|Publication number||US3658060 A|
|Publication date||Apr 25, 1972|
|Filing date||Aug 19, 1969|
|Priority date||Aug 19, 1969|
|Publication number||US 3658060 A, US 3658060A, US-A-3658060, US3658060 A, US3658060A|
|Inventors||Eklof Anders A|
|Original Assignee||Bendix Corp|
|Export Citation||BiBTeX, EndNote, RefMan|
|Patent Citations (8), Referenced by (21), Classifications (4), Legal Events (3)|
|External Links: USPTO, USPTO Assignment, Espacenet|
United State-s Patent Eklof  AUDIBLE BLOOD PRESSURE MONITOR  inventor: Anders A. Eklof, Baltimore, Md.
 Assignee: The Bendix Corporation  Filed: Aug. 19, 1969  Appl.'N0.: 855,072
 US. Cl. ..128/2.05 A  ..Afilb 5/02 Field of Search ..128/2.05 A,-2.05 D, 2.05 F, 128/205 G, 2.05 M, 2.05 P, 2.05 O, 2.05 R, 2.05 T, 2.06 A, 2.06 F, 2.06 R, 2.1 A
 Reierences Cited UNITED STATES PATENTS 2,821,188 1/1958 Pigeon ..128/2.05 3,002,185 9/1961 Bases .....128/2.05 S 3,126,885 3/1964 Hinman 128/205 M 3,227,155 1/1966 Erickson et al 128/205 R 3,412,729 11/1968 Smith, .11 l28/2.05 R
[451 Apr. 25, 1972 3,510,765 5/1970 Baessler ..l28/2.06A
Primary Examiner-William E. Kamm Attorney-Pl'ante, Arens, Hartz, Hix & Smith, Bruce L. Lamb and William G. Christoforo [5 7] I ABSTRACT.
- the audio signal is proportional to blood pressure deviation from the normal and any rhythmic variation in pitch is proportional to heart beat rate. I An alarm circuit includes a capacitor which is charged by variations in blood pressure characteristic of .heat beats. in heart beat ceases the capacitor is discharged and one of the pulse trains is blocked from the subtraction circuit so that the resultant audio signal is a loud monotone signal which decays as blood pressure drops.
3,453,546 7/1969 Fryer ..128/2 1 A 3,467,837 9/1969 Vick .;....128/2.05 Q 6 Claims, 5 Drawing Figures 2: ALARM AMPLIFIER SIGNAL PULSE MUTlNG TRANSDUCER T CONDlTlONER GENERATOR cmcun I I2 1 I I0 |4 15 3o LOUDSPEAKER CONTROL KNOB PATENTEDAPR25|972 3,658,060 SHEET 30F 3 OUTPUT OF PULSE T T T H H H GENERATOR l5 7 OUTPUT OF FLIP- FLOP l7 OUTPUT OF ONE- SHOT l8 LOUDSPEAKER 3O INPUT FIG. 3
OUTPUT OF amamom 1 1 "1'1 1 1 w 1 OUTPUT OF FLIP-FLOP I7 OUTPUT OF ONE-SHOT I8 LOUDSPEAKER "Q I H T C". 30 INPUT INVENTOR ANDERS A. EKLOF ATTORNE This invention relates to means for monitoring blood pressure and heart beat and more particularly to such a monitor which will generate an audible signal containing information both as to blood pressure and heart beat rate and which will automatically provide an alarm signal should heart beat become arrhythmic or cease.
The usual method of monitoring arterial and venous blood pressure during surgery involves the cannulation of the patients arteries and veins. These cannula are attached to strain gauges comprising the interface with electronic circuits that display the pressure on an oscilloscope as a vertical displacement of the oscilloscope trace from a base line. This displacement is calibrated in millimeters of mercury pressure. Patient heart beats, which produce momentary blood pressure spikes, are displayed as spikes on the oscilloscope trace. It isdifficult, if not impossible, for the operating surgeon to monitor the oscilloscope directly since he must be concerned with the operation, itself. It is also impractical for personnel in the operating room to monitor the oscilloscope since it is an extremely boring job, especially when all parameters appear to be normal. It has been found by experience that the oscilloscope cannot be monitored continuously by operating room personnel regardless of skill or assignment without their attention being diverted to other problems within the operating room.
Conventional electrocardiographic apparatus has also been used to monitor heart action with the electrocardiographic apchanged, the pulsewidth of the square wave changes but the monostable output pulsewidth remains thesame. Thus, by subtracting the one-shot pulse from the square wave, an output results which is comprised of a train of pulses of a frequency equal to that of the square wave and having a width proportional to the change in blood pressure from the normal set value. The resultant pulse train is fed to a loudspeaker where paratus being connected to an oscilloscope to visually display both heart beat rate and blood pressure or connected to audio apparatus for generatingan audible signal containing information only as to heart beat rate.
SUMMARY OF THE INVENTION Means for providing an audio signal which contains information both as to blood pressure and heart beat could be 'advantageously employed to monitor the cardiac condition of a patent. It would also be advantageous if the aforementioned audible signal is muted whenever the heart action is normal so as not todistract operating personnel. It would also be advantageous to provide means which would sound alarm whenever an arrhythmia developes.
The aforementioned advantages are provided by the present invention. The invention herein resides in electronic circuitry which is interfaced with a patient by some sort of telemetering device which generates an electrical signal whose'magnitude is proportional to blood pressure. As aforementioned, this telemetering device can be a strain gauge attached to a cannula which is inserted into the patients artery or vein, depending on whether the patients arterial or venous pressure is to be monitored. The'electrical signal generated by the strain gauge will follow the blood pressure For example, in a person with a blood pressure of I20 systolic over 80 diastolic the pressure before the heart contracts would be 80 millimeters of mercury and would be raised by contraction of the heart to 120 millimeters of mercury and at the cessation of the heart beat the pressure would slowly fall back to 80 millimeters of mercury to be repeated periodically at the heart beat rate. The voltage level output of a strain gauge telemetering device will track the blood pressure approximately linearly. The strain gauge output controls the repetition rate of a pulse generator to thus generate a first pulse train whose pulse repetition frequency is proportional to blood pressure. The frequency form the pulse generator is then divided by 2 yielding a square wave of 50 percent duty cycle if the blood pressure, that is the output of the strain gauge, remains constant. The square wave triggers a one-shot having a pulsewidth which is settable by a calibrated knob. For a selected normal value of blood pressure the pulsewidth can be made equal to that ofthe square wave so that if subtracted, the two signals cancel. If the pulse generator frequency should change, indicating that blood pressure has the resultant pitch of thesound indicates blood pressure and the strength of the sound is proportional to the deviation of the blood pressure from the normal setting. This is so because the power contained in a pulse train is proportional to the width of the pulses which, as has been mentioned, is related to the deviation of the blood pressure from a set normal value.
Of course, as the heart beats the blood pressure will vary over its normal systolic and diastolic range. This will be evidenced by the electronic circuitry by its production of an audible signal whose pitch and intensity will both increase as the heart contracts and whose pitch and intensity will decrease as the heart relaxes. Since both change of pitch and changes of sound intensity can be used to indicate heart beat a muting circuit is provided which suppresses the changes in sound intensity solong as the blood pressure remains within acceptable limits, so that the sound level is kept low even if the patients blood pressure drifts up and down within certain limits while the change in sound pitch is monitored to provide an indication of heart beat rate.
An alarm circuit is also provided which sounds an alarm if heart beat should cease or the heart become arrhythmic. This is accomplished by the use of a discharge circuit which is charged by the voltage spikes output from the strain gauge caused by the contraction of the heart as it beats. This voltage enables a gate through which the pulse train whose pulse repetition frequency is proportional to blood pressure is fed to the subtraction circuit. If the heart beat ceases or the heart becomes arrhythmic the voltage spikes generated by the strain gauge in response to the contractions of the heart are no longer present and the voltage across the discharge circuit will discharge and disable the aforementioned gate. The subtraction circuit now only has an input from the one-shot and thus will generate an output having the highest possible energy content. A resultant high audio level monotone audible signal which decays as blood pressure drops comprises the alarm.
BRIEF DESCRIPTION OF THE DRAWINGS DESCRIPTION OF TI-IE PREFERRED EMBODIMENT Referring first to FIG. 1, a block diagram of the invention, there is seen a transducer 10, suitably a strain gauge, which interfaces with the blood stream of a patient and generates a voltage output proportional to blood pressure at input terminal 12 of the blood pressure monitor. The signal on input terminal 12 is applied to signal conditioner 14, which is basically an'amplifier with variable sensitivity to accept a wide range of input voltages. Signal conditioner output is a DC voltage level proportional to input voltage and is applied to pulse generator 15 which in response thereto generates a train of pulses whose pulse repetition frequency is proportional to its input voltage. This pulse train is applied to a divide by 2 multivibrator, suitably flip-flop 17, connected as a binary divider. The output of flip-flop I7 is a square wave having a duty cycle of 50 percent so long as blood pressure remains constant. Should the blood pressure change, for example increase, the voltage input to signal conditioner 14 also increases, thus increasing the pulse repetition frequency for the pulse train ap-- plied to flip-flop 17 so that the frequency of the square wave output from flip-flop 17 increases and its pulse width decreases. Flip-flop 17 output pulse train is applied to oneshot 18 which is triggered on by the leading edge ofthe pulses. The width of the one-shot output pulse is variable, for reasons which will be made obvious later, by manipulation ofa control knob 19 which adjusts means not shown here but which will be shown below. The output pulses from one-shot 18 are applied to exclusive Or gate 20.
' The output signal from signal conditioner 14 is also applied to alarm circuit 21 which includes a discharge circuit which is charged by the rapid variations in the signal conditioner output signal which are characteristically present while the heart is beating. So long as the discharge circuit is being charged the alarm circuit generates an output along line 22 to And gate 25 thereby qualifying this latter gate. The output pulse train from flip-flop 17 is applied along line 23 to And gate 25 which, when qualified, passes this pulse train to exclusive Or gate 20. Thus, so long as the heart is beating exclusive Or gate 20 receives as inputs the pulse. train from one-shot 18 and the pulse train from flip-flop 17. Exclusive Or gate 20 will pass a signal therethrough when only one of its input terminals is energized and will pass no signal therethrough when both or neither of the input terminals are energized. Exclusive Or gate 20 thus operates as a subtraction circuit to. subtract the pulse train generated by one-shot 18 from the pulse train generated by flip-flop 17. If, at some normal valve of blood pressure, the output pulse from one-shot 18 is made equal in length to the pulse generated by flip-flop 17, exclusive Or gate 20 will pass no signal therethrough. However, if the heart is beating, it is known that the blood pressure will vary during each heart between its systolic and diastolic pressures so that there is generally some output from exclusive Or gate 20 whose energy content is indicative of heart beat rate. Additionally, since the output pulse train of pulse generator is a pulse repetition frequency which is related to blood pressure, the pulse repetition frequency of the signal output of exclusive Or gate will vary in accordance with the heart beat. 'A muting circuit 27 widens the range over which the output from exclusive Or gate 20 is suppressed. The width of this range is normally set by a potentiometer'as will be later shown. With this potentiometer set to zero, the output from the exclusive Or gate is zero only when the input pulses thereto are exactly the same width. Since the exclusive Or gate output pulsewidth gradually increases with increasing difference between the input pulses, the power contained in the output also gradually increases. The effect is that the resultant null notch has sides where a gradual increase in signal is obtained as the frequency of the pulses deviates from the point where their pulsewidths are equal. This in itself provides a muting in the immediate vicinity of the null point, but the range is rather narrow. If it is desired to keep the signal level low until certain blood pressure limits arereached, the potentiometer can be varied to give up to 100 percent muting range. The signal from the muting circuit 27 is applied to loudspeaker 30 through amplifier 28 so as to generate an audible signal whose intensity is related tothe deviation of blood pressure from a preset normal value and whose change in pitch is indicative of heart beat.
As previously mentioned, alarm circuit 21 includes a discharge circuit which is charged by the rapid variations in the output signal from signal conditioner 14 which are produced by the rapid fluctuations in blood pressure characteristic of the heart beat. Should the heart cease to beat or become arrhythmic these rapid signal variations will cease and the discharge circuit will discharge and remove the signal from line 22, thus closing gate 25. The output pulse train from flipflop 17 will thus be blocked by gate and only the pulse train from one-shot 18 will be applied to exclusiveOr gate 20. This latter pulse train will thus pass directly therethrough so as to cause loudspeaker 30 to generate a continuous high level monotone audible signal which slowly decays as blood pressure drops.
Referring now to FIG. 2A the blood pressure signals generated by the pressure transducer are applied to input terminal 12 of the blood pressure monitor. These signals are applied across resistor and applied via adjustable resistor slider 40:: to the.gate electrode of field effect transistor.
The adjustment of slider 40a permits the monitor to accept a wide range of'input signal voltages. Resistor 40 is chosen to be a large value and this fact, together with the use of field effect transistor 41 results in the input terminal 12 having a high input impedance thus preventing loading of the transducer. Transistors 41 and 42 are differentially connected and together comprise an amplifier with the amplifier output being taken from the collector electrode of transistor 42. Transistor 42 receives an adjustable bias at its base electrode from the voltage divider comprised of resistor 44 and potentiometer 45 serially connected between a source of A+ voltage and ground. By the manipulation of potentiometer 45 the bias at the base electrode of transistor 42 may be varied so as to change the amplifier output voltage level at the collector of transistor 42. Filter capacitor 46 removes high frequencies from the amplifier output so as to reduce noise and interference. The output from the signal conditioner 14 is applied to the time constant circuit comprised of resistor 47 and capacitor 48 in the pulse generator 15. Unijunction transistor 50, together with resistor 47 and capacitor 48 comprise a pulse generator with the unijunction becoming conductive to discharge capacitor 48 whenever the voltage thereacross reaches the unijunction trigger level. The resultant pulse appears across the voltage divider comprised of resistors 51 and 52 and is coupled via resistor 51 and capacitor 53 in parallel to the toggle input C of flip-flop 17. This latter circuit element is well known to those skilled in the art and its schematic need not be shown for a complete understanding of the invention. Each output pulse from pulse generator 15 causes flip-flop 17 to complement so that its output is'comprised of a pulse train having an approximately percent duty cycle.
The flip-flop output pulse train is applied to the one-shot comprised of transistors and through capacitor 55 and diode 56 so that the one-shot is triggered on positive voltage excursions. The one-shot output pulsewidth, which is determined by the resistance of potentiometer 63 and resistor 62 and capacitor 61, can be varied by the adjustment of potentiometer 63 which is coupled to knob 19 seen in FIG; 1. The one-shot output pulse train appears at terminal E while the flip-flop output pulse train appears at terminal D.
The output of signal conditioner 14 is also applied to the alarm circuit 21 at the gate electrode of field effect transistor 70. The use of a field effect transistor at this point presents a high impedance to the output of the signal conditioner thus preventing excessive loading of that circuit. The amplified outputof transistor is picked off resistor 71 by resistor slider 71a and capacitively coupled through capacitor 73 to the base electrode of transistor 78. This latter transistor receives a DC bias from the voltage divider comprised of resistors 75 and 76 connected across the A+ voltage supply.
' Output is taken from the collector of transistor 78 and capacitively coupledto the diode circuit comprised of diodes 80 and 81' at the base oftransistor Capacitor 72 eliminates electrical noise which may be present on slider 71a while, capacitors 73 and 79 insure that only rapid variations in blood pressure characteristic of a heart beat are effective at the base of transistor 85' so as to hold that transistor non-conductive so that its collector electrode and hence terminal G are disconnected from ground. However, should the heart stop or become arrhythmic, rapid variations in blood pressure are no longer present, thus the negative charge across capacitor 84' will leak off through resistor 83 until transistor 85 becomes conductive,at which time terminal G will be'grounded.
Referring now to FIG. 25, wherein exclusive Or gate 20 and And gate 25 are'seen to be comprised of transistors 80, 81, 83 and 85 and diodes 82 and 84. The operation of these gates is such as to provide a current sink at the input of muting circuit 27 whenever the gates are open. The pulse train from one-shot I8 is applied to terminal E and hence to the base electrode of transistor 80 while the pulse train of flip-flop 17 is applied to terminal D and hence to the base of transistor 85. With signal present on both terminals E and D, transistors 80 and 85 are both conductive so that their respective'collector electrodes are grounded, thus grounding the base electrodes of transistors 81 and 83 holding these latter transistors non-conductive and hence no current can flow therethrough, thus presenting a closed gate condition to muting circuit 27. With the signal present on either terminal E or terminalD, but not both, for example, with a signal on terminal E and no signal on terminal D transistor 80 is conductive while transistor 85 is non-conductive, thus grounding the collector electrode of transistor 80. Transistor 81 is thus non-conductive, however, transistor 83 is conductive and current can flow therethrough and trough diode 84 and transistor 80 to ground, thus indicating the gate open condition to muting circuit 27. Of course, since the circuit is symmetrical, the presence ofa signal at terminal D and the absence of .a signal at terminal E accomplishes the same gate open condition.
It will be remembered that in the absence of a heart beat or in the presence of an arrhythmic heart condition, terminal G is grounded thus grounding the base electrode of transistor 81'. This effectively eliminates any signal at terminal E from effecting the gating circuit. Thus, the pulse train from flip-flop l7 appearing on terminal D will be fully effective to open the gating circuit so as to present a current sink to muting circuit 27.
As the width of the pulses from the exclusive Or gate 20 goes up, the DC level of the pulse train goes up. It will be remembered that the output of the exclusive Or gate is zero only when the pulse train from flip-flop l7 and one-shot 18 are identical and that this occurs only at some normal present value of blood pressure but that this normal preset value of blood pressure occurs only momentarily during each heart beat. It will also be remembered that the pulse train passed by the exclusive Or gate contains redundant information as to heart beat in that this latter pulse train includes the heart beat information in both its DC level and its pulse repetition frequency. Muting circuit 27 is provided to increase the width of the null in which the pulse train from the exclusive Or gate is muted. Muting circuit 27 is comprised of the amplifier transistors 90 and 92, to the base electrodes-of which the output from the exclusive Or gate is applied, a comparator in the form ofa differential amplifier comprised of transistors 96 and 97, and a switching transistor 93. The null width over which the pulse train from the exclusive Or gate ,is muted is determined by the setting of potentiometer 99, which sets the bias' on the base electrode of transistor 97, which comprises the threshold level of the comparator comprised of transistors 96 and 97. As already mentioned, the output from the exclusive Or gate is applied to the base electrode of transistor 92 wherein it is amplified and applied through the integrating circuit comprised of resistor 87 and capacitor 88 to the base electrode of transistor 96. The integrating circuit converts the amplified pulse train to a DC voltage level. So long as the DC level of the amplified pulse train remains below the comparator threshold level set by potentiometer 99 switch transistor 93 will be conductive and will prevent the pulse train from passing directly from amplifier transistor 90, resistor 95 and diode 94 to amplifier 28. During the time switching transistor 93 is conductive a portion of the signal from :amplifier transistor 99 is shunted to amplifier 28 and loudspeaker 30 through capacitor 91 so as to provide some background but muted audible signal indicative of the heart beat rate from loudspeaker 30. When the DC level of the amplified pulse train at the base electrode of transistor 96 exceeds the threshold value for the comparator, transistor 96 will turn on and transistor 97 will turn off, thus causing switching transistor 93 to become non-conductive. The signal from amplifier transistor 90 now passes directly through resistor 95 and diode 94 to the amplifier 28. Amplifier 28 is comprised of output transistor 100, diode 102 which protects the output transistor from inductive overshoots generated by the loud speaker when pulse driven and a volume adjusting potentiometer 103 connected across diode I02, that is, between the collector electrode of transistor 100 and ground. The signal tapped from potentiometer 103 drivesloudspeaker 30.
Referring now also to FIG. 3 wherein the letters C, D, E and F correspond to like indicated points in the circuitry of FIGS. 2A and 28, it can be seen that the output of pulse generator 15 g is comprised of a series of narrow pulses. The output pulse train of flip-flop 17, as seen at point D, is comprised ofa series of pulses having approximately percent duty cycle and whose leading edge coincides with the leading edge ofthe pulses at point C since flip-flop 17 is triggered by positive-going pulses, while the pulse train at point E is similarly synchronized with the pulse trains at points C and D, since the one-shot is triggered by the positive-going pulses at point D. It can further be seen that the pulse train at point E have been adjusted by potentiometer 63 to be identical to the pulse train at point D. The energy content of the loudspeaker 30 input at point F is thus zero.
Referring now to FIG. 4 wherein there is seen the waveforms of FIG. 3 after the blood pressure has increased somewhat from its normalpreset condition. It will be remembered that if blood pressure rises the pulse repetition frequency of the pulse train from pulse generator 15 will increase as can be seen by comparing line C of FIG. 4 with line C of FIG. 3. The pulse train output of flip-flop 17 as seen at line D will thus be comprised of shorter width pulses having a higher pulse repetition frequency. Of course, the pulse train generated by one-shot 18 would be comprised of pulses having the same width as in FIG. 3, but having the same pulse repetition frequencyas thepulse train at point D. Thus the pulse train at point E will have a duty cycle in excess of 50 percent. Subtraction of the pulse trains on lines D and E from one another results in the pulse train at line F, which is the pulse train applied to the loudspeaker 30 to generate the audible signal when the DC level of the waveform on line F is above the threshold set by potentiometer 99 in FIG. 28. If the DC level of the waveform on line F is below the threshold set by potentiometer 99 that part of the pulses above line 110 will be suppressed in that only that portion of the pulses below line 110 will be able to proceed from amplifier transistor to point F through capacitor 91 since switching transistor 93 will be conductive thus suppressing the pulse path through resistor 95 and diode 94.
The invention claimed is: I. A blood pressure monitor comprising: 7 means for generating a first pulse train having a pulse repetition frequency proportional to blood pressure and a duty cycle related to the rate of blood pressure change; adjustable means responsive to said first pulse train for generating a second pulse train having a pulse repetition frequency equal to the pulse repetition frequency of said first pulse train and synchronized therewith and including means for adjusting the pulsewidth of the pulses in said second pulse train, said second train pulsewidth thereafter remaining constant;
means combining said first and second pulse trains for generating an output signal; and,
utilizations means responsive to said output signal for monitoring said blood pressure.
2. A-blood pressure monitor as recited in claim I with additionally muting means for attenuating said output signal when said output signal is below a predetermined threshold.
3. A blood pressure monitor as recited in claim 2 wherein said muting means includes means for varying said predetermined threshold.
4. A blood pressure monitor as recited in claim 1 wherein said combining means comprises means for subtracting one of said first and second pulse trains from the other of said pulse trains to produce a third pulse train comprising said output 7 8 means integratingsaid third pulse train for generating a DC 6 A blood pressure monitor as recited in claim 4 with addivoltage; tionally: threshold means fsponslble to 531d DC Voltage for generat" means integrating said third pulse train for generating a DC ing a switching signal; g voltage; and, a first attenuated signal path connecting said subtracting 5 means responsive to said DC voltage for varying means with said utilization means; and,
a second signal path controlled b id switching Signal and response of said utilization means to said third pulse train.
shunting said first path.
|Cited Patent||Filing date||Publication date||Applicant||Title|
|US2821188 *||Apr 26, 1954||Jan 28, 1958||Pigeon Gerard||Apparatus for the measurement of arterial pressure|
|US3002185 *||Jun 13, 1957||Sep 26, 1961||Low frequency pulse detector|
|US3126885 *||May 18, 1961||Mar 31, 1964||Blood pressure measuring device|
|US3227155 *||Jul 10, 1961||Jan 4, 1966||Honeywell Inc||Sphygmomanometric measuring apparatus|
|US3412729 *||Aug 30, 1965||Nov 26, 1968||Nasa Usa||Method and apparatus for continuously monitoring blood oxygenation, blood pressure, pulse rate and the pressure pulse curve utilizing an ear oximeter as transducer|
|US3453546 *||Nov 4, 1966||Jul 1, 1969||Nasa||Telemeter adaptable for implanting in an animal|
|US3467837 *||Dec 27, 1966||Sep 16, 1969||Nasa||Blood pressure measuring system for separating and separately recording d.c. signal and an a.c. signal|
|US3510765 *||Jul 31, 1967||May 5, 1970||Humetrics Corp||Method and apparatus for gating variably recurrent waveforms|
|Citing Patent||Filing date||Publication date||Applicant||Title|
|US4161173 *||Oct 12, 1976||Jul 17, 1979||U.S. Philips Corporation||Blood pressure gauge|
|US4576178 *||Mar 28, 1983||Mar 18, 1986||David Johnson||Audio signal generator|
|US4653498 *||May 20, 1986||Mar 31, 1987||Nellcor Incorporated||Pulse oximeter monitor|
|US4802486 *||Jun 7, 1985||Feb 7, 1989||Nellcor Incorporated||Method and apparatus for detecting optical pulses|
|US4836212 *||Mar 17, 1987||Jun 6, 1989||Fa Nattermann Arneimittel Gmbh||Apparatus for the noninvasive determination and acoustical representation of the dynamic behavior of peripheral venous hemodynamic|
|US4911167 *||Mar 30, 1988||Mar 27, 1990||Nellcor Incorporated||Method and apparatus for detecting optical pulses|
|US4928692 *||Nov 23, 1988||May 29, 1990||Goodman David E||Method and apparatus for detecting optical pulses|
|US4934372 *||Apr 5, 1989||Jun 19, 1990||Nellcor Incorporated||Method and apparatus for detecting optical pulses|
|US5730140 *||Apr 28, 1995||Mar 24, 1998||Fitch; William Tecumseh S.||Sonification system using synthesized realistic body sounds modified by other medically-important variables for physiological monitoring|
|US6542764||Dec 1, 2000||Apr 1, 2003||Masimo Corporation||Pulse oximeter monitor for expressing the urgency of the patient's condition|
|US6947780 *||Mar 31, 2003||Sep 20, 2005||Dolphin Medical, Inc.||Auditory alarms for physiological data monitoring|
|US8475385||Oct 19, 2005||Jul 2, 2013||The University Of Queensland||Method and apparatus for physiological monitoring|
|US20040193026 *||Mar 31, 2003||Sep 30, 2004||Scharf Tom D.||Auditory alarms for physiological data monitoring|
|US20080114216 *||Oct 19, 2005||May 15, 2008||The University Of Queensland||Method and Apparatus For Physiological Monitoring|
|US20100049061 *||Aug 20, 2009||Feb 25, 2010||Mr Holdings (Hk) Ltd.||Systems and methods for providing auditory feedback during catheter placement|
|US20120116235 *||Nov 5, 2010||May 10, 2012||Nellcor Puritan Bennett Llc||Systems and methods for producing audible indicators that are representative of measured blood pressure|
|USRE35122 *||Feb 24, 1992||Dec 19, 1995||Nellcor Incorporated||Method and apparatus for detecting optical pulses|
|DE3609073A1 *||Mar 18, 1986||Sep 24, 1987||Hans J Prof Dr Rer Nat Schmitt||Einrichtung zur nichtinvasiven feststellung und akustischen darstellung des dynamischen verhaltens der peripheren venoesen haemodynamik|
|EP1807003A1 *||Oct 19, 2005||Jul 18, 2007||The University of Queensland||Method and apparatus for physiological monitoring|
|EP1807003A4 *||Oct 19, 2005||Mar 10, 2010||Univ Queensland||Method and apparatus for physiological monitoring|
|WO2006079148A1||Oct 19, 2005||Aug 3, 2006||The University Of Queensland||Method and apparatus for physiological monitoring|
|Jun 16, 1989||AS||Assignment|
Owner name: ENVIROMENTAL TECHNOLOGIES GROUP, INC., MARYLAND
Free format text: ASSIGNMENT OF ASSIGNORS INTEREST.;ASSIGNOR:ALLIED-SIGNAL INC.;REEL/FRAME:005115/0035
Effective date: 19890525
|Oct 31, 1988||AS06||Security interest|
Owner name: ENVIRONMENTAL ANALYTICAL SYSTEMS, INC.
Effective date: 19880922
Owner name: NATIONAL WESTMINSTER BANK USA, 175 WATER STREET, N
|Oct 31, 1988||AS||Assignment|
Owner name: ENVIRONMENTAL ANALYTICAL SYSTEMS, INC., A DE CORP.
Free format text: ASSIGNMENT OF ASSIGNORS INTEREST.;ASSIGNOR:ALLIED-SIGNAL INC.;REEL/FRAME:005006/0607
Effective date: 19880919
Owner name: NATIONAL WESTMINSTER BANK USA, A NATIONAL BANKING
Free format text: SECURITY INTEREST;ASSIGNOR:ENVIRONMENTAL ANALYTICAL SYSTEMS, INC.;REEL/FRAME:005006/0599
Effective date: 19880922