US3811428A - Biological signals monitor - Google Patents

Biological signals monitor Download PDF

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Publication number
US3811428A
US3811428A US00214287A US21428771A US3811428A US 3811428 A US3811428 A US 3811428A US 00214287 A US00214287 A US 00214287A US 21428771 A US21428771 A US 21428771A US 3811428 A US3811428 A US 3811428A
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signals
output
signal
circuitry
fetal heart
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P Phillipps
Horn J Van
P Epstein
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Wyeth LLC
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BRATTLE INSTR CORP
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Priority to US00214287A priority Critical patent/US3811428A/en
Priority to FR7242615A priority patent/FR2166971A5/fr
Priority to DE2265229A priority patent/DE2265229C2/de
Priority to DE2263180A priority patent/DE2263180C2/de
Priority to CA160,179A priority patent/CA993522A/en
Priority to GB5580674A priority patent/GB1410940A/en
Priority to JP734538A priority patent/JPS572331B2/ja
Priority to IT71147/72A priority patent/IT976241B/it
Priority to GB6012072A priority patent/GB1410939A/en
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Priority to CA228,451A priority patent/CA980874A/en
Assigned to AMERICAN HOME PRODUCTS CORPORATION, A CORP. OF DE reassignment AMERICAN HOME PRODUCTS CORPORATION, A CORP. OF DE ASSIGNMENT OF ASSIGNORS INTEREST. Assignors: MEDICAL ELECTRONICS CORPORATION A CORP. OF MA
Assigned to MEDICAL ELECTRONICS CORPORATION reassignment MEDICAL ELECTRONICS CORPORATION ASSIGNMENT OF ASSIGNORS INTEREST. Assignors: BANK OF NEW ENGLAND, N.A.
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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
    • A61B5/43—Detecting, measuring or recording for evaluating the reproductive systems
    • A61B5/4306—Detecting, measuring or recording for evaluating the reproductive systems for evaluating the female reproductive systems, e.g. gynaecological evaluations
    • A61B5/4343—Pregnancy and labour monitoring, e.g. for labour onset detection
    • A61B5/4362—Assessing foetal parameters
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
    • A61B5/316—Modalities, i.e. specific diagnostic methods
    • A61B5/318—Heart-related electrical modalities, e.g. electrocardiography [ECG]
    • A61B5/344—Foetal cardiography

Definitions

  • ABSTRACT Biological signals especlally, e.g., fetal QRS complexes
  • signal processingcircuitry [g2] ⁇ J.S.(gl.
  • l28/2.06 F, l28/2.06 B featuring, in various aspects, in the fetal bean rate 'f i 5/04 monitor, automatic thresholding of maternal and fetal 1 3g E 5' signals; a digital phase lock loop for generating fetal R heart rate signals related to the loop frequency, the loop including means for estimating the rate during [56] References (med occurrences of blank spaces caused by removal of sig- UN STATES PATENTS nals representing merged maternal and fetal heart 3.171392 3/I965 Pantle l28/2.05 R. ats; unt r ontr lled m ans for disabling readout; 3,581,735 6/1971 Gentner etal.
  • Abdominal detection is complicated by the masking effect of the maternal heartbeat, which is many times stronger than, and frequently merges (i.e., occurs simultaneously) with, the fetal, and by a variety of other sources of noise that make accurate detection of the very weak fetal signals extremely difficult; existing devices for abdominal detection are difficult to operate and are not reliably accurate.
  • the invention makes possible real time monitoring of fetal heart rate (as well as analogous monitoring of other relatively weak components of complex biological signals, such as T and P waves in ECG signals) with improved accuracy and reliability, yet with equipment that is relatively inexpensive and easy to operate.
  • the system is operable over a wide range of frequencies; excellent electrical isolation of the patient is provided; and excellent balance is achieved between avoiding readout of erroneous information and minimizing readout outages during which accurate information is lost (including, e.g., rapid recovery from outages caused by noise).
  • a monitor for a first electrical signal representing a first component of a recurring complex biological signal including a second component that is stronger than the first component the components respectively being fetal and maternal QRS complexes when the invention is embodied in a fetal heart rate monitor
  • the monitor comprising a signal processing path in which the first signals are detected and along part of which second signals representing occurrences of the second component are transmitted, automatic thresholding circuitry in the path for tracking signal magnitude and providing an output signifying the occurrence of the first component only upon receipt of a signal of magnitude bearing a predetermined relationship to previously tracked signal magnitude, and means for preventing effective response by the automatic thresholding circuitry to the second signals.
  • the invention in general, features logic circuitry for generating readout signals, with the decision as to each readout signal being based in part upon a statistical prediction derived from the pattern of signals received in past time periods, including (in the fetal heart rate monitor) a phase lock loop for generating fetal heart rate signals related to the loop frequency, the loop including means for estimating the rate during the occurrences of blank spaces in the modified signal train caused by removal of signals representing merged maternal and fetal heart beats; a counter responsive to deviation between the time of signal receipt by the logic circuitry and the prediction thereof, the counter increasing upon an instance of deviation greater than a predetermined value, readout being disabled when the counter is above a first count, derivation of the prediction being reinitiated when the counter reaches a second, higher count; electrodes for picking up the signals from a human body, and a low impedance pre-amplifier followed by a high impedance isolation amplifier magnetically (or otherwise indirectly) coupled at its output to the rest of the signal processing circuitry;
  • the invention features a digital phase lock loop adapted to produce repeating windows each sized and spaced to overlap a fetal signal on the basis of past spacing statistics despite variation within predetermined limits; means for updating under certain conditions the phase and frequency of the windows on the basis of the actual positions of the signals within the windows; a separate electrode for picking up maternal QRS complex signals, with signal processing circuitry which the maternal signals are transmitted in timed relationship to the transmission of maternal signals over the first path, the circuitry having a connection to the first path for the removal of maternal signals therefrom; and automatic thresholding means for both maternal and fetal signals, the fetal signal thresholding means including means for storing and decaying peak signal values, between an upper limit and a variable lower limit responsive to average signal value over the recent past.
  • FIG. 1 is a block diagram of the analog signal processing circuitry
  • FIGS. 2a, b together comprise a circuit diagram corresponding to FIG. 1;
  • FIGS. 3-8 comprise voltage-time graphs illustrating the signal patterns at various stages of the circuitry of FIGS. 1, 2a, and 2b;
  • FIG. 9 is a'flow chart of the digital'phase lock loop and readout algorithm
  • FIG. 10 is a block diagram of the digital phase lock loop and readout circuitry for implementing the algorithm illustrated in FIG. 9.
  • FIGS. 1 la, b, c, d together comprise a circuit diagram corresponding to FIG. 10.
  • FIGS. 12 and 13 comprise circuit diagrams of timing pulse generators
  • FIG. 14 is a combined block and circuit diagram illustrating variable lower limit circuitry for the fetal signal peak detector.
  • electrodes 10 and II are provided for placementon the patient to pick up the maternal and fetal QRS signals and feed them through ultra-low noise gain of 30 amplifiers l2 and 13 to patient isolation amplifiers l6 and 18, respectively.
  • Electrode 11 is placed on the abdomen, where the best fetal signal is available, and electrode 10 preferably in position (e.g., on the ribs) to maximize the maternal signal.
  • Reference electrode 20 is placed on the hip.
  • Amplifiers l2 and 13 have a low impedance, of the order of 10 ohms. As shown in the detailed circuitry of FlGS.2a-, these amplifiers are shunted by 100K resistors and 0.01 ufcapacitors. It has been-discovered that such low-impedance gives an improvementin signal-to-noise ratio which outweighs the corresponding reduction in overall signal level. Amplifiers l6 and 18 are transformer coupled to the rest of the system and to their power supply, and provide a very high impedance (of the order of 10 ohms) between the elec-. trodes and ground, thus protecting the patient from shock.
  • the amplified maternal signal passes through a low Q (less than 10, and preferably /2 to 1) band pass active filter 28 centered at l7Hz (the optimum in a preferred center frequency range of 15-25Hz), the center of peak energy in the maternal QRS waves.
  • the amplified fetal signal is passed through a cascaded pair of similarly low Q band pass active filters 30, 32 centered at 32Hz (the optimum in a preferred range of 25-40Hz for center frequency), the center of peak energy in the fetal QRS waves, thay energy extending roughly from SHz'to IOOHz.
  • filters 28 and 30 are incorporated into amplifiers l6 and 18, which respectively provide gains of and 40 with Q 1.) These low Q filters provide excellent transient response (equivalent to that of matched filters) to the thus far linearly processed signals they receive.
  • the filtering characteristics of the cascaded pair of filters 30, 32 multiply, narrowing the bandwidth and providing a very flat characteristic.
  • the output of filter 32 has at least percent of the signal energy in the SO-IOOHz range (exclusive of 60l-Iz noise), since important useful energy of the fetal waves lies there.
  • the signals from filters 28 and 30 fed voltage controlled oscillators 29 and 31 which convert the input voltage into a frequency which bears a linear relationship to the input voltage, in effect generating an FM signal of th input wave form.
  • the output voltages from the oscillators pass through isolation transformers which are coupled into demodulating and analog circuitry including analog phase lock loops 33 and 35 which convert the signal back into a wave form identical with that which was fed into the voltage controlled oscillators.
  • FIG. 3 illustrates the maternal and fetal waveforms 44 and 46 (waveform 46 of course still including maternal as well as fetal signals), respectively, at the rectifier inputs, and the corresponding outputs 48 and 50.
  • the rectifiers eliminate any need to consider varying signal polarity.
  • the output of rectifier 40 is fed both to peak detector 52 and comparator S4.
  • the peak detector stores and gradually decays toward zero the value of peak amplitude of a signal reaching it, until it receives another signal having a peak amplitude higher than the instantaneous valueto which the originally stored peak has decayed; the new peak value is thus stored, and so on.
  • the second input to comparator 54 is 90 percent (the preferred range is -90 percent) of the value stored in the peak detector.
  • the comparator fires whenever the output of 'rectifier 40 has apeak greater than percent the value stored in the peak'detector.
  • comparator 54 is used to fire a one shot (mono-stable multi-vibrator) 56 having a pulse width (e.g., milliseconds) as wide as the widest expected maternal QRS signal.
  • a pulse width e.g., milliseconds
  • FIG. 4 illustrates the output 57 of peak detector 52, the output 58 of comparator 54, and the output 59 of one shot 56.
  • FIG. 5 illustrates the Paynter output 62, which includes fetal pulses '64 and maternal pulses 66, the latter of course masking the former whenever the fetal and maternal heartbeatsmerged.
  • the output of Paynter filter 60 and one shot 56 are fed to analog gate 70, which closes during each firing of the one shot, thus gating out of the Paynter output all but the leading edges of the maternal pulses.
  • analog gate 70 which closes during each firing of the one shot, thus gating out of the Paynter output all but the leading edges of the maternal pulses.
  • the result is illustrated in FIG. 6, where the spikes 7-2 arethe leading edges of the blocked maternal pulses.
  • the result is passed through amplifier 74 to both a peak detector 76 and a comparator 78, which, just as did peak detector 52 a comparator S4 for maternal pulses, provide for detection of fetal pulses 64 with automatic thresholding.
  • the charging time constant of the peak detector about 3-4 milliseconds, is such that the maternal spikes 72 will not cause a reset.
  • Upper and lower limits are provided in the peak detector, the lower limit being set to avoid mistaking low level noise for a fetal pulse. Although the lower limit may rarely block out very weak fetal pulses, the device preferably is set up so that a direct display of the output of filter 32 can be switched on, this feature not being described in detail here.
  • While the lower limit may be fixed, greater accuracy (in the face of changing general noise or fetal signal levels) is obtained if the limit value is caused to change in accordance with average signal value reaching the peak detector over a recent prior period, e.g., over the past l0 seconds.
  • Circuitry 79 providing such a variable lower limit equal to, e.g., twice that average signal value, is shown in FIG. 14.
  • the outputs 80 and 82 of the peak detector and the comparator are illustrated in FIG. 7.
  • Pulses 84 correspond to fetal waves, the spikes 86 to the leading edges of the maternal waves.
  • the output 82 of comparator 78 is then passed through a shift register 90 (FIGS. 1, 11a) which provides a 32 millisecond delay.
  • the output of one shot 56 is used, each time-it fires, to zero register 90, thus blocking spikes 86.
  • the shift register output 85 is illustrated in FIG. 8. The register is gated to produce a four millisecond pulse 87 coinciding with the falling edge of each pulse 84 (it having been discovered that the time between the falling edges is a more accurate representation of the pulse spacing than the time between the leading edges).
  • the resulting signal train will, in general, in comparison to the real sequence of fetal heartbeats, have some gaps corresponding to missing fetal signals, and will of course include some pulses (noise) which do not correspond to real beats.
  • the digital circuitry to be dey scribed is designed to modify that signal train, so far as possible, by restoring the missing fetal pulses and removing the noise.
  • the digital circuitry employs a phase lock loop, and a sequence of windows (each window being essentially the positive half of a square wave) is generated with a period and phase that are updated on the basis of the recent history of the output of shift register 90, in such a way as to tend to center the windows on pulses 87. Any pulse 87 received outside a window is ignored for readout purposes.
  • the loop similarly ignores any two or more pulses that fall within a single window.
  • the value read out is the actual time between pulses 87 when they occur singularly in consecutive windows. When only one of two consecutive windows has a single pulse, the readout is the time from that pulse to the center of the window. When neither of two consecutive windows has a single pulse, the readout is the time between the center of the windows. If too many windows occur without single pulses, or if too many pulses occur outside windows, readout is temporarily halted. Window phase is updated only when single pulse windows occur, and window period (frequency) is updated only when consecutive single pulse windows occur.
  • the algorithm employed in the phase lock loop is illustrated in the flow chart of FIG. 9.
  • the window width (block 100) is roughly (a more precise definition appears below) half the running period of the loop, i.e., half the interval from the middle of one window to the middle of the next.
  • the pulse pattern in the current and next previous windows controls the values of New Period (which ultimately provides the rate readout).
  • Average Period (which in turn determines the actual window frequency, as well as window width), and Interval Between Windows (which in the absence of a window frequency adjustment, controls window phase).
  • the current window contains multiple pulses or no pulse, no adjustment is made in either New Period (block 102) or Average Period (block 104), and the Interval remains half the Average Period (block 106).
  • New Period is adjusted to equal the time from the middle of the first window to the pulse in the second (block 108), Average Period is left unchanged (i.e., no frequency adjustment, block 110), and the Interval is adjusted to equal three-fourths of Average Period minus the time between the end of the current window and the pulse therein (block 1 12). That is, window phase is adjusted so that the next pulse 87 will be centered in its window (if pulse frequency has not changed), yet without changing window frequency, since the information in the previous window was unreliable and an erroneous frequency adjustment based upon that unreliable information would produce an error that would grow from window to window.
  • New Period is adjusted to equal the time between the successive pulses 87 (block 114)
  • Average Period is adjusted to half the sum of the updated New Period and the old Average Period (block 116, thus. giving a frequency adjustment, though only by enough to account for half of any changes in the interval between pulses 87, to avoid over-correction)
  • the Interval is adjusted to equal three-fourths of the new Average Period minus the time between the end of the current window and the pulse therein (i.e., phase is adjusted too, block 118). (It should be noted that the value readout is always New Period, which is not directly affected by the frequency and phase adjustments just described.)
  • phase lock loop is able to operate over a wide range of frequencies (e.g., 60-240 pulses per minute), and makes it possible to postpone adjustment and readout decisions until the end of each window.
  • a counter keeps track of the relationship between pulses 87 that occur outside windows and those that occur singularly inside windows.
  • the count is incremented one for each outside pulse (block 117) and decremented one half for each single inside pulse (block 119). (The counter ignores multiple inside pulses).
  • When the count reaches 5 readout of New Period is halted (block 120).
  • When the count returns to less than 5 readout is resumed (block 122). Should-the count reach 8 or more, readout is halted (block 120), the counter is zeroed, and a Restart routine is initiated (block 124).
  • pulse 87 is measured (block 126). Should that next pulse arrive in less than 250 milliseconds it is ignored (block 128), because it would signify an unlikely fetal rate of more than 240 beats per minute. On the other hand, should that next pulse not arrive by 800 milliseconds, the counter is zeroed and, upon the arrival of the next pulse 87, the Restart routine is begun again (block 130); here again, restart at an unlikely (here too low) rate is prevented.
  • the algorithm thus set forth strikes an excellent balance' between avoiding readout of erroneous information and minimizing readout outages during which accurate information is lost.
  • FIG. illustrates in block diagram form the implementation of the phase lock loop and associated readout components.
  • the detailed circuitry appears in FIG. Ila-d, l2, 13.
  • the signals from shift register 90 pass into New Period measurement circuitry 150 (FIG. 11b), composed of two fourbit counters 152, 154 with parallel loads a .ll( flip flop 156 for clearing the counters.
  • the New Period data goes to four-bit full adders 158, 160 in Interval Between Window Generator 162 (FIGS. 11b, 110), which adders also receive the Average Period data generated in block 164 (FIG. 11b).
  • the signals from the full adders pass into the parallel loads of four-bit counters 166, 168, which generate the Interval Between Windows data.
  • the counter 166, 168 start out preset to the sum of one-fourth the Average Period plus the value thus for counted in the New Periodcounters 152, 154 (the-latter value being the time between the just previouspulse and the end of its window), and increment one during each clock cycle.
  • Two four-bit binary comparators 170,.172 signal when the count on counters 166, 168 equals the stored Average Period value, signifying the end of the Interval Between Windows. That signal then passes to Window Generator 174 (FIG.
  • Counters 176, 178 controls its width at half the Average Period value.
  • Counters 176, 178 are loaded with half the value of the last Average Period, and decrement one during each clock cycle; at zero the correct width will have been generated.
  • Restart counting circuitry 180 (FIG. 11a) includes four-bit up-down counter 182 with parallel load, and a JK flip flop 184 which generates a count of one for every other input for counting down, providing the weighting factor described above.
  • the New Period value is stored in four-bit registers 190, 192 in block 194 (FIG. 11d), and goes to digitalto-analog converter 196 (FIG. 1 1d) for conversion into an analog voltage. That voltage, a measurement of period, passes to analog storage circuitry 198, which includes a junction FET 200 and a high input impedance operational amplifier 202, as well as logical circuitry to inhibit readout when counter 182 is at 5 or more. From the storage circuitry the signal goes to analog divider 204 which converts it to rate information by generating an analog signal proportional to the reciprocal of the period signal. The output from the divider is amplified and given some D.C. offset (to restore the level to the correct base line reference) in amplifier 206, and then is fed to digital voltmeter readout 208 and strip chart recorder 210.
  • D.C. offset to restore the level to the correct base line reference
  • the gain between the input to storage circuitry 198 and the output of divider 204 is adjusted so that each 8 l0 millivolts of output corresponds to'a rate of one heart beat per minute.
  • a digital voltmeter which has a reading of for a l volt input gives the exact count of the heart reat in beats per minute.
  • the strip recorder is set up for direct reading of the rate.
  • off the shelf readout devices can be used.
  • FIG. 12 illustrates a 2KHz oscillator 220 which is a source of clock signals for the digital logic.
  • the signal is divided down in four-bit counter 222 to a 256Hz square wave T, along with faster versions T and T".
  • FIG. 13 illustrates a 11-12 oscillator 224 which generates a clockpulse to control the readout rate.
  • Fairchild MA739C dual low noise operational amplifier is used for amplifiers l2 and 13.
  • Teledyne Philbrick l3 I9 is used for. bandpass stages 28 and 30.
  • Oscillators 29 and-31 are Signetics NE566.
  • Analog phase lock loops 33 and 35 are Signetics NE565. V
  • the preamplifier power supply output transistors are Texas Instruments 2N3704, and all other tranistqrsa s, kannc dlm l l0. Matched diode pairs are Fairchild FAZOOO, and allothgr diodes are Motorola 1N914.
  • Analog'divider 204 is Teledeyne Philbrick 4452.
  • Digital to analog converter 186 is Analog Devices I MDA8H.
  • the logic elements comprise Texas Instruments:
  • a fetal heart rate monitor having a pickup for electrical signals received through the body of the mother, and means for providing an output relating to fetal heart rate
  • input circuitry means defining a signal processing path and responsive to said pickup for producing along said path a signal train including first signals representing maternal heart beats and second signals representing fetal heart beats, some of said first signals also representing fetal heart beats which occurred simultaneously with maternal heartbeats,
  • removal means for removing from said path at least the major portions of said first signals, whereby blank spaces are left by such removal of those of said first signals representing fetal heart beats which occurred simultaneously with maternal heart beats and circuitry means defining a phase lock loop having a frequency and including means responsive to they thus modified train of signals for generating fetal heart rate signals related to said frequency, said phase lock loop including means responsive to the updating means for detecting the position of successive fetal signals within the respective windows and for varying future windows spacing on the basis of the detected position of the signals in the windows.
  • the fetal heart rate monitor of claim 1 wherein means are provided for producing, at said phase lock loop, a train of digital signals, each representing a fetal QRS complex, including means for disabling said updating means upon the occurrence of no pulse or more than one pulse in said window, thereby continuing the use of the past spacing setting.
  • the fetal heart rate monitor of claim 2 wherein said updating means includes means to relocate the next window upon the occurrence of a single pulse in the present window by pulse shift of the past spacing in the event no single pulse appeared in the last preceding window.
  • the fetal heart rate monitor of claim 2 wherein said updating means includes means to relocate the next window upon the occurrence of a single pulse in the present window by alteration of the loop frequency in the event a single pulse appeared in the last preceding window.
  • said updating means includes means to relocate the next window upon the occurrence of single pulses in two successive windows by alteration of the loop frequency so that the corresponding altered window period is between the window period prior to said alteration and the spacing between said two single pulses.
  • the fetal heart rate monitor of claim 1 including a counter, means for incrementing said counter upon the occurrence of signals outside said window and means for decrementing said counter upon the occurl0- rence of signals inside said window, including means for weighing more heavily in said count the signals outside said window and means for resetting said phase lock loop upon the occurrence of a count greater than a predetermined value.
  • the fetal heart rate monitor of claim 1 further comprising circuitry means defining a second signal processing path and for transmitting along said second path third signals representing maternal heart beats, said removal means having a connection to said circuitry means defining said second path and being responsive to occurrence of said third signals in said second path.
  • the fetal heart rate monitor of claim 7 including in said circuitry means defining said second path, preceding said connection, an automatic threshold means for generating from a signal derived from a maternal QRS complex a signal representative thereof.
  • the fetal heart rate monitor of claim 8 including as said threshold means a peak detector including means for fixing predetermined limit and for storing a value less than said limit and allowing said stored value to decay over time, and a comparator effectively connected to said peak detector and to said circuit means defining said second path for generating an output signal when a signal in said second path exceeds-the decayed value of the preceding peak stored in said detector.
  • the fetal heart monitor of claim 9 including a monostable multivibrator effectively connected to said comparator foor energization upon the occurrence of said output signal, said monostable multi-vibrator having a time constant substantially corresponding to the maximum width of the maternal QRS complex.
  • the fetal heart rate monitor of claim 7 wherein there is included in said circuitry means defining said first path an automatic threshold means for generating from a fetal QRS complex wave av signal representative thereof.
  • the fetal heart rate monitor of claim 11 including as said threshold means a peak detector including means for fixing a predetermined limit and for storing a value greater than said limit and allowing said stored value to decay over time, and a comparator effectively connected to said peak detector and to said circuitry defining said first path for generating an output signal when a signal exceeds the decayed value of the preceding peak stored in said detector, g
  • the fetal heart rate monitor of claim 12 including means in said first'path effectively connected to said comparator and responsive to signals in said second path for removing output signals from said comparator which coincide in time with a maternal QRS complex, thereby to remove portions of maternal signals present in the output of said comparator.
  • phase lock loop is digital
  • a monitor having a pickup for a first electrical signal representing a first component of a recurring complex biological signal including a second component that is stronger than the first component, and output circuitry means including means for providing an output related to occurrences of said first component,
  • said second path includes automatic thresholding means for tracking-signal magnitude and providing an outputto said automatic thresholding means in said first path signifying the occurrence of said second component only upon receipt of a signal of magnitude bearing a predetermined relationship to previously tracked signal magnitude.
  • said automatic thresholding means includes means for storing and decaying over time the peak value of a received signal, and a'comparator effectively connected to said means for storing, said comparator including means for providing said output when a received signal is greater than a predetermined percentage of the decayed value presently stored.
  • said means for storing includes means for preventing the value stored therein from decaying below a limit, including means for establishing said limit.
  • the monitorof claim 21 wherein said means for establishing said limit includes means for monitoring the past history of signals reaching said automatic thresholding means and for varying said limit in accordance with said history.
  • the monitor of claim 15 further comprising removal means for removing at least the major portions of said second signals from said path, while leaving leading edges of said second signals, a
  • delay means for receiving signals from said removal circuitry, includingsignals representing said leading edges, and means for excluding from the effective output of said delay-means said signals representing said leading edges.
  • the monitor of claim 24 further comprising means for detecting the falling edges of said first signals and for causing said output of said delay means to be I quency noise, and a notch filter for removing said line frequency noise,
  • the monitor of claim 26 comprising automatic thresholding means effectively connected between said filters and said readout for tracking signal magnitude and providing an output signalling the occurrence of a fetal QRS complex only upon receipt of a signal of magnitude bearing a predetermined relationship to previously tracked signal magnitude, said thresholding means including means for determining said relationip- 28.
  • the monitor of claim 27 further comprising additional signal processing means for electrical signals-corresponding to maternal QRS complex signals, and means connected in the signal path leading to said antomatic thresholding-means for preventing at least the major portion of electrical signals corresponding to ma- I ternal QRS complex signals from reaching said automatic thresholding means, said means for preventing being responsive to detection of said electrical signals processed by said additional signal processing means.
  • fetal heart rate monitor having a pickup for electrical signals received through the body of the mother, and output circuitry means including means for providing an output relating to fetal heart rate
  • input circuitry means defining a signal processing path and responsive to said pickup for producing along said path a signal train including first signals representing maternal heart beats and second signals representing fetal heart beats, some of said first signals also representing fetal heart beats which occurred simultaneously with maternal heart beats,
  • removal means for removing from said path at least the major portions of said first signals, whereby blank spaces are left by such removal of those of said first signals representing fetal heart beats put in which at least 25 percent of the signal energy" is in the 50-100 Hz range, exclusive of line fre which occurred simultaneously with maternal heart beats,
  • circuitry means defining a phase lock loop having a frequency and including means responsive to the thus modified train of signals for generating and providing to said output circuitry means fetal heart rate signals related to said frequency, said phase lock loop including means responsive to the spacing characteristics between said signals in said modified train for estimating fetal heart rateduring the occurrence of said blank spaces in said modified train, and
  • circuitry means defining a second signal processing path and for transmitting along said second path third signals representing maternal heart beats, said removal means having a connection to said circuitry means defining said second path and being responsive to occurrence of said third signals in said second path,
  • circuitry means defining said second path including, preceding said connection, input means for a maternal QRS complex signal, a notch filter for removing line frequency noise, and a band pass filter having Q less than and a center frequency between 15 Hz and 25 Hz.
  • a fetal heart rate monitor having a pickup for electrical signals received through the body of the mother, and output circuitry means including means for providing an output relating to fetal heart rate
  • input circuitry-means defining a signal processing path and responsive 'to said pickup for producing along said patha signal train including first signals representing maternal heart beats and second signals representing fetal heart beats, some of said first signals also representing fetal heart beats which occurred simultaneously with maternal heart beats,
  • removal means for removing from said path at least the major portions of said first signals, whereby blank spaces are left by such removal of those of said first signals representing fetal heart beats which occurred simultaneously with maternal heart beats,
  • circuitry means defining a phase lock loop having a frequency and including means responsive to the thus modified train of signals for generating and providing to said output circuitry means fetal heart rate signals related to said frequency, said phase lock loop including means responsive to the spacing characteristics between said signals in said modified train for estimating fetal heart rate during the occurrence of said blank spaces in said modified train, and
  • circuitry means defining a second signal processing path and for transmitting along said second path third signals representing maternal heart beats, said removal means having a connection to said circuitry means defining said second path and being responsive to occurrence of said third signals in said second path,
  • circuitry means defining said first path including,
  • input means for a fetal QRS complex signal input means for a fetal QRS complex signal, a notch filter for removing line frequency noise, and a band pass filter having Q less than 10 and a center frequency between 25 Hz and 40 Hz.
  • input circuitry means responsive to said pickup for producing a signal train including signals representing fetal heart beats
  • prediction circuitry means responsive to said input circuitry for predicting occurrences of said signals representing fetal heart beats, based upon past occurrences of such signals in said train
  • output circuitry means responsive of said input and prediction circuitry means for providing an output relating to fetal heart rate, said output circuitry means including means for basing said output on said signals representing fetal heart beats when such signals occur within a predetermined range of predicted occurrences thereof and for otherwise basing said output on said predicted occurrences,
  • said prediction circuitry means including means for basing said predictions at least in part upon selected previous predictions upon which said output was based.
  • said prediction circuitry means includes means for referring the phase of asaid predicted occurrence to the next previous said predicted occurrence if said output was based thereupon, and otherwise to the next previous said signal representing a fetal heart beat upon which said out-.
  • said output circuitry includes means for basing said output upon a said predicted occurrence whenever more than one pulse in said signal train occurs within said predetermined range of said predicted occurrence.
  • input circuitry means responsive to said pickup for producing a signaltrain including signals representing occurrences of said first component
  • prediction circuitry means responsive to said input circuitry for predicting-occurrences of said signals representing occurrences of said first component, based upon past occurrences of such signals in said train, and
  • output circuitry means responsive to said input and prediction circuitry means for providing an output related to occurrences of said first component, said output circuitry means including means for basing said output on said signals representing occurrences of said first component when said signals occur within a predetermined range of predicted occurrences thereof and for otherwise basing said output on said predicted occurrences,
  • said prediction circuitry means including means for basing said predictions at least in part upon selected previous predictions upon which said output was based.
  • input circuitry means responsiveto said pickup for producing a signal train including signals representing fetal heart beats with attendant noise signals and with some heart beats unrepresented in the signal train,
  • prediction circuitry means responsive tovsaid input circuitry for predicting occurrences of said signals representing fetal heart beats, based upon past occurrences of such signals in said train, and
  • output circuitry means responsive to said input and prediction circuitry means for providing an output relating to fetal heart rate
  • said prediction circuitry means including means for repeatedly producing a window overlapping the predictable point in time of the next heart beat based upon past occurrences, said output circuitry means responsive to a signal occurring in a window to treat said signal as a detected heart beat and agjust the output according to the position of the signal in the signal train, said output circuitry means further including means for disregarding as noise any signals occurring outside of said window, -means causing said prediction circuitry to continue to operate when a heart beat is not detected in a window to produce a window for the next succeeding heart beat, said window having a duration sized to overlap a fetal heart beat signal in the presence of a predetermined amount of predicted change in fetal heart rate which may occur over a plurality of each said window is approximately one half of a predicted fetal heart beat interval.
  • a monitor having input circuitry means including a pickup for a train of signals, including true and false signals, representative of a selected component of quasi-periodic, complex physiological electrical signals, signal-to-signal spacing being variable, and output circuitry'means including means for providing an output relating to real and expected occurrences of said component:
  • window means responsive to said input circuitry means for producing windows spaced in accordance with the previous history of said train of signals for enabling said receiving means to effectively receive said signals only during an interval pre- 7 scribed by each said window;
  • output means coupled to said receiving means and 'window means for producing and providing to said output circuitry output signals indicative of real and expected occurrences of true quasi-periodic signals occurring in said train.
  • control means responsive to said quality means for controlling the operation of said window means in accordance with said qualitysignal.
  • control means operates to reset said window means to its initial condition in the event the number of such counts exceeds a predetermined magnitude.
  • a monitor having input circuitry means including a pickup for recurrent complex electrical physiological signals having a first component weaker than a second-component and in the presence of extraneous recurrent noise signals, and output circuitry means including means for providing an output relating to occurrences of said first component, processing circuitry means coupled to said input and output circuitry means and comprising:'
  • band pass filter means having a Q under 10 for passing signals having a frequency content spanning the maximum energy in said first component
  • notch filter means for excluding extraneous noise 0 a selected frequency
  • v automatic threshold means responsive to said filtered first component for excluding signals below a threshold determined as a function of previously received filtered first component signals to produce and provide to'said output circuitry means a train of signals representative of said first component.
  • prediction circuitry means responsive to said input circuitry means for making predictions of said occurrences based upon past historyof saidsignals in said train, output circuitry means responsive to said input and prediction circuitry means for providing an output relating to occurrences of said component, including elements for basing said output upon said predictions under predetermined circumstances,
  • restart circuitry means for reinitiating derivation of said predictions when said quality means indicates a predetermined degree of unreliability.
  • output disabling means for preventing output when said quality means indicates a predetermined degree of unreliability including means for requiring a higher reliability to permit output during said reinitiation than when said reinitiation is completed.
  • restart circuitry means includes means for requiring a higher degree of reliability for acceptance of an attempted reinitiation than the reliability required when said reinitiation is completed.

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  • Gynecology & Obstetrics (AREA)
  • Reproductive Health (AREA)
  • Measurement And Recording Of Electrical Phenomena And Electrical Characteristics Of The Living Body (AREA)
  • Measuring Pulse, Heart Rate, Blood Pressure Or Blood Flow (AREA)
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US00214287A 1971-12-30 1971-12-30 Biological signals monitor Expired - Lifetime US3811428A (en)

Priority Applications (10)

Application Number Priority Date Filing Date Title
US00214287A US3811428A (en) 1971-12-30 1971-12-30 Biological signals monitor
FR7242615A FR2166971A5 (de) 1971-12-30 1972-11-30
DE2263180A DE2263180C2 (de) 1971-12-30 1972-12-22 Signalverarbeitungsschaltung zum Bestimmen der Folgefrequenz einer Komponente physiologischer Signale
DE2265229A DE2265229C2 (de) 1971-12-30 1972-12-22 Schaltungsanordnung zur Überwachung einer schwachen EKG-Signalkomponente, wie fetaler Herzsignale
GB5580674A GB1410940A (en) 1971-12-30 1972-12-29 Signal processors
JP734538A JPS572331B2 (de) 1971-12-30 1972-12-29
CA160,179A CA993522A (en) 1971-12-30 1972-12-29 Monitoring biological signals
IT71147/72A IT976241B (it) 1971-12-30 1972-12-29 Elaboratore di segnali biologici particolarmente del battito cardia co del feto nel grembo materno
GB6012072A GB1410939A (en) 1971-12-30 1972-12-29 Signal processors for physiological signals
CA228,451A CA980874A (en) 1971-12-30 1975-06-04 Monitoring biological signals

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US00214287A US3811428A (en) 1971-12-30 1971-12-30 Biological signals monitor

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JP (1) JPS572331B2 (de)
CA (1) CA993522A (de)
DE (2) DE2265229C2 (de)
FR (1) FR2166971A5 (de)
GB (2) GB1410940A (de)
IT (1) IT976241B (de)

Cited By (22)

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US3916878A (en) * 1973-06-05 1975-11-04 Hewlett Packard Gmbh Circuit arrangement for producing a pulse sequence corresponding to a foetal cardiac rhythm
US3921621A (en) * 1973-08-23 1975-11-25 Lee R Baessler Method and system utilizing a disposable transmitter for monitoring a patient{3 s condition
US3982528A (en) * 1975-02-24 1976-09-28 Brattle Instrument Corporation Apparatus for refining signals derived from fetal heartbeats
US3994286A (en) * 1974-06-21 1976-11-30 Siemens Aktiengesellschaft Circuit arrangement for the processing of physiological measuring signals
US4023565A (en) * 1974-06-21 1977-05-17 Siemens Aktiengesellschaft Circuit arrangement for the processing of physiological measuring signals
US4155352A (en) * 1977-06-09 1979-05-22 Temple University Nystagmus processor for EEG machines
US4161945A (en) * 1977-10-25 1979-07-24 Cambridge Instrument Company, Inc. Selective interference filter
US4182315A (en) * 1977-07-21 1980-01-08 Diamond George A Apparatus and method for detection of body tissue movement
US4202340A (en) * 1975-09-30 1980-05-13 Mieczyslaw Mirowski Method and apparatus for monitoring heart activity, detecting abnormalities, and cardioverting a malfunctioning heart
US4211237A (en) * 1977-04-14 1980-07-08 Biotronik Mess- Und Therapiegerate Gmbh & Co. Method and apparatus for identifying recurring signal patterns
US4256118A (en) * 1977-07-13 1981-03-17 Biotronik Mess-Und Therapiegerate Gmbh & Co. Apparatus for the detection and recording of uterine activity
US4299234A (en) * 1979-03-30 1981-11-10 Brattle Instrument Corporation Fetal heart rate monitor apparatus and method for combining electrically and mechanically derived cardiographic signals
US4306567A (en) * 1977-12-22 1981-12-22 Krasner Jerome L Detection and monitoring device
USRE31097E (en) * 1977-07-21 1982-12-07 Cardiokinetics, Inc. Apparatus and method for detecton of body tissue movement
US4510944A (en) * 1982-12-30 1985-04-16 Porges Stephen W Method and apparatus for evaluating rhythmic oscillations in aperiodic physiological response systems
US4516579A (en) * 1982-09-01 1985-05-14 Werner Irnich Interference recognition circuit in a heart pacemaker
US4898179A (en) * 1985-06-17 1990-02-06 Vladimir Sirota Device for detecting, monitoring, displaying and recording of material and fetal vital signs and permitting communication between a woman and her fetus
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
CN104224157A (zh) * 2014-09-28 2014-12-24 成都金海鼎盛科技有限公司 适用于可穿戴设备的高可靠低计算量的心律识别电路与方法
US20160045131A1 (en) * 2014-08-18 2016-02-18 Cameron Health, Inc. Cardiac rate tracking in an implantable medical device
US9289167B2 (en) 1997-04-14 2016-03-22 Masimo Corporation Signal processing apparatus and method
CN105530857A (zh) * 2013-09-09 2016-04-27 皇家飞利浦有限公司 根据母体腹部ecg记录的胎儿心率提取

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JPS538790U (de) * 1976-07-08 1978-01-25
US4313445A (en) * 1977-10-25 1982-02-02 Ivac Corporation Electronic sphygmomanometer
US4321932A (en) * 1979-06-29 1982-03-30 International Business Machines Corporation Electrode impedance monitoring method apparatus for electrocardiography
DE3120309C2 (de) * 1981-05-21 1985-10-03 Belorusskij naučno-issledovatel'skij institut kardiologii, Minsk Elektronisches Ergometer
WO1984001705A1 (en) * 1982-10-29 1984-05-10 London Hospital Med Coll Cardio-respiratory monitor apparatus & method
JPH05226168A (ja) * 1991-03-20 1993-09-03 Kawatetsu Densetsu Kk 定電圧変圧器
GB2342449B (en) 1998-12-22 2000-09-20 Neoventa Medical Ab Device for reducing signal noise in a fetal ECG signal
GB2580247B (en) * 2017-12-20 2022-06-01 Halliburton Energy Services Inc Capture and recycling methods for non-aqueous cleaning materials

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GB975373A (en) * 1961-07-10 1964-11-18 Hitachi Ltd Measuring instrument for bio-electrical signals and the like
US3367323A (en) * 1964-11-17 1968-02-06 Nat Res Councll Fetal electrocardiograph and method
FR1445220A (fr) * 1965-08-24 1966-07-08 Teldix Luftfahrt Ausruestung Dispositif pour la surveillance du fonctionnement cardiaque d'un foetus
US3554187A (en) * 1965-10-21 1971-01-12 Humetrics Corp Method and apparatus for automatically screening of electrocardiac signals
US3524442A (en) * 1967-12-01 1970-08-18 Hewlett Packard Co Arrhythmia detector and method
US3547104A (en) * 1968-01-17 1970-12-15 Marvin A Buffington Electrocardiographic monitoring apparatus and system
US3581735A (en) * 1968-06-12 1971-06-01 Hewlett Packard Gmbh Heartbeat frequency determining apparatus and method
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US3613670A (en) * 1969-02-12 1971-10-19 Princo Instr Inc Heartbeat monitor with audio and visual outputs

Cited By (26)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3916878A (en) * 1973-06-05 1975-11-04 Hewlett Packard Gmbh Circuit arrangement for producing a pulse sequence corresponding to a foetal cardiac rhythm
US3921621A (en) * 1973-08-23 1975-11-25 Lee R Baessler Method and system utilizing a disposable transmitter for monitoring a patient{3 s condition
US3994286A (en) * 1974-06-21 1976-11-30 Siemens Aktiengesellschaft Circuit arrangement for the processing of physiological measuring signals
US4023565A (en) * 1974-06-21 1977-05-17 Siemens Aktiengesellschaft Circuit arrangement for the processing of physiological measuring signals
US3982528A (en) * 1975-02-24 1976-09-28 Brattle Instrument Corporation Apparatus for refining signals derived from fetal heartbeats
US4202340A (en) * 1975-09-30 1980-05-13 Mieczyslaw Mirowski Method and apparatus for monitoring heart activity, detecting abnormalities, and cardioverting a malfunctioning heart
US4211237A (en) * 1977-04-14 1980-07-08 Biotronik Mess- Und Therapiegerate Gmbh & Co. Method and apparatus for identifying recurring signal patterns
US4155352A (en) * 1977-06-09 1979-05-22 Temple University Nystagmus processor for EEG machines
US4256118A (en) * 1977-07-13 1981-03-17 Biotronik Mess-Und Therapiegerate Gmbh & Co. Apparatus for the detection and recording of uterine activity
US4182315A (en) * 1977-07-21 1980-01-08 Diamond George A Apparatus and method for detection of body tissue movement
USRE31097E (en) * 1977-07-21 1982-12-07 Cardiokinetics, Inc. Apparatus and method for detecton of body tissue movement
US4161945A (en) * 1977-10-25 1979-07-24 Cambridge Instrument Company, Inc. Selective interference filter
US4306567A (en) * 1977-12-22 1981-12-22 Krasner Jerome L Detection and monitoring device
US4299234A (en) * 1979-03-30 1981-11-10 Brattle Instrument Corporation Fetal heart rate monitor apparatus and method for combining electrically and mechanically derived cardiographic signals
US4516579A (en) * 1982-09-01 1985-05-14 Werner Irnich Interference recognition circuit in a heart pacemaker
US4510944A (en) * 1982-12-30 1985-04-16 Porges Stephen W Method and apparatus for evaluating rhythmic oscillations in aperiodic physiological response systems
US4898179A (en) * 1985-06-17 1990-02-06 Vladimir Sirota Device for detecting, monitoring, displaying and recording of material and fetal vital signs and permitting communication between a woman and her fetus
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
US9289167B2 (en) 1997-04-14 2016-03-22 Masimo Corporation Signal processing apparatus and method
CN105530857A (zh) * 2013-09-09 2016-04-27 皇家飞利浦有限公司 根据母体腹部ecg记录的胎儿心率提取
CN105530857B (zh) * 2013-09-09 2019-05-10 皇家飞利浦有限公司 根据母体腹部ecg记录的胎儿心率提取
US20160045131A1 (en) * 2014-08-18 2016-02-18 Cameron Health, Inc. Cardiac rate tracking in an implantable medical device
US9451892B2 (en) * 2014-08-18 2016-09-27 Cameron Health, Inc. Cardiac rate tracking in an implantable medical device
US9895071B2 (en) 2014-08-18 2018-02-20 Cameron Health, Inc. Cardiac rate tracking in an implantable medical device
CN104224157B (zh) * 2014-09-28 2017-03-01 成都维客亲源健康科技有限公司 适用于可穿戴设备的高可靠低计算量的心律识别电路与方法
CN104224157A (zh) * 2014-09-28 2014-12-24 成都金海鼎盛科技有限公司 适用于可穿戴设备的高可靠低计算量的心律识别电路与方法

Also Published As

Publication number Publication date
IT976241B (it) 1974-08-20
GB1410939A (en) 1975-10-22
DE2265229C2 (de) 1984-03-29
JPS572331B2 (de) 1982-01-16
GB1410940A (en) 1975-10-22
DE2263180C2 (de) 1984-12-20
DE2265229A1 (de) 1976-12-09
JPS4878793A (de) 1973-10-22
DE2263180A1 (de) 1973-07-05
CA993522A (en) 1976-07-20
FR2166971A5 (de) 1973-08-17

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