WO2018001413A1 - Simulateur de poumons - Google Patents

Simulateur de poumons Download PDF

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Publication number
WO2018001413A1
WO2018001413A1 PCT/DE2017/100525 DE2017100525W WO2018001413A1 WO 2018001413 A1 WO2018001413 A1 WO 2018001413A1 DE 2017100525 W DE2017100525 W DE 2017100525W WO 2018001413 A1 WO2018001413 A1 WO 2018001413A1
Authority
WO
WIPO (PCT)
Prior art keywords
compliance
resistance element
lung
pneumatic
lung simulator
Prior art date
Application number
PCT/DE2017/100525
Other languages
German (de)
English (en)
Inventor
Peter Schaller
Original Assignee
Peter Schaller
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Peter Schaller filed Critical Peter Schaller
Priority to CN201780040500.XA priority Critical patent/CN109478380A/zh
Priority to EP17745972.4A priority patent/EP3479369A1/fr
Publication of WO2018001413A1 publication Critical patent/WO2018001413A1/fr

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Classifications

    • G—PHYSICS
    • G09—EDUCATION; CRYPTOGRAPHY; DISPLAY; ADVERTISING; SEALS
    • G09B—EDUCATIONAL OR DEMONSTRATION APPLIANCES; APPLIANCES FOR TEACHING, OR COMMUNICATING WITH, THE BLIND, DEAF OR MUTE; MODELS; PLANETARIA; GLOBES; MAPS; DIAGRAMS
    • G09B23/00—Models for scientific, medical, or mathematical purposes, e.g. full-sized devices for demonstration purposes
    • G09B23/28—Models for scientific, medical, or mathematical purposes, e.g. full-sized devices for demonstration purposes for medicine
    • G09B23/288—Models for scientific, medical, or mathematical purposes, e.g. full-sized devices for demonstration purposes for medicine for artificial respiration or heart massage

Definitions

  • the invention relates to a device for simulating a z. B. human lung and is particularly applicable in the field of educational tools in medicine.
  • the lungs serve the gas exchange, ie the supply of oxygen to the blood and the removal of C02 produced by the metabolism.
  • the lung is divided symmetrically into two lung halves. Each lung has its own bronchial tree and alveolar area. The inhaled respiratory gas flows through the trachea across the two main bronchi into both halves of the lung.
  • the bronchi represent a flow resistance called resistance
  • the alveolar region in combination with the respiratory musculature has elastic properties described by the term compliance.
  • stretching forces are exerted on the alveoli by the respiratory muscles. This force is called the respiratory drive.
  • a model of respiratory mechanics in the simplest case assumes that both halves of the lung are grouped into a compartment characterized by a single resistance, a single compliance, and a single respiratory drive. Such a model is called a one-compartment lung model.
  • a two-compartment lung model applies this model to each lung.
  • the actual behavior of the respiratory mechanical properties of the lung is much better describable.
  • DE 10 2010 027 436 B3 describes a lung simulator that realizes a single-compartment lung model. Respiratory tube and airway resistance are realized as pneumatic resistances.
  • the compliance and the respiratory drive are generated by a piston-cylinder system in conjunction with a linear drive in that the linear drive on the piston exerts such a position-dependent counterforce that leads to the desired elastic behavior.
  • compliance breathing drive system consist of either a piston-cylinder system or a bellows system, wherein either the piston or the movable end plate of the bellows are moved by a linear drive.
  • the bellows solution has the advantage of absolute leak-free, but the disadvantage that as a result of the deflection of the folds, the compliance is not as well defined as in a piston-cylinder system.
  • intubation simulators that simulate a trachea in which the physician, endoscopically assisted, learns to insert a breathing tube into the trachea. This is especially important when it comes to the intubation of double-lumen tubes, the ends of which must be inserted into each main bronchus. Such intubation, which is difficult to perform, is needed for frequently used single-sided ventilation. Some of these intubation simulators have one quite simple lung simulation, but not about the comfortable analysis possibilities by a computer.
  • intubation simulator and lung simulator are usually designed as two different devices.
  • the prior art does not allow true two-compartment simulation, which is a requirement for double-lumen intubation and single-face ventilation.
  • the object of the invention is to provide a lung simulator which permits both intubation simulation with double-lumen tubes and lung simulation on the basis of a true physical two-compartment lung model and which offers complex analysis possibilities via an external or internal computer should.
  • the lung simulator should be light, easy to transport and, if possible, still approved as carry-on luggage in the aircraft.
  • Essential to the invention is that a two-compartment model of the lung is achieved by the lung model has a trachea tube, which branches at its output into two narrower bronchial tubes. From each bronchial tube there is a pneumatic connection to one resistance-compliance respiratory drive system each. The entrance of the tachometer tube is pneumatically connected to an intubation port (i.e., the intubation port) through which the ventilator tube is inserted.
  • an intubation port i.e., the intubation port
  • the trachea tube with the two bronchial tubes mechanically simulates a real physical trachea with the two main bronchi. This is easily possible via 3D printing of CAD data of a real trachea. This has the advantage that the intubation usually performed with endoscopic support can be practiced under largely real circumstances.
  • the trachea tube and the bronchial tubes may also be formed by simple tubes or tubes.
  • Resistance compliance breathing drive systems each consist of a pneumatic resistance element and a compliance breathing drive system. They are preferably structurally identical for both compartments, but may also be designed differently.
  • the resistance is formed by a pneumatic resistance element, which is variable in its value.
  • the resistance is formed by a variable pneumatic resistance element whose hydraulic diameter can be changed either manually or via a drive.
  • a solution consists in a pneumatic resistance element, which is constructed as follows:
  • a conical inner body is arranged axially aligned in a conical tube. Both parts have the same conicity and the inner body is axially displaceable relative to the tube. Both parts form an annular gap to each other, whose size, and thus also its hydraulic diameter, is dependent on the axial position of the inner cone to the tube.
  • the flow resistance is a function of annular gap width and annular gap length.
  • the axial displacement of the inner cone to the tube can be done manually, but preferably electric motor, z. B. by means of a small linear drive, which can be adjusted by a path control loop for the position of the inner cone to the pipe a defined distance, which results in a defined Resistance.
  • a variable in value pneumatic resistance element is that a system of gaps is formed by thin plates, each plate to the other at the lateral periphery by an elastic material is kept at a distance. As a result, the free gap surface can be flowed through. If one exerts a force on the outer plates, the plate spacing and, in turn, the hydraulic diameter of this gap system is reduced, which leads to a change in the flow resistance.
  • the change in the gap distance can be done either manually or by motor gear.
  • the first pneumatic resistance element is pneumatically connected to the outlet of the first bronchial tube and the second pneumatic resistance element is pneumatically connected to the outlet of the second bronchial tube.
  • the compliance-breathing drive system can be formed in a known manner either by a piston-cylinder system or a bellows system, on which a force is applied via a linear drive.
  • the linear drive acts on the piston and in the case of the bellows system on the movable end plate of the bellows.
  • the inlet of the first compliance breathing system is pneumatically connected to the outlet of the first pneumatic resistance element and the inlet of the second compliance breathing system is connected to the outlet of the second pneumatic resistance element.
  • the drive units of the compliance breathing drive systems and, if driven by an electric motor, the flow resistances require a power supply and one motor drive each.
  • the lung simulator comprises a central control, which coordinates the interaction of all units.
  • volume flow V on the route from the exit of the first bronchial tube to the first compliance breathing drive system and the output of the second bronchial tube to the second compliance breathing drive system can be carried out in a known manner by measurement by means of volume flow sensor at the appropriate place in this track will be installed. Another possibility is the volume flow by evaluating the piston movement in the respective
  • Vz is the cylinder volume
  • pz the cylinder pressure in the respective piston-cylinder system
  • pO the atmospheric air pressure
  • the pressures within the lung simulator are determined by pressure sensors. In this case, at least two pressure sensors are needed, the
  • the outputs of the pressure sensors are electrically connected to the inputs of the central controller.
  • the entire intelligence of the device is programmatically in a computer, z. B. a PC / laptop, which allows communication with the operator via a graphical user interface (GUI).
  • GUI graphical user interface
  • the computer also takes over the control of the central controller and evaluates its output signals by means of complex algorithms and displays the results in numerical and graphic form.
  • the linear drive of the respective compliance breathing drive system is controlled by a drive control.
  • This drive control receives the control signals from the central controller. At the same time the drive control supplies signals, position, speed, power to the central control.
  • the housing of the lung simulator is divided according to the invention into a front part and a back part.
  • the front part can, for. B. by means of hinges, be connected at the lower end to the back so that it can be opened against the back, with preferably the Aufklappwinkel is limited to 90 °.
  • the facial model • a physical replica of the larynx and another tube; or • a physical replica of the larynx and a physical replica of the oral cavity, including the mouth, preferably as a three-dimensional replica of a human face with the mouth open (hereafter called the facial model).
  • the trachea tube and its different connection options lie horizontal to the intubation opening in the position in which the physician intubates.
  • the piston-cylinder system is arranged vertically, whereby a disturbing friction between the piston and cylinder is largely reduced.
  • the front part does not need to be unfolded.
  • the ventilator can be introduced into the front part of an opening to which a second input of the trachea tube is pneumatically connected. The doctor can use this opening to insert a breathing tube into the two bronchial tubes just before the branching.
  • a tubular linear motor is used as a linear drive, which exerts the force directly on the piston of the piston-cylinder system or the bellows, without further gearbox.
  • a telescopic tube may be provided, whose extension length is variable, and which can be pulled out during operation of the device and pushed together in the other case.
  • removable sleeves may be provided, which can be used prior to operation of the device on z. B. closable openings of the housing, from which the rotor bars emerge during operation, are plugged.
  • the lung simulator according to the invention represents a two-compartment lung model
  • two such telescopic tubes or sleeves are needed.
  • these can be connected to the, the linear motor remote end portion by a crossbar, which also serves as a carrying handle.
  • the telescopic tubes are z. B. locked in a known manner by laterally projecting bolts, which is possible both for the pulled out and the pushed-in state.
  • This solution has the advantage that the housing can be kept small for transport, but in operation by pulling out of the telescopic tubes or attaching the sleeves of the required space for the movement of the rotor bar is given.
  • the device has an extendable carrying handle.
  • the weight of the lung simulator is not insignificant. In order to transport it better, at the back of the housing z. B. be mounted two rollers. In conjunction with the pull-out handle, the device thus resembles a trolley from its transport capability. This is a very cheap, weight and cost saving solution.
  • vibration-sensitive parts of the lung simulator are preferably arranged vibration-damped within the housing.
  • a particularly favorable embodiment of the invention provides that the front part and the rear part of the housing are connected to each other via a zipper.
  • FIG. 1 shows a schematic representation of the functional interaction of all components of the lung simulator
  • FIG. 2 shows a schematic representation of the most important pneumatic components of the lung model
  • FIG. 3 is a schematic representation of the compliance-breath drive system
  • FIG. 4 shows a schematic representation of the housing with facial model.
  • FIG. 1 shows that the ventilation tube 16 is introduced into the trachea tube 1 via the intubation opening 1 .1.
  • the input of the ventilation tube 16 is connected to the Y-piece 15 of the ventilator.
  • the trachea tube 1 branches into the bronchial tube 1 .2 and the bronchial tube 1.3.
  • a pneumatic connection to the pneumatic resistance element 2, which is variable in its value.
  • the output of the pneumatic resistance element 2 is connected to the input of the compliance breathing system 4.
  • This consists of a cylinder 4.1 and a piston 4.2, which is mechanically connected via a rotor bar 4.4 with the linear drive 4.3.
  • the control of the linear drive 4.3 is performed by the drive control 9, which in turn is connected to the central controller 8 via a CAN bus in combination.
  • the central controller 8 is connected to an external computer 1 1 via a data connection 12.
  • the power supply for the entire system is provided by a power supply 7.
  • the pneumatic resistance element 2 gives its information about its switching position via a data line to the central controller 8.
  • a pressure sensor 6.1 determines the pressure at the inlet of the compliance breathing drive system 4.
  • the second pressure sensor 6.2 determines the pressure at the input of the compliance breathing system 5.
  • the third pressure sensor 6.3 determines the pressure at the end of the trachea tube 1 and the fourth Pressure sensor 6.4 determines the pressure on the Y-piece 15.
  • the function of the other lung half represented by the pneumatic resistance element 3, the compliance breathing drive system 5 and the drive control 10, is identical to that of the first lung half and therefore will not be further described.
  • Figure 2 shows the pneumatic scheme for both lung halves, which are symmetrical. In the following, only one lung half will be described.
  • the output of the bronchial tube 1 .2 is connected to the input of the pneumatic resistance element 2.
  • a hose 2.5 establishes the pneumatic connection to the cylinder 4.1 of the compliance respiratory drive system 4.
  • FIG. 3 shows the compliance breathing drive system 4, which is identical to the compliance breathing drive system 5.
  • the linear drive 4.3 is mechanically connected to the piston 4.2 via its rotor rod 4.4. This moves inside the cylinder 4.1. It can be seen how the rotor bar 4.4 extends upwards out of the stator of the linear drive 4.3.
  • Figure 4 shows the housing 13, consisting of the front part 13.1 and the rear part 13.2, in which all components are structurally housed.
  • the face model 14 is arranged, the mouth opening with the
  • Tracheairohr 1 is pneumatically connected. From the rear part 13.2 protrude both telescopic tubes 17.1 and 17.2 out, which are connected at their end by a carrying handle 17.3. The transverse pins required for the locking of the telescopic tubes 17.1 and 17.2 are not shown.
  • the power supply 7, central control 8 and the drive controls 9 and 10 are arranged within the rear part 13.2.
  • the rear part 13.2 contains at its lower end on both sides each a roller 18th

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  • Engineering & Computer Science (AREA)
  • General Physics & Mathematics (AREA)
  • Health & Medical Sciences (AREA)
  • Physics & Mathematics (AREA)
  • Computational Mathematics (AREA)
  • Mathematical Optimization (AREA)
  • Medical Informatics (AREA)
  • Medicinal Chemistry (AREA)
  • Chemical & Material Sciences (AREA)
  • Algebra (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Cardiology (AREA)
  • Mathematical Analysis (AREA)
  • General Health & Medical Sciences (AREA)
  • Mathematical Physics (AREA)
  • Pure & Applied Mathematics (AREA)
  • Business, Economics & Management (AREA)
  • Educational Administration (AREA)
  • Educational Technology (AREA)
  • Theoretical Computer Science (AREA)
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Abstract

L'invention concerne un simulateur de poumons qui peut être employé aussi bien en tant que simulateur d'intubation qu'en tant que simulateur de respiration artificielle. Il reproduit la mécanique de respiration d'un système réel à deux compartiments et il est parfaitement approprié pour l'intubation à chambre double et la respiration artificielle unilatérale.
PCT/DE2017/100525 2016-07-01 2017-06-21 Simulateur de poumons WO2018001413A1 (fr)

Priority Applications (2)

Application Number Priority Date Filing Date Title
CN201780040500.XA CN109478380A (zh) 2016-07-01 2017-06-21 肺模拟器
EP17745972.4A EP3479369A1 (fr) 2016-07-01 2017-06-21 Simulateur de poumons

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
DE102016112073.1 2016-07-01
DE102016112073.1A DE102016112073A1 (de) 2016-07-01 2016-07-01 Lungensimulator

Publications (1)

Publication Number Publication Date
WO2018001413A1 true WO2018001413A1 (fr) 2018-01-04

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ID=59501123

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/DE2017/100525 WO2018001413A1 (fr) 2016-07-01 2017-06-21 Simulateur de poumons

Country Status (4)

Country Link
EP (1) EP3479369A1 (fr)
CN (1) CN109478380A (fr)
DE (1) DE102016112073A1 (fr)
WO (1) WO2018001413A1 (fr)

Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN113920838A (zh) * 2021-10-26 2022-01-11 北京航空航天大学 一种电子式主动模拟肺
WO2022264045A1 (fr) * 2021-06-15 2022-12-22 Fisher & Paykel Healthcare Limited Système d'entraînement par simulation de patient pour une assistance respiratoire ou un appareil respiratoire

Families Citing this family (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN113643601B (zh) * 2021-08-04 2023-04-18 康莉娜 一种支气管体位引流方法

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DE3049583C2 (de) 1980-12-31 1984-08-16 Obermayer, Anton, Dipl.-Ing., 7954 Bad Wurzach Atmungsgerät für die technische Ausbildung von Ärzten, Schwestern und Pflegepersonal
WO1997012351A1 (fr) 1995-09-29 1997-04-03 Ihc Health Services, Inc. Simulateur de poumons asservi et procede de commande associe
DE19714684A1 (de) * 1997-04-09 1998-10-15 Medecontrol Electronics Gmbh Vorrichtung zur Prüfung von Beatmungs- und Narkosegeräten
US6296490B1 (en) 2000-08-04 2001-10-02 O-Two Systems International Inc. Ventilation training analyzer manikin
PL183237B1 (pl) 1997-11-28 2002-06-28 Inst Biocybernetyki I Inzynier Symulator tłokowy własności mechanicznych płuc
US6874501B1 (en) 2002-12-06 2005-04-05 Robert H. Estetter Lung simulator
DE102010027436B3 (de) 2010-07-09 2011-07-21 Schaller, Peter, Dr., 01326 Lungensimulator
US20110250578A1 (en) * 2010-04-13 2011-10-13 Northern Alberta Institute Of Technology Ventilator test lung and trigger assembly
WO2012155283A1 (fr) 2011-05-16 2012-11-22 Organis Gmbh Modèle physique de poumon permettant de simuler la fonction de cet organe selon qu'il est sain ou malade
WO2013143933A1 (fr) * 2012-03-28 2013-10-03 Laerdal Global Health As Simulateur de poumons
CN104998328A (zh) * 2015-07-08 2015-10-28 湖南明康中锦医疗科技发展有限公司 模拟肺装置及模拟肺装置运行系统

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US8517740B2 (en) * 2011-02-18 2013-08-27 Gaumard Scientific Company, Inc. Lung compliance simulation system and associated methods
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CN203351112U (zh) * 2013-05-27 2013-12-18 周元桃 多功能肺模拟器
CN204759879U (zh) * 2015-06-15 2015-11-11 天津市圣宁生物科技有限公司 一种新型模拟呼吸装置
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* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE3049583C2 (de) 1980-12-31 1984-08-16 Obermayer, Anton, Dipl.-Ing., 7954 Bad Wurzach Atmungsgerät für die technische Ausbildung von Ärzten, Schwestern und Pflegepersonal
WO1997012351A1 (fr) 1995-09-29 1997-04-03 Ihc Health Services, Inc. Simulateur de poumons asservi et procede de commande associe
DE19714684A1 (de) * 1997-04-09 1998-10-15 Medecontrol Electronics Gmbh Vorrichtung zur Prüfung von Beatmungs- und Narkosegeräten
PL183237B1 (pl) 1997-11-28 2002-06-28 Inst Biocybernetyki I Inzynier Symulator tłokowy własności mechanicznych płuc
US6296490B1 (en) 2000-08-04 2001-10-02 O-Two Systems International Inc. Ventilation training analyzer manikin
US6874501B1 (en) 2002-12-06 2005-04-05 Robert H. Estetter Lung simulator
US20110250578A1 (en) * 2010-04-13 2011-10-13 Northern Alberta Institute Of Technology Ventilator test lung and trigger assembly
DE102010027436B3 (de) 2010-07-09 2011-07-21 Schaller, Peter, Dr., 01326 Lungensimulator
WO2012155283A1 (fr) 2011-05-16 2012-11-22 Organis Gmbh Modèle physique de poumon permettant de simuler la fonction de cet organe selon qu'il est sain ou malade
WO2013143933A1 (fr) * 2012-03-28 2013-10-03 Laerdal Global Health As Simulateur de poumons
CN104998328A (zh) * 2015-07-08 2015-10-28 湖南明康中锦医疗科技发展有限公司 模拟肺装置及模拟肺装置运行系统

Cited By (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2022264045A1 (fr) * 2021-06-15 2022-12-22 Fisher & Paykel Healthcare Limited Système d'entraînement par simulation de patient pour une assistance respiratoire ou un appareil respiratoire
CN113920838A (zh) * 2021-10-26 2022-01-11 北京航空航天大学 一种电子式主动模拟肺
CN113920838B (zh) * 2021-10-26 2023-10-03 北京航空航天大学 一种电子式主动模拟肺

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Publication number Publication date
EP3479369A1 (fr) 2019-05-08
DE102016112073A1 (de) 2018-01-04
CN109478380A (zh) 2019-03-15

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