WO2021073614A1 - 一种气动心肺复苏按压装置 - Google Patents

一种气动心肺复苏按压装置 Download PDF

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WO2021073614A1
WO2021073614A1 PCT/CN2020/121608 CN2020121608W WO2021073614A1 WO 2021073614 A1 WO2021073614 A1 WO 2021073614A1 CN 2020121608 W CN2020121608 W CN 2020121608W WO 2021073614 A1 WO2021073614 A1 WO 2021073614A1
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cylinder
control valve
air
pneumatic
cardiopulmonary resuscitation
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PCT/CN2020/121608
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English (en)
French (fr)
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孔伟方
章军辉
方志庆
严跃明
方志平
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苏州尚领医疗科技有限公司
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Publication of WO2021073614A1 publication Critical patent/WO2021073614A1/zh

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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61H—PHYSICAL THERAPY APPARATUS, e.g. DEVICES FOR LOCATING OR STIMULATING REFLEX POINTS IN THE BODY; ARTIFICIAL RESPIRATION; MASSAGE; BATHING DEVICES FOR SPECIAL THERAPEUTIC OR HYGIENIC PURPOSES OR SPECIFIC PARTS OF THE BODY
    • A61H31/00—Artificial respiration or heart stimulation, e.g. heart massage
    • A61H31/004—Heart stimulation
    • A61H31/006—Power driven
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61H—PHYSICAL THERAPY APPARATUS, e.g. DEVICES FOR LOCATING OR STIMULATING REFLEX POINTS IN THE BODY; ARTIFICIAL RESPIRATION; MASSAGE; BATHING DEVICES FOR SPECIAL THERAPEUTIC OR HYGIENIC PURPOSES OR SPECIFIC PARTS OF THE BODY
    • A61H2201/00—Characteristics of apparatus not provided for in the preceding codes
    • A61H2201/12—Driving means
    • A61H2201/1238—Driving means with hydraulic or pneumatic drive
    • A61H2201/1246—Driving means with hydraulic or pneumatic drive by piston-cylinder systems

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  • the invention relates to the technical field of medical equipment, in particular to a pneumatic cardiopulmonary resuscitation pressing device.
  • Cardiopulmonary resuscitation compression device is one of the most commonly used and most important equipment in medical emergency.
  • the current compression devices are basically pneumatic, and the clinical effects of pneumatic compression devices are generally recognized, and they are the first-choice first-aid equipment for first aid in hospitals.
  • the technical problem to be solved by the present invention is to overcome the above-mentioned shortcomings of the existing pneumatic cardiopulmonary resuscitation compression device, and further provide a pneumatic cardiopulmonary resuscitation compression device that can eliminate the influence of tracheal air resistance or air source flow restriction on the depth of piston compression.
  • a pneumatic cardiopulmonary resuscitation pressing device comprising a cylinder and a buffer chamber, the buffer chamber is arranged close to the cylinder; the cylinder is provided with a piston, the ejection end of the piston is connected with a pressing head, the inlet of the cylinder
  • the air port is connected to the air supply port of the control valve.
  • the air inlet of the control valve is connected to an air source through an air inlet pipe.
  • the control valve is adapted to divert the gas in the air source to the cylinder to drive the air supply.
  • the piston is pushed downward, or the gas in the cylinder is discharged outward so that the piston rebounds and resets; an end of the intake pipe close to the control valve is provided with a bronchus, and the bronchus connects the intake pipe with The buffer cavity is turned on.
  • the buffer chamber is attached to the outer wall of the cylinder, and the bronchus is connected at a position of the buffer chamber close to the air inlet of the control valve.
  • the volume of the buffer chamber is greater than or equal to 3 times the volume of the cylinder.
  • a cylinder is sleeved on the outside of the cylinder, and the cylinder is arranged coaxially with the cylinder, both ends of the cylinder are closed, and there is a gap between the inner side of the cylinder and the outer side of the cylinder.
  • the space forms the buffer cavity.
  • the two ends of the buffer cavity are flush with the two ends of the cylinder.
  • a valve plate is provided at the upper end surface of the buffer chamber and the cylinder, and the control valve is installed on the valve plate.
  • control valve is a pneumatic control valve or an electric control valve.
  • control valve is controlled by a controller to perform opening and closing actions.
  • the pneumatic cardiopulmonary resuscitation compression device of the present invention not only solves the technical problem of insufficient inflation in the cylinder caused by tracheal air resistance or flow restriction that has plagued the pneumatic compression device for a long time, but also improves the clinical application environment of the pneumatic compression device so that it can be used in different air sources. In all cases, the clinical effect of the presser can be guaranteed.
  • FIG. 1 is a schematic diagram of the vertical half-section structure of the cylinder of the pneumatic cardiopulmonary resuscitation pressing device of the present invention
  • FIG. 2 is a schematic diagram of the horizontal projection structure of the cylinder and the buffer cavity of the pneumatic cardiopulmonary resuscitation pressing device of the present invention.
  • a pneumatic cardiopulmonary resuscitation pressing device includes a cylinder 1 and a buffer chamber 2.
  • the buffer chamber 2 is arranged close to the cylinder 1; the cylinder 1 is provided with a piston 3, and the piston 3 is ejected The end is connected with a pressing head 4, which moves up and down with the piston to perform a cardiopulmonary resuscitation pressing action.
  • the air inlet of the cylinder 1 is connected to the air supply port 51 of the control valve 5 through a pipeline.
  • the air inlet 52 of 5 is connected to the air source 7 through the air inlet pipe 6, and the control valve 5 is controlled by the controller 10 to perform opening and closing actions; the control valve 5 is suitable for guiding the gas in the air source 7 to
  • the cylinder 1 is used to drive the piston 3 to eject downward, or the control valve 5 is adapted to discharge the gas in the cylinder 1 through the exhaust port 53 to make the piston 3 rebound and reset;
  • a bronchus 8 is provided at one end of the air inlet pipe 6 close to the control valve 5, and the bronchus 8 connects the air inlet pipe with the buffer cavity 2.
  • the pneumatic cardiopulmonary resuscitation pressing device of the present invention provides a buffer chamber 2 close to the cylinder.
  • the buffer chamber 2 communicates with the intake pipe 6 through the bronchus 8, and the air source 7 first injects equal-pressure gas into the buffer chamber 2 to facilitate buffering.
  • the cavity assists the gas source to quickly replenish sufficient gas into the cylinder at the moment when the piston performs the downward pressure action, which overcomes the disadvantage that the gas pressure injected into the cylinder cannot meet the requirements caused by the air resistance of the gas supply pipe or the restriction of the gas source flow rate. , To ensure the rapid pressing action of the piston to meet the requirements of the predetermined pressing frequency and pressing depth.
  • the specific air supply method is as follows: in normal state, the air source supplies air to the air inlet 52 of the control valve through the air inlet pipe 6 and at the same time supplies air to the buffer chamber 2 through the bronchus 8; when the air inlet 52 of the control valve and the air supply port 51 lead When ventilating, the gas from the air source and the buffer chamber is simultaneously charged into the cylinder through the air supply port 51 of the control valve to push the piston downward to perform the pressing action; when the piston is pressed in place and starts to rebound, the control valve will open the air supply port 51 Connect with the exhaust port 52 and block the gas path between the intake port 52 and the air supply port 51 to return to normal air supply.
  • the gas in the cylinder is discharged to the atmosphere through the air supply port 51 and the exhaust port 53 With gas, the piston moves upward under the action of the chest cavity to rebound. In this way, the cardiopulmonary resuscitation pressing action is completed back and forth.
  • the pneumatic cardiopulmonary resuscitation pressing device switches the opening and closing states of the control valve at a certain frequency, so that the cylinder is inflated and deflated alternately.
  • the piston In the process of inflation, the piston is required to overcome the resistance of the thoracic cavity and move quickly. To achieve a good clinical effect, the piston movement of 50mm requires about 120ms. In an ideal state, if the gas source flow is large enough and the air resistance of the air pipe is small enough, the gas pressure supplied by the gas source into the cylinder is constant, and the piston can act according to the theoretical compression frequency and compression depth.
  • the air source of the pneumatic cardiopulmonary resuscitation compression device in actual use is generally a certain volume of air tank, the air pressure in the air tank will decrease with the consumption of the air source, which will gradually affect the air supply to the cylinder.
  • a buffer chamber is arranged as close as possible to the cylinder, so that when the pressure of the air source drops to a sufficient amount to inject gas into the cylinder, the cylinder can be directly supplemented with gas from the closer buffer chamber, and the air source (including the air pipe) The flow rate only needs to meet the average flow rate.
  • the air resistance effect of the intake pipe and the flow restriction effect of various valves on the intake pipe are eliminated.
  • a cylinder 9 is sleeved on the outer side of the cylinder 1, and the cylinder 9 is arranged coaxially with the cylinder 1, both ends of the cylinder 9 are closed, and the inner side of the cylinder 9 is connected to
  • the space between the outer sides of the cylinder 1 forms the buffer chamber 2, and the buffer chamber 2 has a substantially annular chamber structure.
  • the volume of the buffer chamber 2 is greater than or equal to 3 times the volume of the cylinder 1.
  • the pressure P2 at the intake port of the cylinder is basically 0.3 MPa when the cylinder is inflated.
  • the pressure drop is less, only about 10%, so it can meet the inflation requirements of the cylinder.
  • the buffer chamber As for the requirement that the buffer chamber be as close to the cylinder as possible, it is to reduce the air resistance of the gas path as much as possible, and the gas in the buffer chamber is determined according to the structure of the specific equipment, and it is not blindly required to be too large, which will make the entire equipment cumbersome.
  • the two ends of the buffer cavity 2 are flush with the two ends of the cylinder 1.
  • This arrangement makes the cylinder and the buffer cavity an integrated structure, which facilitates the movement of the piston.
  • a valve plate 11 may be provided on the upper end surface of the buffer chamber 2 and the cylinder 1.
  • the control valve 5 is installed on the valve plate, and the corresponding valve plate is engraved on the valve plate.
  • the pipeline or the air inlet and outlet ports are used to facilitate the control valve to control the gas inlet or exhaust channel.
  • control valve 5 is a pneumatically controlled valve or an electronically controlled valve, as long as the alternate charging and exhausting needs of the cylinder can be realized, and the specific form is not limited.
  • the invention not only solves the technical problem of insufficient inflation in the cylinder caused by tracheal air resistance or flow restriction that has plagued the pneumatic press for a long time, but also improves the clinical application environment of the pneumatic press, so that it can be used under different air sources.
  • the clinical effect of the compressor is guaranteed. Since the compression device is a device for rescuing patients in critical condition, the guarantee of its clinical effect cannot be measured by material benefits.
  • the shape of the buffer cavity and the structure of the cylinder and the cylinder provided in the above embodiments are only preferred solutions. Those skilled in the art should understand that under the guidance of the spirit and principles of the present invention, they are not limited to the above forms, and buffer cavities of other shapes can also be used. , And can be separated from the cylinder.
  • the above-mentioned specific embodiments are only detailed explanations of the technical solutions of the present invention. Any improvement or substitution based on the above-mentioned principle and spirit on the basis of the present invention should fall within the protection scope of the present invention.

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  • Health & Medical Sciences (AREA)
  • Cardiology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Emergency Medicine (AREA)
  • Pulmonology (AREA)
  • Epidemiology (AREA)
  • Pain & Pain Management (AREA)
  • Physical Education & Sports Medicine (AREA)
  • Rehabilitation Therapy (AREA)
  • Life Sciences & Earth Sciences (AREA)
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Abstract

一种气动心肺复苏按压装置，其包括气缸(1)和缓冲腔(2)，缓冲腔(2)靠近气缸(1)设置；气缸(1)内设置有活塞(3)，活塞(3)的顶出端连接有按压头(4)，气缸(1)的进气口连接控制阀(5)的供气口(51)，控制阀(5)的进气口(52)通过进气管(6)与气源(7)连接；进气管(6)靠近控制阀(5)的一端设置有支气管(8)，支气管(8)将进气管(6)与缓冲腔(2)导通。气动心肺复苏按压装置不仅解决了长期困扰气动按压器的因气管气阻或流量限制引发的气缸内充气不足的技术问题，且改善了气动按压器的临床适用环境，使得在不同气源的情况下都可以使按压器的临床效果得到保证。

Description

一种气动心肺复苏按压装置 技术领域
本发明涉及医疗设备技术领域，特别是涉及一种气动心肺复苏按压装置。
背景技术
心肺复苏按压装置是医疗急救最常用最重要的设备之一。目前的按压装置基本上以气动为主，气动类的按压器临床效果被普遍认可，是院内急救的首选急救设备。
目前的气动按压器普遍存在一个问题，并始终没得到有效的解决，也即由于连接气缸和气源的气管存在气阻，或者因为气源的流量限制，会使得气缸中活塞移动变慢，甚至在规定的按压频率时达不到规定的按压深度，进而严重影响临床急救效果。
发明内容
为此，本发明要解决的技术问题是克服现有气动心肺复苏按压装置存在的上述不足，进而提供一种能够消除气管气阻或气源流量限制对活塞按压深度影响的气动心肺复苏按压装置。
为实现上述目的，本发明采用以下技术方案：
一种气动心肺复苏按压装置，其包括气缸和缓冲腔，所述缓冲腔靠近所述气缸设置；所述气缸内设置有活塞，所述活塞的顶出端连接有按压头，所述气缸的进气口连接控制阀的供气口，所述控制阀的进气口通过进气管与气源连接，所述控制阀适于将所述气源内的气体导流至所述气缸内以驱动所述活塞向下顶出，或将所述气缸内的气体向 外排出以便所述活塞回弹复位；所述进气管靠近所述控制阀的一端设置有支气管，所述支气管将所述进气管与所述缓冲腔导通。
优选的，所述缓冲腔贴附在所述气缸外壁上设置，所述支气管连接在所述缓冲腔靠近所述控制阀进气口的位置。
优选的，所述缓冲腔的容积大于等于3倍所述气缸的容积。
优选的，所述气缸的外侧套设有筒体，所述筒体与所述气缸同轴设置，所述筒体的两端封闭，所述筒体的内侧与所述气缸的外侧之间的空间形成所述缓冲腔。
优选的，所述缓冲腔的两端与所述气缸的两端齐平。
优选的，所述缓冲腔、所述气缸的上端面处设置有阀板，所述控制阀安装在所述阀板上。
优选的，所述控制阀为气控阀或电控阀。
优选的，所述控制阀由控制器控制执行启闭动作。
本发明的有益效果：
本发明的气动心肺复苏按压装置不仅解决了长期困扰气动按压器的因气管气阻或流量限制引发的气缸内充气不足的技术问题，且改善了气动按压器的临床适用环境，使得在不同气源的情况下都可以使按压器的临床效果得到保证。
附图说明
为了使本发明的内容更容易被清楚的理解，下面结合附图，对本发明作进一步详细的说明，其中：
图1是本发明的气动心肺复苏按压装置气缸处的竖向半剖结构示意图；
图2是本发明的气动心肺复苏按压装置气缸与缓冲腔的水平投影结构示意图。
图中附图标记表示为：
1-气缸；2-缓冲腔；3-活塞；4-按压头；5-控制阀；51-供气口；52-进气口；53-排气口；6-进气管；7-气源；8-支气管；9-筒体；10-控制器；11-阀板。
具体实施方式
参见图1，一种气动心肺复苏按压装置，其包括气缸1和缓冲腔2，所述缓冲腔2靠近所述气缸1设置；所述气缸1内设置有活塞3，所述活塞3的顶出端连接有按压头4，所述按压头4随所述活塞上下运动以执行心肺复苏按压动作，所述气缸1的进气口通过管路连接控制阀5的供气口51，所述控制阀5的进气口52通过进气管6与气源7连接，所述控制阀5由控制器10控制执行启闭动作；所述控制阀5适于将所述气源7内的气体导流至所述气缸1内以驱动所述活塞3向下顶出，或所述控制阀5适于将所述气缸1内的气体通过排气口53向外排出以使所述活塞3回弹复位；所述进气管6靠近所述控制阀5的一端设置有支气管8，所述支气管8将所述进气管与所述缓冲腔2导通。本发明的气动心肺复苏按压装置通过在靠近气缸的位置设置缓冲腔2，该缓冲腔2通过支气管8与进气管6连通，气源7先向缓冲腔2内注入等压的气体，以便于缓冲腔在活塞执行下压动作的瞬间协助气源迅速向气缸内补入足量的气体，克服了因供气管气阻或气源流量限制而引发的注入气缸内的气体气压达不到要求的弊端，保证了活 塞的快速下压动作，以满足预定按压频率和按压深度的要求。具体供气方式为：常态时气源通过进气管6向控制阀的进气口52供气的同时通过支气管8向缓冲腔2供气；当控制阀的进气口52与供气口51导通时，气源和缓冲腔的气体同时通过控制阀的供气口51充入气缸内以推动活塞向下运动执行按压动作；当活塞按压到位后开始回弹时，控制阀将供气口51与排气口52导通，并阻断进气口52与供气口51之间的气路使回复常态供气，此时气缸内的气体通过供气口51和排气口53向大气排出气体，活塞在胸腔回弹作用下向上运动回复。如此往复完成心肺复苏按压动作。
气动心肺复苏按压装置按一定的频率切换控制阀的启闭状态，使得气缸交替进行充气、放气。在充气的过程中要求活塞克服胸腔的阻力快速移动。要取得好的临床效果，活塞移动50mm要求在120ms左右。理想状态下，如果气源流量足够大并且气管气阻足够小，那么气源向气缸内供入的气体气压是恒定的，活塞能够按照理论的按压频率和按压深度进行动作。但由于实际使用中的气动心肺复苏按压装置的气源一般为一定体积的储气罐，该储气罐内的气压会随着气源的消耗而降低，继而会逐渐影响到向气缸内供气。实验表明，传统的气动心肺复苏按压装置当气源流量为168升/每分钟，气源压力P1＝0.33MPa时，由于流量限制或气管气阻的存在，达到气缸充气口处的气压P2会降到0.2MPa或以下，这样就使得气缸活塞产生的压力变小而达不到要求的按压频率和深度。但由于心肺复苏按压过程中所需的大流量恒压供气时间很短暂(只有气缸下压时需要)，一次按压周期约600ms，其中充气过程只有120ms左右，所以平均流量并不需要很大。本发明通过在尽可能靠近气缸位置设置一个缓冲腔，以便于在气源压力下降到不能足量向气缸内注入气体时直接从较近的缓冲腔内向气缸补充气体，而气源(包括气管)的流量只要满足平均流量就可以了，此时 消除了进气管的气阻作用和进气管路上各处阀(如减压阀、稳压阀、限流阀等)的限流作用。
本实施例中，所述气缸1的外侧套设有筒体9，所述筒体9与所述气缸1同轴设置，所述筒体9的两端封闭，所述筒体9的内侧与所述气缸1的外侧之间的空间形成所述缓冲腔2，所述缓冲腔2基本呈环形的腔室结构。
为了保证缓冲腔能够达到效果较为理想的协助进气作用，所述缓冲腔2的容积大于等于3倍的气缸1的容积。据粗略估算，当缓冲腔的容积是气缸容积的5倍时，当气源的压力P1＝0.33MPa，流量为60升/分，那么气缸充气时其进气口处的压力P2基本在0.3MPa，压降较少，仅10％左右，因此能够满足气缸的充气要求。至于要求缓冲腔尽可能靠近气缸则是为了尽可能减少气路气阻，而缓冲腔的气体则根据具体设备的结构而定，并非一味要求过大，如此则会使整个设备笨重不堪。
本实施例中，所述缓冲腔2的两端与所述气缸1的两端齐平。这种设置方式使得气缸与缓冲腔的呈一体式结构，便于活塞的运动。
为了便于减少管路的设置，所述缓冲腔2、所述气缸1的上端面处可以设置一块阀板11，所述控制阀5安装在所述阀板上，在阀板上刻制出对应的管线或进出气口，以便于控制阀控制气体的进气通道或排气通道。
本实施例中，所述控制阀5为气控阀或电控阀，只要能够实现气缸的交替充气和排气需要即可，具体形式不限。
本发明不仅解决了长期困扰气动按压器的因气管气阻或流量限制引发的气缸内充气不足的技术问题，而且改善了气动按压器的临床 适用环境，使得在不同气源的情况下都可以使按压器的临床效果得到保证。由于按压器是抢救危急病人的器械，其临床效果的保障是无法用物质效益来衡量的。
上述实施例所提供的缓冲腔形状及其与气缸的构成仅为优选方案，本领域技术人员应该明白，在本发明的精神原理指引下，并不限于上述形式，还可以采用其他形状的缓冲腔，并且可以与气缸是分离的。上述具体实施方式只是对本发明的技术方案进行详细解释，凡是依据上述原理及精神在本发明基础上的改进、替代，都应在本发明的保护范围之内。

Claims (8)

  1. 一种气动心肺复苏按压装置，其特征在于：包括气缸和缓冲腔，所述缓冲腔靠近所述气缸设置；所述气缸内设置有活塞，所述活塞的顶出端连接有按压头，所述气缸的进气口连接控制阀的供气口，所述控制阀的进气口通过进气管与气源连接，所述控制阀适于将所述气源内的气体导流至所述气缸内以驱动所述活塞向下顶出，或将所述气缸内的气体向外排出以使所述活塞回弹复位；所述进气管靠近所述控制阀的一端设置有支气管，所述支气管将所述进气管与所述缓冲腔导通。
  2. 根据权利要求1所述的气动心肺复苏按压装置，其特征在于：所述缓冲腔贴附在所述气缸外壁上设置，所述支气管连接在所述缓冲腔靠近所述控制阀进气口的位置。
  3. 根据权利要求1或2所述的气动心肺复苏按压装置，其特征在于：所述缓冲腔的容积大于等于3倍所述气缸的容积。
  4. 根据权利要求3所述的气动心肺复苏按压装置，其特征在于：所述气缸的外侧套设有筒体，所述筒体与所述气缸同轴设置，所述筒体的两端封闭，所述筒体的内侧与所述气缸的外侧之间的空间形成所述缓冲腔。
  5. 根据权利要求4所述的气动心肺复苏按压装置，其特征在于：所述缓冲腔的两端与所述气缸的两端齐平。
  6. 根据权利要求4所述的气动心肺复苏按压装置，其特征在于：所述缓冲腔、所述气缸的上端面处设置有阀板，所述控制阀安装在所述阀板上。
  7. 根据权利要求1所述的气动心肺复苏按压装置，其特征在于： 所述控制阀为气控阀或电控阀。
  8. 根据权利要求1所述的气动心肺复苏按压装置，其特征在于：所述控制阀由控制器控制执行启闭动作。
PCT/CN2020/121608 2019-10-17 2020-10-16 一种气动心肺复苏按压装置 WO2021073614A1 (zh)

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