WO2004084980A1 - Verfahren und vorrichtung zur erkennung von leckagen bei einrichtungen zum zuführen von atemgasen - Google Patents
Verfahren und vorrichtung zur erkennung von leckagen bei einrichtungen zum zuführen von atemgasen Download PDFInfo
- Publication number
- WO2004084980A1 WO2004084980A1 PCT/DE2004/000607 DE2004000607W WO2004084980A1 WO 2004084980 A1 WO2004084980 A1 WO 2004084980A1 DE 2004000607 W DE2004000607 W DE 2004000607W WO 2004084980 A1 WO2004084980 A1 WO 2004084980A1
- Authority
- WO
- WIPO (PCT)
- Prior art keywords
- ventilation
- pressure
- volume flow
- breathing
- evaluation device
- Prior art date
Links
- 238000000034 method Methods 0.000 title claims abstract description 28
- 230000000241 respiratory effect Effects 0.000 title claims abstract description 12
- 230000029058 respiratory gaseous exchange Effects 0.000 claims abstract description 80
- 238000011156 evaluation Methods 0.000 claims abstract description 25
- 238000009423 ventilation Methods 0.000 claims description 57
- 239000007789 gas Substances 0.000 claims description 45
- 230000003434 inspiratory effect Effects 0.000 claims description 9
- 230000002269 spontaneous effect Effects 0.000 claims description 7
- 238000004364 calculation method Methods 0.000 claims description 6
- 238000001514 detection method Methods 0.000 claims description 5
- 238000005259 measurement Methods 0.000 claims description 3
- 238000010586 diagram Methods 0.000 description 13
- 230000007704 transition Effects 0.000 description 8
- 238000012546 transfer Methods 0.000 description 4
- 230000000694 effects Effects 0.000 description 3
- 210000004072 lung Anatomy 0.000 description 3
- 238000010276 construction Methods 0.000 description 2
- 230000009466 transformation Effects 0.000 description 2
- RZVAJINKPMORJF-UHFFFAOYSA-N Acetaminophen Chemical compound CC(=O)NC1=CC=C(O)C=C1 RZVAJINKPMORJF-UHFFFAOYSA-N 0.000 description 1
- 238000013459 approach Methods 0.000 description 1
- 208000029618 autoimmune pulmonary alveolar proteinosis Diseases 0.000 description 1
- 238000006243 chemical reaction Methods 0.000 description 1
- 230000008878 coupling Effects 0.000 description 1
- 238000010168 coupling process Methods 0.000 description 1
- 238000005859 coupling reaction Methods 0.000 description 1
- 238000013461 design Methods 0.000 description 1
- 238000011982 device technology Methods 0.000 description 1
- 238000012986 modification Methods 0.000 description 1
- 230000004048 modification Effects 0.000 description 1
- 238000005312 nonlinear dynamic Methods 0.000 description 1
- 230000000737 periodic effect Effects 0.000 description 1
- 238000012545 processing Methods 0.000 description 1
- 238000005070 sampling Methods 0.000 description 1
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
-
- 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
-
- 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
- A61M2016/0015—Accessories therefor, e.g. sensors, vibrators, negative pressure inhalation detectors
- A61M2016/0018—Accessories therefor, e.g. sensors, vibrators, negative pressure inhalation detectors electrical
- A61M2016/0021—Accessories therefor, e.g. sensors, vibrators, negative pressure inhalation detectors electrical with a proportional output signal, e.g. from a thermistor
-
- 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
- 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
- A61M2016/0042—Accessories therefor, e.g. sensors, vibrators, negative pressure with a flowmeter electrical in the expiratory 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
- A61M2205/15—Detection of leaks
-
- 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
- A61M2230/00—Measuring parameters of the user
- A61M2230/40—Respiratory characteristics
- A61M2230/46—Resistance or compliance of the lungs
Definitions
- the invention relates to a method for detecting leaks in ventilation devices, in which both a pressure of the breathing gas and a volume flow of the breathing gas are detected and an evaluation device is supplied.
- the invention further relates to a device for detecting leaks in respirators, which has both a device for detecting a pressure of the breathing gas and a device for detecting a volume flow of the breathing gas and in which the detection devices are connected to an evaluation device.
- the device When carrying out ventilation, different control methods are used for the respirators used.
- the device is mainly controlled with a pressure control, so that no defined one Flow volume per ventilation cycle is defined.
- a device control that is also fundamentally possible, taking into account a volume control of the flow volume assigned to a particular ventilation cycle, has proven to be problematic since leaks can occur in the immediate area of the ventilator, in the area of a breathing mask used and in the area of a connecting tube between the ventilator and the breathing mask. Further leaks can also occur in the area of the breathing mask on the patient's face. Leakage losses in the region of 50% of the flow volume generated by the ventilator frequently occur in the overall area of the ventilation device formed by these individual components.
- the object of the present invention is therefore to improve a method of the type mentioned in the introduction in such a way that improved device control is supported.
- This object is achieved in that the respiratory variables pressure and flow are recorded for at least two successive ventilation cycles by the evaluation device and that at least one control parameter with different signal amplitude is specified for the successive ventilation cycles and that from the resulting differences in pressure and flow for these ventilation cycles resistance, compliance and the leakage resistance are determined.
- Another object of the present invention is to construct a device of the type mentioned in the introduction in such a way that volume-controlled device control is supported.
- the evaluation device is designed to determine the respiratory variables pressure and flow, that there is a storage device for at least one value sequence pair of pressure and flow for a ventilation cycle and that for determining the difference courses of compliance and resistance for at least two successive ventilation cycles, at least one sequence of differences can be generated.
- the ventilator On the basis of the leakage determined, it is possible, in terms of device technology, to provide the ventilator with such an increased flow volume that, taking the leakage losses into account, an exactly defined useful flow volume is provided.
- an exactly defined useful flow volume is provided.
- different pressure levels are specified for the successive breaths.
- the first pressure level is chosen to be higher than the second pressure level.
- the first pressure level prefferably chosen lower than the second pressure level.
- the first volume flow is specified higher than the second volume flow.
- first volume flow is set lower than the second volume flow.
- a closed control loop can be provided by performing leakage compensation.
- the leakage compensation is carried out dynamically.
- the evaluation device determine the course of the spontaneous breathing.
- the evaluation device compensates for the effects of a spontaneous course on ventilation.
- a typical embodiment is defined by performing leak detection in an area between a ventilator and a patient.
- the measurements are only carried out during inspiratory phases of the ventilation cycles.
- At least one pressure sensor is connected to the evaluation device.
- a ventilation flow can be detected by connecting at least one volume flow sensor to the evaluation device.
- a compact device design is supported by the fact that at least one of the sensors is the one Breathing gas providing respirator is arranged facing.
- Improved measuring accuracy can be achieved by arranging one of the sensors facing a respiratory mask.
- an expiration valve is arranged facing the respiratory mask.
- a patient interface connected to the ventilator via the breathing gas hose is designed as an invasive device.
- a patient interface connected to the ventilator via the breathing gas hose is designed as a non-invasive device.
- An execution form for a signal generator is defined in that the evaluation device has an amplitude generator for a pressure which varies from ventilation cycle to ventilation cycle.
- the evaluation device has an amplitude generator for a volume flow that varies from ventilation cycle to ventilation cycle.
- exemplary embodiments of the invention are shown schematically in the drawings. Show it:
- FIG. 1 shows a block diagram of the technical equipment for Veit: - illustration of the essential technical components
- FIG. 6 is a block diagram of a modified device structure
- Fig. 14 shows another modified embodiment
- a ventilation device (1) has a driven blower (3). This drive takes place via a motor or another drive unit.
- the blower (3) is connected to a control valve (4), which has an adjusting device (6) and transforms a control voltage into an assigned valve position.
- a pressure sensor (8) and a volume flow sensor (9) are connected to a ventilator (7), which essentially consists of the blower (3) and the control valve (4).
- the volume flow sensor (9) is typically designed as a differential pressure sensor, the signal of which is transformed into an assigned volume flow.
- the respirator (7) is connected via a breathing gas hose (10) and an expiration valve (11) to a breathing mask (12) which can be positioned in the face area of a patient (13).
- the sensors (8, 9) are connected to an evaluation device (14), which in turn is connected to the actuating device (6).
- FIG. 2 shows an electrical equivalent circuit diagram which shows the function of the patient's lungs (13) and which is used in the area of the evaluation device (14) as a model for carrying out the calculations.
- a volume flow generated by a volume flow source (15) is fed to the parallel connection of two flow branches.
- One of the branches contains the series connection of the resistance (16) and the compliance (17) as well as a source of interference (18) which generates an additional volume flow and depicts a possible self-activity of the patient (13).
- the second flow branch contains a leakage resistance (19).
- the electrical equivalent circuit diagram of the airways according to FIG. 2 shows that the pressure p muH generated by the active breathing activity of a patient makes a contribution to the airway pressure p aw and thus to the flow into the lungs (V ' a "). So leakage identification must also consider p MUB if it is to succeed, to compensate for the leakage flow V 'L sufficiently.
- the equivalent circuit in FIG. 2 shows the following relationship in the image area of the Laplace transformation for the airway pressure p aw and the inspiratory flow V ' ⁇ nBp :
- ⁇ p aw (s) ⁇ V '. nBp (s) (1 + sRC) R L / (1 + s (R + R L ) C)
- the inversion of the first equation is used to reconstruct the course of p mUB .
- the identified estimated values are used as parameters and the measured values of an inspiration phase are calculated.
- Such a reconstruction allows an assessment of spontaneous breathing and thus indirectly the ventilation quality. In the simplest case, it can be decided by integrating the reconstructed values whether the patient breathes or counter breaths. For the first time, more complex classification procedures can be used for controlled ventilation derive a definite assessment, for example with regard to synchronization or the amount of breathing work.
- FIG 3 shows a time course for the difference for the measured variables between two ventilation cycles, on the one hand for an inspiratory volume flow difference (20) and on the other hand for a pressure difference (21) in the area of the breathing mask (12).
- FIG. 4 shows, with respect to a first pressure curve (22) for a first ventilation cycle and a second pressure curve (23) of a second ventilation cycle, the determined reconstruction curve (24) for spontaneous breathing by the patient (13) taking into account the volume flow difference (20) and the pressure difference ( 21) between two breaths with different inspiratory volume flow.
- FIG. 5 shows the device illustrated in FIG. 1 in a representation as a block diagram.
- the ventilator (7) is connected to the breathing gas hose (10) and the volume flow sensor is in a transition area from the ventilator (7) to the breathing gas hose (10)
- the breathing gas hose (10) is connected to the breathing mask (12) and in the transition area from the breathing gas hose (10) to the breathing mask (12) there is an additional volume flow sensor
- the sensors can also be used only in the transfer area between the ventilator (7) and the breathing gas tube (10) or only in the transfer area between the breathing gas tube
- an expiration valve (11) is arranged in the transition area from the breathing gas hose (10) to the breathing mask (12) and an outlet system (27) is arranged in the transition area from the ventilator (7) to the breathing gas hose (10). It is also possible to position the expiration valve (11) only in the area of the transition from the breathing gas hose (10) to the breathing mask (12) or only in the transition area from the ventilator (7) to the breathing gas hose (10) to position the outlet system (27). It is also conceivable that the expiration valve (11) is replaced by an outlet system and the outlet system (29) is also replaced by an expiration valve (11).
- non-invasive devices can also be used to provide a connection to the patient (13).
- the use of masks or helmets is contemplated.
- the connection between the ventilation device (1) and the patient (13) can also be made by invasive coupling devices, for example a tube, a tracheostoma or a laryngeal mask.
- the ventilation devices used can be designed to carry out different forms of ventilation. For example, it can be controlled, assisted ventilation or breathing aid.
- the method can also be used for periodic breathing, CPAP or APAP. Resistance and compliance can be determined, for example, only within the inspiratory or only the expiratory time intervals of the ventilation cycles. However, it is also possible to carry out the corresponding evaluations both in the inspiratory and in the expiratory phases.
- FIG. 7 shows the embodiment already mentioned, in which the breathing gas hose (10) is directly coupled to the breathing gas mask (12) and the outlet system (27) and the sensors () only in the transition area from the ventilator (7) to the breathing gas hose (10). 8, 9) are positioned.
- FIG. 8 shows an embodiment modified from FIG. 7, in which the outlet system (27) and the oleum flow sensor (9) are positioned between the ventilator and the breathing gas tube (10) and in which between the breathing gas tube (10) and the breathing mask (12) the pressure sensor (8) is positioned.
- the outlet system (27) and the pressure sensor (8) are positioned between the ventilator (7) and the breathing gas tube (10), and the volume flow sensor (9) is between the breathing gas tube (10) and the breathing mask (12) ) arranged.
- both the outlet system (27) is arranged between the ventilator (7) and the breathing gas hose (10) and both the volume flow sensor and the pressure sensor (8) are between the breathing gas hose (10) and the breathing mask (12) positioned.
- both the pressure sensor (8) and the volume flow sensor (9) are positioned between the ventilator (7) and the breathing gas hose (10) and between the breathing hose (10) and the breathing mask ( _L2) the expiration valve (11) is positioned.
- volume flow sensor (9) is arranged between the ventilator (7) and the breathing gas hose (10) and between the breathing gas hose (10) and the breathing mask (12) are the expiration valve (11) and the Pressure sensor (8) positioned.
- only the pressure sensor (8) is arranged between the ventilator (7) and the breathing gas hose (10) and between the breathing gas hose (10) and the breathing mask (12) are both the expiration valve (11) and the volume flow sensor (9) is also arranged.
- FIG. 15 shows an equivalent circuit diagram supplemented to the representation in FIG. 2, which in the case of linear behavior for the system consists of the patient and the breathing tube.
- the capacity (28) resulting from the hose volume is taken into account in an additional parallel branch.
- p FS is not equal to p aw .
- the extension can also be used
- T s represents the readjustment time of the flexible ventilation hose with the hose connection pieces.
- the dead time Tt corresponds to the sound propagation time through the hose.
- the parameters R, C and R L can be estimated using known identification or parameter estimation methods for linear and also nonlinear dynamic systems.
- a temporally distributed calculation of the parameter estimate is particularly advantageous for the implementation. Recursive methods enable results that are closest to the last observation period.
Abstract
Description
Claims
Priority Applications (3)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US10/550,634 US7475685B2 (en) | 2003-03-24 | 2004-03-23 | Method and device for detecting leaks in respiratory gas supply systems |
DE112004000944T DE112004000944D2 (de) | 2003-03-24 | 2004-03-23 | Verfahren und Vorrichtung zur Erkennung von Leckagen bei Einrichtungen zum Zuführen von Atemgasen |
EP04722532A EP1605999A1 (de) | 2003-03-24 | 2004-03-23 | Verfahren und vorrichtung zur erkennung von leckagen bei einrichtungen zum zuführen von atemgasen |
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
DE10313082.9 | 2003-03-24 | ||
DE10313082 | 2003-03-24 |
Publications (1)
Publication Number | Publication Date |
---|---|
WO2004084980A1 true WO2004084980A1 (de) | 2004-10-07 |
Family
ID=33038745
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
PCT/DE2004/000607 WO2004084980A1 (de) | 2003-03-24 | 2004-03-23 | Verfahren und vorrichtung zur erkennung von leckagen bei einrichtungen zum zuführen von atemgasen |
Country Status (4)
Country | Link |
---|---|
US (1) | US7475685B2 (de) |
EP (1) | EP1605999A1 (de) |
DE (2) | DE112004000944D2 (de) |
WO (1) | WO2004084980A1 (de) |
Cited By (10)
Publication number | Priority date | Publication date | Assignee | Title |
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WO2006021169A1 (de) * | 2004-08-20 | 2006-03-02 | Weinmann Geräte für Medizin GmbH & Co. KG | Vorrichtung zur beatmung sowie verfahren zur steuerung eines beatmungsgerätes |
WO2007068132A1 (de) * | 2005-12-16 | 2007-06-21 | Hamilton Medical Ag | Schlauchsystem für beatmungsgeräte |
WO2009123981A1 (en) * | 2008-03-31 | 2009-10-08 | Nellcor Puritan Bennett Llc | Leak-compensated proportional assist ventilation |
WO2010099373A1 (en) * | 2009-02-27 | 2010-09-02 | Nellcor Puritan Bennett Llc | Leak-compensated respiratory mechanics estimation in medical ventilators |
US7861711B2 (en) | 2006-01-20 | 2011-01-04 | Shenzhen Mindray Bio-Medical Electronics Co., Ltd. | Method for judging the reverse connection of a flow sensor and a respiratory mechanics measuring module used therein |
CN103180002A (zh) * | 2010-07-30 | 2013-06-26 | 雷斯梅德有限公司 | 泄漏检测方法和设备 |
CN104080503A (zh) * | 2011-12-27 | 2014-10-01 | 皇家飞利浦有限公司 | 呼吸递送的补偿 |
US9675771B2 (en) | 2013-10-18 | 2017-06-13 | Covidien Lp | Methods and systems for leak estimation |
US10207069B2 (en) | 2008-03-31 | 2019-02-19 | Covidien Lp | System and method for determining ventilator leakage during stable periods within a breath |
CN111481848A (zh) * | 2020-04-24 | 2020-08-04 | 张乐 | 节能型人防工程用通风设备 |
Families Citing this family (57)
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FR2858236B1 (fr) * | 2003-07-29 | 2006-04-28 | Airox | Dispositif et procede de fourniture de gaz respiratoire en pression ou en volume |
DE102005061439B3 (de) * | 2005-12-22 | 2007-05-16 | Draeger Medical Ag | Vorrichtung und Verfahren zur Bestimmung von Leckagen einer Beatmungsvorrichtung |
CN100998902B (zh) | 2006-01-13 | 2010-12-08 | 深圳迈瑞生物医疗电子股份有限公司 | 流量监测与控制的装置 |
EP3025748B1 (de) * | 2006-08-30 | 2019-01-16 | ResMed Limited | Bestimmung von leckagen bei der cpap-behandlung |
US8746248B2 (en) * | 2008-03-31 | 2014-06-10 | Covidien Lp | Determination of patient circuit disconnect in leak-compensated ventilatory support |
US8272379B2 (en) * | 2008-03-31 | 2012-09-25 | Nellcor Puritan Bennett, Llc | Leak-compensated flow triggering and cycling in medical ventilators |
US8267085B2 (en) * | 2009-03-20 | 2012-09-18 | Nellcor Puritan Bennett Llc | Leak-compensated proportional assist ventilation |
US8457706B2 (en) * | 2008-05-16 | 2013-06-04 | Covidien Lp | Estimation of a physiological parameter using a neural network |
DE102008048824A1 (de) * | 2008-09-22 | 2010-03-25 | Borm, Hans-Jürgen | Verfahren und Einrichtung zur automatischen Ermittlung eines Beatmungsvolumens bei der maschinellen Beatmung, unter Berücksichtigung von Leckagen |
US20100071696A1 (en) * | 2008-09-25 | 2010-03-25 | Nellcor Puritan Bennett Llc | Model-predictive online identification of patient respiratory effort dynamics in medical ventilators |
US8302602B2 (en) | 2008-09-30 | 2012-11-06 | Nellcor Puritan Bennett Llc | Breathing assistance system with multiple pressure sensors |
DE102009005048A1 (de) | 2009-01-13 | 2010-07-15 | Borm, Hans-Jürgen | Verfahren und Einrichtung zur automatischen Ermittlung eines inspiratorischen Leckagevolumens bei der maschinellen Beatmung |
US8434479B2 (en) | 2009-02-27 | 2013-05-07 | Covidien Lp | Flow rate compensation for transient thermal response of hot-wire anemometers |
US20100218766A1 (en) * | 2009-02-27 | 2010-09-02 | Nellcor Puritan Bennett Llc | Customizable mandatory/spontaneous closed loop mode selection |
US8418691B2 (en) * | 2009-03-20 | 2013-04-16 | Covidien Lp | Leak-compensated pressure regulated volume control ventilation |
CN102695536B (zh) * | 2009-08-11 | 2016-02-24 | 瑞思迈发动机及马达技术股份有限公司 | 单级轴对称鼓风机和便携式通风机 |
US8439037B2 (en) * | 2009-12-01 | 2013-05-14 | Covidien Lp | Exhalation valve assembly with integrated filter and flow sensor |
US8469030B2 (en) | 2009-12-01 | 2013-06-25 | Covidien Lp | Exhalation valve assembly with selectable contagious/non-contagious latch |
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US8707952B2 (en) | 2010-02-10 | 2014-04-29 | Covidien Lp | Leak determination in a breathing assistance system |
EP2368593A1 (de) * | 2010-03-26 | 2011-09-28 | Dräger Medical GmbH | Schätzung einer Verlustströmung |
USD655809S1 (en) | 2010-04-27 | 2012-03-13 | Nellcor Puritan Bennett Llc | Valve body with integral flow meter for an exhalation module |
USD653749S1 (en) | 2010-04-27 | 2012-02-07 | Nellcor Puritan Bennett Llc | Exhalation module filter body |
USD655405S1 (en) | 2010-04-27 | 2012-03-06 | Nellcor Puritan Bennett Llc | Filter and valve body for an exhalation module |
EP2569034B1 (de) * | 2010-05-11 | 2017-07-26 | Koninklijke Philips N.V. | Induktanzkompensation in einem druckunterstützungssystem |
EP2590702B1 (de) * | 2010-07-09 | 2014-05-14 | Koninklijke Philips N.V. | Leckbeurteilung mittels leckmodellidentifizierung |
IT1401033B1 (it) * | 2010-07-26 | 2013-07-12 | Milano Politecnico | Sistema e metodo per la misura dell'impedenza meccanica del sistema respiratorio |
US8776792B2 (en) | 2011-04-29 | 2014-07-15 | Covidien Lp | Methods and systems for volume-targeted minimum pressure-control ventilation |
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US9364624B2 (en) | 2011-12-07 | 2016-06-14 | Covidien Lp | Methods and systems for adaptive base flow |
US9498589B2 (en) | 2011-12-31 | 2016-11-22 | Covidien Lp | Methods and systems for adaptive base flow and leak compensation |
US9993604B2 (en) | 2012-04-27 | 2018-06-12 | Covidien Lp | Methods and systems for an optimized proportional assist ventilation |
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Also Published As
Publication number | Publication date |
---|---|
US20060249150A1 (en) | 2006-11-09 |
EP1605999A1 (de) | 2005-12-21 |
DE102004014619A1 (de) | 2005-03-17 |
DE112004000944D2 (de) | 2006-02-09 |
US7475685B2 (en) | 2009-01-13 |
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