US3572317A - Respiratory distress monitor - Google Patents

Respiratory distress monitor Download PDF

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Publication number
US3572317A
US3572317A US764448A US3572317DA US3572317A US 3572317 A US3572317 A US 3572317A US 764448 A US764448 A US 764448A US 3572317D A US3572317D A US 3572317DA US 3572317 A US3572317 A US 3572317A
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Prior art keywords
respiratory
heart
respiratory distress
output
rate
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US764448A
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Gerald James Wade
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F Hoffmann La Roche AG
Kontron Inc
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F Hoffmann La Roche AG
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/02—Detecting, measuring or recording pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure
    • A61B5/024—Detecting, measuring or recording pulse rate or heart rate
    • A61B5/0245—Detecting, measuring or recording pulse rate or heart rate by using sensing means generating electric signals, i.e. ECG signals
    • A61B5/02455—Detecting, measuring or recording pulse rate or heart rate by using sensing means generating electric signals, i.e. ECG signals provided with high/low alarm devices
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/08—Detecting, measuring or recording devices for evaluating the respiratory organs
    • A61B5/0809—Detecting, measuring or recording devices for evaluating the respiratory organs by impedance pneumography
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/72—Signal processing specially adapted for physiological signals or for diagnostic purposes
    • A61B5/7235—Details of waveform analysis
    • A61B5/7242—Details of waveform analysis using integration

Definitions

  • a monitoring system adapted to continuously observe a neonate and provide an early warning alarm at the onset of a respiratory distress condition to enable early corrective action to be taken, would be highly desirable.
  • Monitoring devices of the type referred to above are commercially available, whereby basically these devices attempt to provide signals for respiratory distress conditions by indiscriminately analyzing respiratory activity of the neonate.
  • newborn infants breath very irregular, whereby non-critical respiratory arrests are a common occurrence in such irregular breathing.
  • Similar respiratory arrests heretofore referred to as respiratory distress may arise which might lead to total respiratory failure and death or a prolonged respiratory failure and subsequent physiologic damage such as brain damage or physical handicap, if not detected early by the medical staff.
  • the latter has been accomplished by the discovery of a heart beat activity and respiratory activity interaction and specifically that pronounced bradycardia and respiratory arrests when taken together and analyzed, sharply delineate the newborn requiring immediate attention from the child who is varying his routine a little with temporary non-critical respiratory arrests and is not in any immediate danger.
  • prescribed minimum heart rate values and prescribed minimum respiratory arrest time values are related to one another relative to time.
  • bradycardia is absent, and by providing a detection system for responding only to extremely low respiration rates to supplement the detecting of the above discussed interactions, most all conditions of respiratory distress can be continuously monitored with virtually little chance of causing false alarms.
  • FIG. l is a block diagram of one form of the present invention.
  • FIG. 2 represents a detailed schematic block diagram of the invention.
  • FIG. 3 illustrates a series of time related voltage waveforms corresponding to points indicated in FIG. 2.
  • FIG. 4 pictures a recorded comparison of the beat-tobeat heart activity signal and an output signal display represented by heart-beats per minute of the integrated heart-beat value over eight second periods.
  • FIG. 5 displays representations of respiratory rate and Iheart rate values as would resceptively appear on meters 47 and 28 in FIG. 2.
  • FIG. 1 there is shown a block diagram of a general monitoring system utilizing the principles of this invention, wherein a patient 11 is connected by suitable transducers (not shown) to blocks 12, and 13 for provding representative electrical signals to respective- 3 ly measure heart-beat activity and respiratory activity parameters of the patient, which parameters are used as a base lfrom which a condition of respiratory distress is evaluated, which respiratory distress will be particularly described with reference to neo-natals in the instant disclosure.
  • each of the specified physiological parameters to heart-rate data and to use the waveform of respiratory activity to provide respiratory arrest data as evidenced by blocks 15 and 16 respectively.
  • Detection of prescribed low heart-rate events and minimum prescribed periods of cessation of breathing, applicable for neo-natals, are also employed in blocks 15 and 16 respectively, whereby simultaneous occurrence of such events are related in block 17 which would respond to denote a condition of respiratory distress and in turn activate an alarm 18 indicating that an infant requires immediate attention.
  • apparatus is additionally disclosed to implement the detection of a second condition of respiratory distress indicating the need for immediate attention to the neo-natal patient, whereby the second condition of respiratory distress may be independently detected but serves to supplement the overall detection of respiratory distress conditions.
  • FIG. 2 there is shown a schematic diagram of a respiratory distress monitoring system including the principles of this invention generally discussed above.
  • Physiological electrodes 21 or other suitable transducers are positioned in contact with a patient 22 either directly or by way of an intermediate medium such as the conventional electrode pastes. Electrodes 21 are positioned on the patient to obtain a usable electrical signal representative of heart beat having the least artifact, such as that depicted in FIG. 3(a), with the conventional PQRST complex illustrated by the two successive heart beat electrical signals 23 and 24.
  • the signal from electrodes 21 is fed to a conventional differential amplifier 25 of the type commonly referred to as an ECG amplifier, having a high common mode rejection at sixty cycles and having a high input im- 4 pedance to not only minimize the flow of current through the electrodes, but additionally to compensate for the possibility of a pair of unbalanced electrodes.
  • the output of the amplier is then directed to a lilter 26 designed to have a center frequency of 30 cycles and a bandwidth of about 10i cycles toy remove the P and T waves and pass the remaining signal whichlargely is the QRS complex, illustrated in FIG. 3(b).
  • 30 cycles has been selected in the present embodiment as the center frequency of filter 26, it has been found that other center frequencies, i.e., 20 or 40 cycles are usable for obtaining a meaningful magnitude.
  • a pulse Shaper unit 27 such as the Schmitt trigger circuit which will respond to the leading edge of the input signal 3(1)) to provide output pulses of uniform duration and amplitude such. as impulses 23' and 24' shown in FIG. 3(0) representative of each QRS complex picked up by electrodes 21.
  • the impulses from pulse shaper 27 are applied to the input of an integrator 28 of a conventional type such as an integrating amplifier, in which a potential increment is accumulated on a storage element (i.e. a condenser) proportional in value to the number of applied impulses representative of heart-beat from pulse shaper 27, to provide an output representative of heart-rate, which heart-rate is determined over a period equivalent to the RC time constant of integrator '28.
  • the integration time constant (T) selected for the present embodiment is eight seconds, which time duration permits good meter displays of heart-beat rates from approximately thirty to two hundred beats per minute with a slowing rate in the neigborhood of ten beats per second.
  • Such a time constant value has also been found sufficiently adequate to provide for ready observation of abnormal steady heart rates while at the same time virtually enabling normal varying heart-rates to be ignored, as these latter type heart rates become unnoticeable by being averaged out at such an integrating period (T).
  • T integrating period
  • eight seconds has been selected for the present embodiment other integration time values for use ⁇ with neo-natals may be successfully utilized such as any value between, for example, five to twenty seconds.
  • the heart-beat electrical signals 23, 24 in FIG. 3(a), and similarly the impulses 23', 24 in FIG. 3(c) are but two of a long series or train of electrical signals picked-up during patient monitoring over an extended period of time.
  • the heart-rate of the patient being monitored, immediately prior in time to heart-beat impulse 23' is x heart-beats per period (T); then, in FIG. 3(d) the waveform 219 commencing at point x would be representative of the heart-rate output at integrator 28. It is observed that the trend of the heart-rate waveform 29 is positively altered at point y as at this point the potential of impulse 24 is charging the capacitor of the RC integrating time constant.
  • the meter 31 might be a galvanometer of the dArsonval type which for convenience, is adjusted to provide for a heart-rate reading in heart-beats per minute rather than heart-beats per an eight second period (T).
  • Sensor unit 32 is an adjustable threshold circuit adapted to respond to occurrences when the heart-rate of the patient being monitored falls below a certain prescribed frequency level or threshold based on the Period (T) at which the heart-rate is being evaluated as denoted by the output of integrator 28. Assuming a prescribed low heart-rate level is z as indicated in FIG. 3(d) by a dashed line, it is observed that waveform '29 will dip below the prescribed threshold z at crossing point v and remains below until crossing point w. As depicted in FIG. 3( e) sensor 32 will respond to heart-rate values at the output of integrator 2S below z to provide an output pulse 35 during the time duration between points v and w.
  • sensor 32 is then connected to one input of an AND gate 33.
  • a biased zero crossing detector which basically acts as a differential voltage comparator.
  • the voltage output signal of integrator 28 is compared with the reference voltage z to produce, in the present embodiment, a digital one, denoted as 33 in FIG. 3(e), lwhen the reference voltage input z is greater than the voltage output signal from integrator 28.
  • a value of z found to be suitable would be equivalent to a low level frequency of about ninety heart-beats per minute.
  • impedance pneumograph arrangement including a pair of physiological electrodes 34 connected to a high frequency current source 35 to provide a high frequency carrier amplitude modulated respiration signal of the type disclosed in FIG. 3(1).
  • impedance pneumography is only one of many techniques which may be ut1- lized in connection with the present invention for providing an electrical signal indicative of respiratory activity. Such other techniques might include the tidal volume approach or a strain gauge taped directly on the abdomen.
  • the filtered amplitude modulated signal is then supplied to a demodulator 38 to provide an output demodulated signal such as that depicted in FIG. 3(g), which signal is fed into a zero-crossing detector 39.
  • pulses of uniform amplitude and polarity are generated from the zero crossing detector in response to crossing of the zero axis by the output signal of demodulator 38.
  • the output of zero crossing detector 39 is connected to a pulse shaper 41 such as a D.C.
  • One leg of the output lead of pulse shaper 41 is connected to an adjustable time delay one-shot multivibrator 43 which basically will generate an output impulse when the duration between successive input impulses 42 will exceed a predetermined time interval denoting absence of the breathing function or a respiratory arrest for at least the pre-set predetermined time interval.
  • the multi- Vibrator would include an adjustable RC circuit, the capacitor charging up at a known rate during the absence of input impulses and discharging upon the presence of an input impulse such as 42 whereby should the charging capacitor exceed a pre-adjusted lvoltage level n as shown at n', a predetermined time interval z reltaed to such voltage would be arrived at or exceeded prior to occurrence of a successive input pulse 42, and the multivibrator would typically respond to provide an output impulse 44 as illustrated in FIG. 3(k), until return of the breathing activity represented by a successive input impulse 42 appearing at the input of multivibrator 43. Suitable time periods for which 43 is adjustable have been found to be fifteen, thirty or forty-five seconds.
  • the output of multivibrator 43 is connected as a second input to AND gate 33 so that when positive output signals depicted at FIGS. 3(e) and 3(k) are simultaneously present at the input of AND gate 33 from the output of sensor 32 and multivibrator 43 to respectively denote a low heart rate and absence of breathing exceeding a pre-selected time interval, then AND gate 33 will be enabled to pass a signal through OR gate 45 and energize the alarm 46 to indicate the existence of a condition of respiratory distress.
  • the alarm might either be of the audible or light signaling type, or both.
  • the second leg of its output is connected to an integrator 47 similar to integrators 28 except that integrator 47, in the present embodiment is provided with an RC integrating time constant of thirty seconds to enable a good meter display of respiration rates from as low as fifteen beats per minute to 250 beats per minute.
  • integrator 47 in the present embodiment is provided with an RC integrating time constant of thirty seconds to enable a good meter display of respiration rates from as low as fifteen beats per minute to 250 beats per minute.
  • the respiration-rate of the patient being monitored immediately prior in time to impulses 42 is x breaths per period (thirty seconds); then, the waveform 48 commencing at point x would be representative of the respiration-rate output at integrator 47. It is noted that the trend of the respiration-rate waveform 48 is positively altered at point y' as at this point the potential of the second illustrated impulse in FIG. 3(1') is charging the capacitor of the RC integrating time constant.
  • meter 49 Connected at the output of integrator 47 are two units, one a meter 49 and the other a low limit sensor 51.
  • the meter similar to meter 31, might be of the dArsonval type which is suitably adjusted to provide a respirationrate reading in breaths per minute as opposed to breaths per thirty second period.
  • Sensor unit 51 comprises a conventional adjustable threshold circuit similar in operation to sensor unit 32 hencetofore discussed whereby the sensor will be triggered when the respiration rate of the patient being monitored, based on the integrated output of integrator 47, falls below a certain prescribed frequency level, a Isuitable frequency level havin-g been found to be eighteen breaths per minute.
  • a certain prescribed frequency level to be equivalent to a voltage level z' illustrated in FIG. 3(1)
  • the sensor unit 51 will be triggered to provide au output Signal i.e., a digital one on lead 52.
  • an output signal will appear at lead S3.
  • a Schmitt trigger a zero crossing detector, or similar suitable type unit may be utilized for sensor 51.
  • Output leads 52 and 53 of sensor unit 51 are connected to a suitable timer unit 54 having in the preferred ernbodiment an RC time constant of sixty seconds, the timer cycle, initiated by charging of the capacitor, being enabled by an output signal from sensor 51 on lead 52, and the timer adapted for reset by an output signal from sen-sor 51 on output lead 53 to cause the capacitor to discharge. If timer 54 is not reset by the end of a sixty second period the timer will be enabled to provide an Output signal 55 as depicted in FIG. 3(m) which signal is passed through OR gate 45 to trigger alarm 46.
  • the signals upon receiving from the patient heart-beat activity signals such as those illustrated in FIG. 3(a) the signals are amplified and filtered by ECG amplifier 25 and lter 26 respectively, and then translated into pulses of equal amplitude and width as depicted in FIG. 3(c).
  • high frequency respiratory activity signals are received such as those shown in FIG. 3(1), which signals are demodulated as appearing in FIG. 3(g) and each crossing of the zero axis by the demodulated signal is detected to ⁇ generate a series of related positive pulses as represented in FIG. 3(11), each of the pulses being shaped by a pulse shaper 41 to provide, as depicted in FIG. 3(1'), pulses 42 having sharp lead edges uniform amplitude and duration.
  • the pulse shaper 27 and 41 outputs, respectively representing heart beat activity and respiratory activity, are each separately fed to a box 30 ⁇ (represented as 14 in FIG. l) wherein the heart beat-respiration interaction detection is carried out to detect existence of a respiratory distress condition, if present.
  • the heart-beat pulse representations are fed into an integrator 28 which continuously integrates over an eight second time period to provide an output as illustrated in FIG. 3(d).
  • FIG. 4 disclosing over a longer period of time a typical EKG signal 56 that would be fed to amplifier 2S, and the lower waveform 57 represents an output heart rate waveform that would be generated by integrator 28. Note the increase in heart rate at 58 with the relative frequency increase in heart beat activity at 59.
  • the second input to AND gate is a respiratory activity signal fed from pulse shaper 41 via the adjustable time delay multivibrator set at say fifteen seconds so that a signal will appear at AND gate 33 when the timefinterval between the leading edges (or even trailing edges) of successive pulse from pulse shaper 41 equals or exceeds the preadjusted period of fifteen seconds to indicate presence of a respiratory arrest,
  • the AND gate will be enabled to activate alarm 46 noting the presence of a respiratory distress condition and thus the need by the neo-natal patient for immediate attention.
  • FIG. shows heart rate 61 and respiration rate 62 waveforms being the respective outputs of integrators 28 and 47. It is observed that the integrated heart rate waveform 61 will fall below the ninety heart beats per minute low level between points 63 and 63, during which time a signal is present at one input to AND gate 33. It is also noted that the integrated respiration rate value 62 has a smooth discharge trend between points 64 and 64 denoting the absence of any breath during this period as otherwise an output pulse from a shaper 41 would positively alter this portion of waveform 62.
  • low limit sensor 51 and timer delay 54 was described with reference to FIG. 2.
  • this low rate will be sensed by level sensor 51 which will respond by providing an output signal to trigger or start timer delay 54.
  • level sensor 51 which will respond by providing an output signal to trigger or start timer delay 54.
  • the low respiratory rate continue for a period equal to at least sixty second timer delay 54 will be enabled, as illustrated at 55, in FIG. 3(m), to activate alarm 46 via OR gate 45.
  • 5 waveform 62 represents the output of integrator 47, along which at point 67 the rate will fall below eighteen breaths per minute to trigger timer delay 54, however, since the rate stays below eighteen breaths per minute for twelve seconds until point 68, the low limit level sensor S1 will be de-energized and the timer delay 54, by way of lead 53, will be reset.
  • An apparatus for monitoring a respiratory distress condition through the physiological functions of heart beat and breathing comprising:
  • timing means responsive to said respiratory activity electrical signal to detect a respiratory arrest exceeding a pre-selected time interval.
  • sensor means responsive to the heart beat activity electrical signal for producing a signal upon the occurrence of successive heart beats below a preselected frequency level.
  • a first pulse generator means adapted for connection to a patient by a suitable transducer means for deriving said electrical signal representative of heart beat activity
  • a second pulse generator means adapted for connection to the patient by a suitable transducer means for deriving said electrical signal representative of respiratory activity.
  • said sensor means includes:
  • sensor means responsive to the heart beat activity electrical signal for producing a signal upon the occurrence of successive heart beats Ibelow a pre-selected frequency level.
  • a monitoring apparatus for use with newborns for detecting respirator distress by investigating the physiological functions of heart -beat and breathing comprising:
  • first generating means adapted for deriving from a newborn electrical impulses representative of heart beat activity
  • second generating means adapted for deriving from the newborn electrical impulses representative of respiratory activity
  • sensor means responsive to said heart beat rate to provide an output when heart beat rates are sensed below a preselected heart beat frequency, timing means responsive to said second generating means to provide an output signal when a respiratory arrest exceeds a preselected time interval,
  • a monitoring apparatus wherein said indicator means includes: j.
  • a monitoring apparatus according to claim 8 whereby:
  • said timing means is adjustable and may be set for detecting a respiratory arrest exceeding a time interval anywhere ybetween fifteen and forty-ve seconds.
  • a monitoring apparatus according to claim 8 wherein:
  • said integrating means is adapted to continuously provide a heart beat rate output representative of heart beat activity over a period of anywhere from approximately five to twenty seconds.
  • a monitoring apparatus according to claim 8 wherein:
  • said relating means includes an AND gate enabled upon simultaneous occurrence of an output from said sensor means and said timing means.
  • a monitoring apparatus including:
  • a monitoring apparatus including:
  • a monitoring apparatus responsive to said relating means and said second sensor means.
  • said second sensor means includes timer delay means activated by respiration rates below said preselected respiration frequency to provide an output signal subsequent to a pre-established time interval and whereby said timer delay means is deactivated and reset when respiration rates exceed said preselected respiration frequency.
  • said second integrating means integrates said respiratory impulses over a time period of anywhere between twenty-ve to forty-five seconds. 17.
  • a monitoring apparatus according to claim 16 wherein:
  • said pre-established time interval of said timer delay means is approximately sixty seconds.

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US764448A 1968-10-02 1968-10-02 Respiratory distress monitor Expired - Lifetime US3572317A (en)

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Cited By (36)

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Publication number Priority date Publication date Assignee Title
US3678296A (en) * 1970-04-14 1972-07-18 American Optical Corp Electrical signal slope polarity change detector
US3727606A (en) * 1970-06-12 1973-04-17 Airco Inc Apnea detection device
US3814082A (en) * 1971-03-18 1974-06-04 Nat Res Dev Patient monitoring systems
US3848591A (en) * 1971-11-02 1974-11-19 Philips Corp Electronically-controlled gas pressure meter
US3942516A (en) * 1974-03-18 1976-03-09 Cyborg Corporation Biofeedback training method and system
US3976052A (en) * 1974-04-19 1976-08-24 Hewlett-Packard Gmbh Respiration monitor
US4031884A (en) * 1974-06-07 1977-06-28 Institut National De La Sante Et De La Recherche Medicale Apparatus for correlating the respiratory and cardiac cycles
US4088138A (en) * 1974-01-02 1978-05-09 Cardiac Resuscitator Corp. Cardiac resuscitator and monitoring apparatus
FR2420332A1 (fr) * 1978-03-20 1979-10-19 Univ Groningen Appareil a detecteur l'activite des organes respiratoires et du coeur d'un etre vivant
EP0012530A1 (de) * 1978-11-24 1980-06-25 Kenneth Layne Kearns Atemstillstandsmonitor
USRE30750E (en) * 1972-05-15 1981-09-29 Cardiac Resuscitator Corporation Cardiac resuscitator and monitoring apparatus
US4306567A (en) * 1977-12-22 1981-12-22 Krasner Jerome L Detection and monitoring device
US4379460A (en) * 1980-09-18 1983-04-12 Judell Neil H K Method and apparatus for removing cardiac artifact in impedance plethysmographic respiration monitoring
US4422458A (en) * 1980-04-28 1983-12-27 Montefiore Hospital And Medical Center, Inc. Method and apparatus for detecting respiratory distress
US4506678A (en) * 1982-06-07 1985-03-26 Healthdyne, Inc. Patient monitor for providing respiration and electrocardiogram signals
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US4580575A (en) * 1982-06-14 1986-04-08 Aequitron Medical, Inc. Apnea monitoring system
US4611998A (en) * 1980-12-08 1986-09-16 Board Of Regents, University Of Texas System Simulator for teaching neonatal resuscitation
US4630614A (en) * 1984-04-08 1986-12-23 Dan Atlas Apnea monitoring apparatus
US4648407A (en) * 1985-07-08 1987-03-10 Respitrace Corporation Method for detecting and differentiating central and obstructive apneas in newborns
US4657025A (en) * 1981-12-09 1987-04-14 Carl Orlando Heart and breathing alarm monitor
FR2589713A1 (fr) * 1985-11-08 1987-05-15 Gradient Appareil de detection d'insuffisance cardio-respiratoire
US4665926A (en) * 1984-11-17 1987-05-19 Hanscarl Leuner Method and apparatus for measuring the relaxation state of a person
US4685461A (en) * 1981-11-25 1987-08-11 Dornier System Gmbh Apparatus and method for triggering shock waves in lithotripsy
US4803997A (en) * 1986-07-14 1989-02-14 Edentec Corporation Medical monitor
US4813427A (en) * 1986-02-17 1989-03-21 Hellige Gmbh Apparatus and method for preventing hypoxic damage
US4915103A (en) * 1987-12-23 1990-04-10 N. Visveshwara, M.D., Inc. Ventilation synchronizer
US4930518A (en) * 1988-09-26 1990-06-05 Hrushesky William J M Sinus arrhythmia monitor
US4982738A (en) * 1988-11-30 1991-01-08 Dr. Madaus Gmbh Diagnostic apnea monitor system
US5022402A (en) * 1989-12-04 1991-06-11 Schieberl Daniel L Bladder device for monitoring pulse and respiration rate
US5042499A (en) * 1988-09-30 1991-08-27 Frank Thomas H Noninvasive electrocardiographic method of real time signal processing for obtaining and displaying instantaneous fetal heart rate and fetal heart rate beat-to-beat variability
US6129675A (en) * 1998-09-11 2000-10-10 Jay; Gregory D. Device and method for measuring pulsus paradoxus
EP1330184A1 (de) * 2000-10-06 2003-07-30 Biomedical Acoustic Research, Inc. Akustischer nachweis von atemwegserkrankungen
EP1556834A2 (de) * 2002-10-03 2005-07-27 Scott Laboratories, Inc. Systeme und verfahren zur bereitstellung von sensorfusion
CN115919255A (zh) * 2022-11-22 2023-04-07 飞依诺科技股份有限公司 识别睡眠呼吸暂停低通气类型的方法、呼吸机及存储介质
US11766537B2 (en) * 2016-07-22 2023-09-26 Fisher & Paykel Healthcare Limited Sensing for respiratory circuits

Families Citing this family (4)

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Publication number Priority date Publication date Assignee Title
DE2235420C3 (de) * 1972-07-19 1981-04-23 Siemens AG, 1000 Berlin und 8000 München Rheograph
US3835839A (en) * 1972-12-08 1974-09-17 Systron Donner Corp Impedance plethysmograph and flow rate computer adjunct and method for use therewith
US4305400A (en) * 1979-10-15 1981-12-15 Squibb Vitatek Inc. Respiration monitoring method and apparatus including cardio-vascular artifact detection
DE3339277A1 (de) * 1983-10-28 1985-05-09 Hans 8929 Schwabsoien Berkmüller Heuwerbungsmaschine, insbesondere kreiselheuer

Cited By (43)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3678296A (en) * 1970-04-14 1972-07-18 American Optical Corp Electrical signal slope polarity change detector
US3727606A (en) * 1970-06-12 1973-04-17 Airco Inc Apnea detection device
US3814082A (en) * 1971-03-18 1974-06-04 Nat Res Dev Patient monitoring systems
US3848591A (en) * 1971-11-02 1974-11-19 Philips Corp Electronically-controlled gas pressure meter
USRE30750E (en) * 1972-05-15 1981-09-29 Cardiac Resuscitator Corporation Cardiac resuscitator and monitoring apparatus
US4088138A (en) * 1974-01-02 1978-05-09 Cardiac Resuscitator Corp. Cardiac resuscitator and monitoring apparatus
US3942516A (en) * 1974-03-18 1976-03-09 Cyborg Corporation Biofeedback training method and system
US3976052A (en) * 1974-04-19 1976-08-24 Hewlett-Packard Gmbh Respiration monitor
US4031884A (en) * 1974-06-07 1977-06-28 Institut National De La Sante Et De La Recherche Medicale Apparatus for correlating the respiratory and cardiac cycles
US4306567A (en) * 1977-12-22 1981-12-22 Krasner Jerome L Detection and monitoring device
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FR2019727A1 (de) 1970-07-03
GB1290537A (de) 1972-09-27
BE739664A (de) 1970-04-01
NL6914723A (de) 1970-04-06
IL33011A0 (en) 1969-11-30
CH512236A (de) 1971-09-15
DE1949445A1 (de) 1971-01-14
AT298663B (de) 1972-05-25

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