US3923055A - Process and device for controlling the pressure course of a respirator - Google Patents
Process and device for controlling the pressure course of a respirator Download PDFInfo
- Publication number
- US3923055A US3923055A US524172A US52417274A US3923055A US 3923055 A US3923055 A US 3923055A US 524172 A US524172 A US 524172A US 52417274 A US52417274 A US 52417274A US 3923055 A US3923055 A US 3923055A
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- United States
- Prior art keywords
- patient
- pressure
- pulse
- respirator
- valve
- Prior art date
- Legal status (The legal status 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 status listed.)
- Expired - Lifetime
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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
-
- 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
-
- 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
- A61M2230/00—Measuring parameters of the user
- A61M2230/04—Heartbeat characteristics, e.g. ECG, blood pressure modulation
Definitions
- ABSTRACT A process and apparatus are disclosed for controlling the pressure course of a respirator connected to a patient, in which the pressure of the respiration gas is momentarily decreased, under the control of a pulsesynchronized signal waveform derived from physiological data taken from the patient, for example, the ECG, during the propagation time of each pulse wave in the alveolar flow path of the patient. Following each decrease there is immediately effected a substantial re-establishment of the pressure of the respiration gas.
- Disclosed apparatus suitable for performing this operation comprises a timer circuit responsive to the pulse-synchronized signals generated from the patients physiological data and a valve arrangement which is coupled into the patient respirator line and controlled by the output pulse waveform of the timer circuit.
- Patent Dec. 2 1975 Sheet 1 of4 3,923,055
- This invention concerns a process and a device for controlling the pressure course of a respirator.
- respirators The functioning of most hitherto available respirators is based on periodically delivering a respiration gas to the lungs of the patient with a frequency lying in the magnitude of the natural respiration frequency.
- control There are essentially two types of control being used: Regarding the so-called pressure-controlled systems, a specified maximum pressure is built up in the lungs of the patient in every respiration cycle and subsequently released.
- volume-controlled systems a volumetrically measured quantity of respiration gas is delivered to the patient in every respiration cycle.
- the present invention is based on the task of eliminating this disadvantage and producing a control for a respirator with which an improved artifical respiration is made possible, especially in the case of patients with weak circulation.
- an apparatus comprising a timer responsive to a pulsesynchronized signal and a valve, the latter of which is connected to the patient line and controlled by an output impulse of the timer, for reducing the pressure in the patient line.
- the pulse-synchronized signal which is brought into use for the pressure control can be produced in various ways.
- One possibility consists, for example, in using the so-called ECG-trigger impulse of an ECG apparatus which gives the R-peak of the electrocardiogram.
- Other possibilities consist in taking the control signal from a plethysmograph or from devices for rheographically determining the heartbeat volume or the detection of blood flow by means of an ultrasonic process.
- there is suitable for the production of the control signal any measurement of action currents or potentials of the heart, as well as sanguinous and nonsanguinous measurements of pressure, flow, flow velocity, acceleration, etc.
- the thus obtained impulses have to be delayed by the time which elapses between the measuring instant and the arrival of the pulse wave in the alveoles.
- This time span depends, for example, on the measuring point when using a signal derived from a plethysmo graph or a signal produced by a rheographical measurement and in other respects is influenced by physiological factors, so that it can be of different duration from patient to patient.
- the delayed impulse is delivered to the respiration system where it effects the reduction of the respiration pressure.
- the respiration system there can also be provided in the pneumatic system of the respirator, various options such as valves, pumps, etc., some of which are described in the following.
- the respiration pressure is re-increased, an additional acceleration impulse being imparted to the blood flowing back to the left heart with appropriate construction of the pressure curve and the action of an auxiliary lung-circulation pump being accordingly produced.
- FIG. 1 is a schematic representation of an embodiment of the device in accordance with the invention in interaction with the patient line of a respirator;
- FIGS. 1A and 1B are enlarged schematic representations of a valve element in the arrangement of FIG. 1;
- FIG. 1C is a schematic representation of the timing circuit portion of the arrangement of FIG. 1;
- FIGS. 2a-2e are graphical representations which show the functioning at various points of the device and the influence thereof on the respiration pressure
- FIGS. 3a-3d are graphical representations for another operating method.
- FIG. 4 is a schematic representation of another embodiment of the invention.
- FIG. 5 is a schematic representation of a further embodiment of the invention.
- a patient 1 is respired with a respirator 2 which is connected with the patient via a line 3.
- the patient 1 can be a new or prematurely born child or also an adult.
- a different respirator 2 is employed, the control of the respirator, however, generally being insignificant.
- the device in accordance with the invention is equally well suited to volume-controlled, pressure-controlled or hybrid systems.
- valve 4 which depending on the disposition of the patient is connected with the respirator 2 or with the open air.
- the two positions of the valve are shown in enlarged scale and in a schematic form with I and II in FIGS. 1A and 13.
- an electromagnetic valve in which a switching is effected by an electronic impulse.
- the electronic impulse required for switching proceeds to the valve 4 viii the l electric line 5.
- the switching signal for the valve is produced in the present embodiment from the ECG of the patient.
- the patient carries the usual ECG electrodes 6, which are connected via lines 7 with the inputs of an electrocardiograph 8.
- the so-called ECG-trigger impulse is obtained from the R-peak of the ECG.
- This ECG-trigger is usually available in the patient monitoring anyhow, so that the ECG device according to the invention is not further concerned with the derivation of same.
- the ECG-trigger signal is delivered to a timer circuit 9, a preferred example of which is illustrated in greater detail in FIG. 10.
- the timer circuit 9 serves for producing a rectangular signal with a certain delay with respect to the ECG-trigger signal.
- the timer circuit contains, for example, two monostable sweep circuits, normally connected in series, the first of which produces an impulse whose length determines the time delay of the output impulse of the timer circuit with respect to the ECG-trigger signal and controls the second sweep circuit with its declining flank.
- Such timer circuits are available in the trade as integrated components. There exists, for example, the component XR-2556 of the Firm Exar-Integrated Systems Inc., which contains two timer stages, with which the functioning of the timer contained in the present embodiment can be realized by suitable conventional switching.
- two potentiometers are contained in the timer circuit 9, with which the impulse lengths of the monostable sweep circuits can be varied.
- the output signal of the timer 9 is amplified in an amplifier 10 until it is suitable for switching the electromagnetic valve 4.
- the patient 1 is respired by the respirator 2 with a permanently set frequency, i.e. at constant intervals a specific amount of respiration gas is pumped into the lungs of the patient and in each case subsequently released or evacuated.
- the ECG of the patient is simultaneously measured, that is with a measuring apparatus which produces an impulse indicating the R-peak.
- the control impulse for the valve 4 is produced in the timer 9.
- the valve switches from the I position shown in FIG. 1A into the II position shown in FIG. 1B, in which the respiration gas line from the respirator to the patient is blocked and a connection between the patient and the open air exists. Since the pressure in the lungs of the patient lies above the atmospheric pressure for practically an entire respiration cycle, at the moment in which the valve produces a connection between the patients lungs and the open air, a sudden pressure decrease occurs in the lungs.
- the valve again switches to position I, the patient is accordingly reconnected to the respirator, by which means the pressure in his lungs again increases to the respiration pressure.
- the time spacing between the ECG-trigger signal and the beginning of the control impulse for the valve 4 should correspond essentially to the time-span between the occurrence of a QRS-complex (or more precisely the R- peak) and the arrival of the respective or, if possible, a following pulse wave in the pulmonary alveolar vessel system, in order to achieve optimal relief of the alveolar circulation.
- the duration of the control impulse has to correspond to the time which the pulse wave requires to pass through the alveolar vessel system in order to subsequently be able to very rapidly re-increase the pressure and accordingly achieve the desired effect of a back-flow acceleration impulse.
- FIG. 2e shows the electrocardiogram. From the R-peaks of same there is derived the ECG-trigger impulse (e.g. pulse 40) which is shown in the curve of FIG. 2a.
- the ECG-trigger impulse waveform is introduced into the timer circuit 9, in which the impulses 11 shown in the curve of FIG. 2b are produced by the first monostable sweep circuit and the impulses 12 shown in the curve 0 are produced by the second sweep circuit, the impulses 12 representing the control impulses for the electromagnetic valve.
- the curve of FIG. 20 shows the output pulse waveform of the timer 9.
- the valve 4 For the duration of an impulse 12, the valve 4 is switched into position II, in which the connection from the respirator 2 to the patient is blocked and the air under pressure can escape from the lungs of the patient. At the end of the impulse 12, the valve 4 is again switched back into position I and the connection between the respirator 2 and the lungs of the patient is again provided.
- the curve of FIG. 2d shows the course of the respiration pressure.
- the dotted line 13 gives the respiration pressure as it is produced from the respirator without the device in accordance with the invention.
- the valve switches into position II by which means, after a short delay dependent on the compliance of the lungs, the pressure decreases.
- the point 15 corresponds to the end of an impulse 12 and accordingly to the switching of the valve 4 back into position I.
- the curve changes into a new pressure increase with a short delay.
- the valve is again switched, by which means the pressure again falls.
- a switching back of the valve into position I is effected, which results in a new pressure increase.
- the same process repeats itself several times during each respiration cycle, the number of switchings per respiration cycle depending on the ratio of respiration frequency to heart frequency.
- the patient can be connected to a reduced pressure instead of the atmospheric pressure for the duration of the impulse 12. This is shown in dotted lines in FIG. 1 by the connection of the valve 4 to a negative pressure chamber 18.
- the chamber 18 is kept constantly at reduced pressure by a pump 19.
- Another possibility consists in connecting the valve 4 directly to the pump 19.
- FIGS. 3a-3d are graphical illustrations or impulse diagrams which show the application of the process in accordance with the invention to a .respiration method which is at present employed repeatedly for the respiration of the new-born.
- the lungs of the patient are kept continuously at a positive final expiratory pressure above which the patient breathes spontaneously.
- pulse-synchronized modulation of the pressure there can also be produced in this method a substantially improved perfusion as well as, above all, the effect of a back-flow auxiliary pump.
- the electrical impulse plots of FIG. 3a and FIGS. 312-311 correspond respectively to those of FIG. 2a and FIGS. 2c2e.
- FIG. 4 an alternative arrangement is shown wherein in place of the valve 4 a pump 20 is provided which for the duration of the impulse 12 extracts respiration gas from the line'from the respirator 2 to the patient 1 and redelivers it at the end of the impulse 12.
- a pump 20 is provided which for the duration of the impulse 12 extracts respiration gas from the line'from the respirator 2 to the patient 1 and redelivers it at the end of the impulse 12.
- a rapid pressure decrease and, in particular, also a rapid pressure increase at the end of the impulse 12 can be obtained. This is particularly favorable for the additional action of the device in accordance with the invention as a back-flow auxiliary pump.
- the hitherto described embodiments of the device in accordance with the invention serve as supplementary apparatus for existing respirators.
- the pressure relief functioning of the device in accordance with the invention is superimposed on the pressure curves of the respirators.
- the entire control of a respirator can be carried out by pulse synchronization.
- a corresponding embodiment is shown in FIG. 4.
- the respiration frequency is not specified independently, but it is a multiple of the heart frequency.
- the inspiration and expiration phases are multiples of the heart cycle.
- Such a respirator (e.g. FIG. 5) consists of a respiration gas source 21 in which respiration gas is available at an elevated pressure, a regulation valve 22 for regulating the flow of the respiration gas and for switching between inspiration and expiration and a pneumatic switch 23 which leads off the expired gas from the patient line.
- a respirator is described, for example in the US. Pat. application Ser. No. 341,432, filed Mar. 15, 1973.
- the patient line 3 leads through a measuring head 26 for measuring the flow and pressure of the respiration gas directly in the tracheal tube which serves for the intubation of the patient. Electric signals are produced in the measuring head 26, which reproduce the flow and/or pressure course of the respiration gas.
- An electric lead 27 serves for transmitting the obtained signals to an electronic regulation device 28.
- respirators such as the previously described respirator regulated entirely with the aid of a valve is especially well suited for a combination with the respiration method in accordance with the invention
- respirators based on other principles can also be adapted to operation with the pulse-synchronized control.
- the pressure characteristic of the pump must therefore by synchronized with the heartbeat.
- this can be carried out in a relatively simple manner either mechanically or also electronically.
- rheographical processes for measuring the perfusion are also suitable for producing the control signal.
- a device for such a process could be arranged to be directly associated with the tracheal tube, which has the advantage that the signal is obtained in the immediate vicinity of the alveolar vessel system and errors caused by variations of the propagation time of the pulse wave can be excluded.
- the tracheal tube is provided, for example, with electrodes at both its ends, which are connected to a suitable measuring circuit.
- the second electrode could alternatively also be applied externally to the thorax.
- a process for controlling the pressure course of a respirator comprising momentarily decreasing the pressure of the respiration gas under the control of a pulsesynchronized signal derived from a measurement of impulses produced by the heart of the patient associated with the respirator in each case during the propagation time of the pulse wave in the pulmonary alveolar blood vessel flow paths of the patient and immediately thereafter causing substantially a re-establishment of the pressure of the respiration gas.
- a process according to claim 1 wherein the pulsesynchronized signal is generated from a patient-derived blood-pressure signal.
- a process according to claim 1 further comprising delaying the pulse-synchronized signals and reforming same into impulses corresponding to the duration of the passage of the pulse wave through the pulmonary alveolar blood vessel flow paths.
- a process according to claim 1 further comprising producing a control signal from the pulse-synchronized signal and superimposing same on the pressure course of a respirator via a valve means connected into the respiration line.
- a process according to claim 5 further comprising coupling the patient line to a reduced pressure via a valve means for the duration of the control impulse.
- a process according to claim 1 further comprising generating a control signal from the pulse-synchronized signal and using same for controlling the time cycle of a respirator.
- a process according to claim 1 further comprising providing additional pneumatic means for shortening the pressure increase following the reduction in pressure.
- Apparatus for controlling the pressure course of a respirator in which the pressure of the respiration gas is momentarily decreased, under the control of a pulse synchronized signal derived from a measurement of impulses produced by the heart taken from a patient associated with the respirator, during the propagationtime of the pulse wave in the pulmonary alveolar blood vessel flow paths of the patient and is immediately substantially re-established thereafter, comprising first means for deriving the pulse synchronized signal from said measurement taken from a patient, second means contained in the line from a respiration gas source to the patient for controllably reducing the pressure momen- 11.
- a device according to claim 10 wherein said valve arrangement is connected with a reduced pressure chamber in said other switching position.
- valve arrangement connects the patient line with a suction pump in said second switching position.
- a device comprising the control valve of a valvecontrolled respirator.
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- Health & Medical Sciences (AREA)
- Emergency Medicine (AREA)
- Pulmonology (AREA)
- Engineering & Computer Science (AREA)
- Anesthesiology (AREA)
- Biomedical Technology (AREA)
- Heart & Thoracic Surgery (AREA)
- Hematology (AREA)
- Life Sciences & Earth Sciences (AREA)
- Animal Behavior & Ethology (AREA)
- General Health & Medical Sciences (AREA)
- Public Health (AREA)
- Veterinary Medicine (AREA)
- Percussion Or Vibration Massage (AREA)
Applications Claiming Priority (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
CH1642973A CH571868A5 (ja) | 1973-11-21 | 1973-11-21 |
Publications (1)
Publication Number | Publication Date |
---|---|
US3923055A true US3923055A (en) | 1975-12-02 |
Family
ID=4417296
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US524172A Expired - Lifetime US3923055A (en) | 1973-11-21 | 1974-11-15 | Process and device for controlling the pressure course of a respirator |
Country Status (7)
Country | Link |
---|---|
US (1) | US3923055A (ja) |
JP (1) | JPS5830059B2 (ja) |
CH (1) | CH571868A5 (ja) |
DE (1) | DE2454330C2 (ja) |
FR (1) | FR2251340B1 (ja) |
GB (1) | GB1466620A (ja) |
NL (1) | NL175702C (ja) |
Cited By (31)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4155356A (en) * | 1976-02-10 | 1979-05-22 | Venegas Jose G | Respiration assisting apparatus and method |
US4203434A (en) * | 1978-04-05 | 1980-05-20 | Brooks Lula M | Timing assembly for oxygen respiration units |
US4543951A (en) * | 1982-11-30 | 1985-10-01 | Senko Medical Instrument Mfg. Co., Ltd. | Respirator with two jet gas injection tubes |
EP0324275A1 (en) * | 1987-12-23 | 1989-07-19 | N. Visveshwara, M.D., Inc. | Ventilation synchronizer |
WO1989009041A1 (en) * | 1988-03-31 | 1989-10-05 | Cardiopulmonary Corporation | Circulatory assist method and apparatus |
US5007420A (en) * | 1981-08-10 | 1991-04-16 | Bird F M | Ventilator having an oscillatory inspiratory phase and method |
US5020528A (en) * | 1990-05-30 | 1991-06-04 | Myers Phillip R | Method and apparatus for permitting medical personnel to attend to a patient situated in a hazardous location remote therefrom |
US5133346A (en) * | 1990-12-03 | 1992-07-28 | Arvee Medical, Incorporated | Apnea monitor data system |
US5150291A (en) * | 1986-03-31 | 1992-09-22 | Puritan-Bennett Corporation | Respiratory ventilation apparatus |
US5377671A (en) * | 1991-04-26 | 1995-01-03 | Cardiopulmonary Corporation | Cardiac synchronous ventilation |
US5423313A (en) * | 1981-03-10 | 1995-06-13 | Siemens-Elema Ab | Respirator intended for connection to human or animal airways |
US5899203A (en) * | 1992-12-24 | 1999-05-04 | Defares; Peter Bernard | Interactive respiratory regulator |
US5931160A (en) * | 1995-12-08 | 1999-08-03 | Cardiopulmonary Corporation | Ventilator control system and method |
US6079412A (en) * | 1997-04-18 | 2000-06-27 | Meier; Bernd Horst | Process and device for controlling and assisting natural breathing and mechanical respiration |
US6158432A (en) * | 1995-12-08 | 2000-12-12 | Cardiopulmonary Corporation | Ventilator control system and method |
US6463930B2 (en) | 1995-12-08 | 2002-10-15 | James W. Biondi | System for automatically weaning a patient from a ventilator, and method thereof |
US6962155B1 (en) * | 1999-07-30 | 2005-11-08 | Universite De Montreal | Target drive ventilation gain controller and method |
EP1718356A1 (en) * | 2004-02-25 | 2006-11-08 | ResMed Limited | Cardiac monitoring and therapy using a device for providing pressure treatment of sleep disordered breathing |
US20080202522A1 (en) * | 2007-02-23 | 2008-08-28 | General Electric Company | Setting mandatory mechanical ventilation parameters based on patient physiology |
US20080202517A1 (en) * | 2007-02-23 | 2008-08-28 | General Electric Company | Setting madatory mechanical ventilation parameters based on patient physiology |
US20080202519A1 (en) * | 2007-02-23 | 2008-08-28 | General Electric Company | Setting mandatory mechanical ventilation parameters based on patient physiology |
US20080202518A1 (en) * | 2007-02-23 | 2008-08-28 | General Electric Company | Setting mandatory mechanical ventilation parameters based on patient physiology |
US20080202520A1 (en) * | 2007-02-23 | 2008-08-28 | General Electric Company | Setting mandatory mechanical ventilation parameters based on patient physiology |
US20080230063A1 (en) * | 2007-03-23 | 2008-09-25 | General Electric Company | Setting inspiratory time in mandatory mechanical ventilation based on patient physiology, such as forced inhalation time |
US20080230064A1 (en) * | 2007-03-23 | 2008-09-25 | General Electric Company | Setting inspiratory time in mandatory mechanical ventilation based on patient physiology, such as when forced inhalation flow ceases |
US20080230060A1 (en) * | 2007-03-23 | 2008-09-25 | General Electric Company | Setting inspiratory time in mandatory mechanical ventilation based on patient physiology, such as when tidal volume is inspired |
US20080230061A1 (en) * | 2007-03-23 | 2008-09-25 | General Electric Company | Setting expiratory time in mandatory mechanical ventilation based on a deviation from a stable condition of end tidal gas concentrations |
US20090118580A1 (en) * | 2004-07-02 | 2009-05-07 | Wei-Zen Sun | Image-type intubation-aiding device |
US20090229612A1 (en) * | 2008-03-14 | 2009-09-17 | General Electric Company | System and method for integrated high frequency oscillatory ventilation |
US20100076262A1 (en) * | 2008-09-19 | 2010-03-25 | National Taiwan University | Endoscope inspection system |
CN105688316A (zh) * | 2015-12-31 | 2016-06-22 | 台培春 | 一种急诊内科新型滤氧呼吸装置 |
Families Citing this family (4)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
EP0273041A4 (en) * | 1986-03-31 | 1990-01-11 | Puritan Bennett Corp | COMPUTER-CONTROLLED SYSTEM PROVIDING POSITIVE PRESSURE AT THE END OF EXPIRATION. |
US5335650A (en) * | 1992-10-13 | 1994-08-09 | Temple University - Of The Commonwealth System Of Higher Education | Process control for liquid ventilation and related procedures |
DE9406407U1 (de) * | 1994-04-18 | 1995-08-17 | Schneider, Peter, 56759 Laubach | Sauerstofftherapiegerät |
DE29622321U1 (de) * | 1996-12-21 | 1997-03-06 | Medicap Medizintechnik GmbH, 35327 Ulrichstein | Einrichtung zur dosierten Gasversorgung von Anwendern |
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US3212496A (en) * | 1962-08-21 | 1965-10-19 | United Aircraft Corp | Molecular physiological monitoring system |
US3452739A (en) * | 1966-08-15 | 1969-07-01 | Avco Corp | Heart pump synchronizing apparatus |
US3587562A (en) * | 1968-02-01 | 1971-06-28 | Becton Dickinson Co | Physiological monitoring system |
US3730173A (en) * | 1970-02-02 | 1973-05-01 | Ahldea Corp | Stimulation method and apparatus for attempting to return a physiological parameter of a patient to normal |
Family Cites Families (1)
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DE1766589B1 (de) * | 1968-06-19 | 1971-08-05 | Heyer Gmbh Carl | Beatmungsgeraet |
-
1973
- 1973-11-21 CH CH1642973A patent/CH571868A5/xx not_active IP Right Cessation
-
1974
- 1974-09-26 NL NLAANVRAGE7412720,A patent/NL175702C/xx not_active IP Right Cessation
- 1974-10-15 GB GB4468274A patent/GB1466620A/en not_active Expired
- 1974-11-15 DE DE2454330A patent/DE2454330C2/de not_active Expired
- 1974-11-15 US US524172A patent/US3923055A/en not_active Expired - Lifetime
- 1974-11-18 FR FR7437926A patent/FR2251340B1/fr not_active Expired
- 1974-11-20 JP JP49133489A patent/JPS5830059B2/ja not_active Expired
Patent Citations (4)
Publication number | Priority date | Publication date | Assignee | Title |
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US3212496A (en) * | 1962-08-21 | 1965-10-19 | United Aircraft Corp | Molecular physiological monitoring system |
US3452739A (en) * | 1966-08-15 | 1969-07-01 | Avco Corp | Heart pump synchronizing apparatus |
US3587562A (en) * | 1968-02-01 | 1971-06-28 | Becton Dickinson Co | Physiological monitoring system |
US3730173A (en) * | 1970-02-02 | 1973-05-01 | Ahldea Corp | Stimulation method and apparatus for attempting to return a physiological parameter of a patient to normal |
Cited By (49)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4155356A (en) * | 1976-02-10 | 1979-05-22 | Venegas Jose G | Respiration assisting apparatus and method |
US4203434A (en) * | 1978-04-05 | 1980-05-20 | Brooks Lula M | Timing assembly for oxygen respiration units |
US5423313A (en) * | 1981-03-10 | 1995-06-13 | Siemens-Elema Ab | Respirator intended for connection to human or animal airways |
US5007420A (en) * | 1981-08-10 | 1991-04-16 | Bird F M | Ventilator having an oscillatory inspiratory phase and method |
US4543951A (en) * | 1982-11-30 | 1985-10-01 | Senko Medical Instrument Mfg. Co., Ltd. | Respirator with two jet gas injection tubes |
US5150291A (en) * | 1986-03-31 | 1992-09-22 | Puritan-Bennett Corporation | Respiratory ventilation apparatus |
EP0324275A1 (en) * | 1987-12-23 | 1989-07-19 | N. Visveshwara, M.D., Inc. | Ventilation synchronizer |
US4915103A (en) * | 1987-12-23 | 1990-04-10 | N. Visveshwara, M.D., Inc. | Ventilation synchronizer |
US5020516A (en) * | 1988-03-31 | 1991-06-04 | Cardiopulmonary Corporation | Circulatory assist method and apparatus |
AU620097B2 (en) * | 1988-03-31 | 1992-02-13 | Cardiopulmonary Corporation | Circulatory assist method and apparatus |
WO1989009041A1 (en) * | 1988-03-31 | 1989-10-05 | Cardiopulmonary Corporation | Circulatory assist method and apparatus |
US5020528A (en) * | 1990-05-30 | 1991-06-04 | Myers Phillip R | Method and apparatus for permitting medical personnel to attend to a patient situated in a hazardous location remote therefrom |
US5133346A (en) * | 1990-12-03 | 1992-07-28 | Arvee Medical, Incorporated | Apnea monitor data system |
US5377671A (en) * | 1991-04-26 | 1995-01-03 | Cardiopulmonary Corporation | Cardiac synchronous ventilation |
US5899203A (en) * | 1992-12-24 | 1999-05-04 | Defares; Peter Bernard | Interactive respiratory regulator |
US5931160A (en) * | 1995-12-08 | 1999-08-03 | Cardiopulmonary Corporation | Ventilator control system and method |
US6158432A (en) * | 1995-12-08 | 2000-12-12 | Cardiopulmonary Corporation | Ventilator control system and method |
US6463930B2 (en) | 1995-12-08 | 2002-10-15 | James W. Biondi | System for automatically weaning a patient from a ventilator, and method thereof |
US6584973B1 (en) | 1995-12-08 | 2003-07-01 | Cardiopulmonary Corporation | Ventilator control system and method |
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Also Published As
Publication number | Publication date |
---|---|
NL7412720A (nl) | 1975-05-23 |
FR2251340A1 (ja) | 1975-06-13 |
NL175702B (nl) | 1984-07-16 |
GB1466620A (en) | 1977-03-09 |
CH571868A5 (ja) | 1976-01-30 |
JPS5830059B2 (ja) | 1983-06-27 |
FR2251340B1 (ja) | 1978-03-24 |
DE2454330C2 (de) | 1984-07-19 |
NL175702C (nl) | 1984-12-17 |
DE2454330A1 (de) | 1975-05-22 |
JPS5085195A (ja) | 1975-07-09 |
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