04-03 呼吸机及其除水汽的气路系统
CN201510158968.1 2015-04-03

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WO2016155392A1 true WO2016155392A1 (fr) 2016-10-06

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Families Citing this family (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN104784792B (zh) * 2015-04-03 2017-05-17 深圳市科曼医疗设备有限公司 呼吸机及其除水汽的气路系统
CN109821120A (zh) * 2019-02-25 2019-05-31 深圳融昕医疗科技有限公司 吹扫方法、系统及具有该系统的呼吸机
CN110681013A (zh) * 2019-10-23 2020-01-14 深圳市科曼医疗设备有限公司 非线性气阻、冲洗模块及呼吸机
CN113069660B (zh) * 2021-03-23 2023-03-14 淄博泰雷兹电子有限公司 呼吸机管道环境自动控制系统
CN113296556B (zh) * 2021-06-29 2024-07-23 东莞市正文机械有限公司 一种自动灌气智能控制系统及方法

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US4971052A (en) * 1988-07-26 1990-11-20 Racal Safety Limited Breathing apparatus
CN103083775A (zh) * 2011-10-31 2013-05-08 北京谊安医疗系统股份有限公司 呼气阀、呼吸机及呼气阀的加热方法
CN103893863A (zh) * 2012-12-26 2014-07-02 北京谊安医疗系统股份有限公司 压差式流量传感器积水处理装置及具有该装置的呼吸机
CN104258491A (zh) * 2014-09-03 2015-01-07 南京舒普思达医疗设备有限公司 一种呼吸机采样管除水方法和装置
CN104784792A (zh) * 2015-04-03 2015-07-22 深圳市科曼医疗设备有限公司 呼吸机及其除水汽的气路系统

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CN203710495U (zh) * 2014-01-02 2014-07-16 深圳市普博科技有限公司 一种呼吸机流量传感器的除水、除尘装置

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Publication number Priority date Publication date Assignee Title
US4971052A (en) * 1988-07-26 1990-11-20 Racal Safety Limited Breathing apparatus
CN103083775A (zh) * 2011-10-31 2013-05-08 北京谊安医疗系统股份有限公司 呼气阀、呼吸机及呼气阀的加热方法
CN103893863A (zh) * 2012-12-26 2014-07-02 北京谊安医疗系统股份有限公司 压差式流量传感器积水处理装置及具有该装置的呼吸机
CN104258491A (zh) * 2014-09-03 2015-01-07 南京舒普思达医疗设备有限公司 一种呼吸机采样管除水方法和装置
CN104784792A (zh) * 2015-04-03 2015-07-22 深圳市科曼医疗设备有限公司 呼吸机及其除水汽的气路系统

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CN104784792B (zh) 2017-05-17

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