AU735569B2 - System and method for monitoring a heartbeat - Google Patents

System and method for monitoring a heartbeat Download PDF

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Publication number
AU735569B2
AU735569B2 AU48744/97A AU4874497A AU735569B2 AU 735569 B2 AU735569 B2 AU 735569B2 AU 48744/97 A AU48744/97 A AU 48744/97A AU 4874497 A AU4874497 A AU 4874497A AU 735569 B2 AU735569 B2 AU 735569B2
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AU
Australia
Prior art keywords
heartbeat
signal
monitor system
system according
filter
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Ceased
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AU48744/97A
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AU4874497A (en
Inventor
Paul William Gibbon
Keith Alexander Ross
Brian Eric Russell
Derek Travers Smith
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MOVEMENT CONTROL SYSTEMS Ltd
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MOVEMENT CONTROL SYSTEMS Ltd
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Priority to GB9623077A priority Critical patent/GB9623077D0/en
Priority to GB9623077 priority
Application filed by MOVEMENT CONTROL SYSTEMS Ltd filed Critical MOVEMENT CONTROL SYSTEMS Ltd
Priority to PCT/GB1997/003024 priority patent/WO1998019596A1/en
Publication of AU4874497A publication Critical patent/AU4874497A/en
Application granted granted Critical
Publication of AU735569B2 publication Critical patent/AU735569B2/en
Anticipated expiration legal-status Critical
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Classifications

    • GPHYSICS
    • G01MEASURING; TESTING
    • G01PMEASURING LINEAR OR ANGULAR SPEED, ACCELERATION, DECELERATION, OR SHOCK; INDICATING PRESENCE, ABSENCE, OR DIRECTION, OF MOVEMENT
    • G01P13/00Indicating or recording presence, absence, or direction, of movement
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00Detecting, measuring or recording for diagnostic purposes; Identification of persons
    • A61B5/103Detecting, measuring or recording devices for testing the shape, pattern, colour, size or movement of the body or parts thereof, for diagnostic purposes
    • A61B5/11Measuring movement of the entire body or parts thereof, e.g. head or hand tremor, mobility of a limb
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00Detecting, measuring or recording for diagnostic purposes; Identification of persons
    • A61B5/103Detecting, measuring or recording devices for testing the shape, pattern, colour, size or movement of the body or parts thereof, for diagnostic purposes
    • A61B5/11Measuring movement of the entire body or parts thereof, e.g. head or hand tremor, mobility of a limb
    • A61B5/1102Ballistocardiography
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00Detecting, measuring or recording for diagnostic purposes; Identification of persons
    • A61B5/103Detecting, measuring or recording devices for testing the shape, pattern, colour, size or movement of the body or parts thereof, for diagnostic purposes
    • A61B5/11Measuring movement of the entire body or parts thereof, e.g. head or hand tremor, mobility of a limb
    • A61B5/113Measuring movement of the entire body or parts thereof, e.g. head or hand tremor, mobility of a limb occurring during breathing
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B2562/00Details of sensors; Constructional details of sensor housings or probes; Accessories for sensors
    • A61B2562/16Details of sensor housings or probes; Details of structural supports for sensors
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00Detecting, measuring or recording for diagnostic purposes; Identification of persons
    • A61B5/68Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
    • A61B5/6887Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient mounted on external non-worn devices, e.g. non-medical devices
    • A61B5/6891Furniture
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00Detecting, measuring or recording for diagnostic purposes; Identification of persons
    • A61B5/68Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
    • A61B5/6887Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient mounted on external non-worn devices, e.g. non-medical devices
    • A61B5/6892Mats
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00Detecting, measuring or recording for diagnostic purposes; Identification of persons
    • A61B5/72Signal processing specially adapted for physiological signals or for diagnostic purposes
    • A61B5/7203Signal processing specially adapted for physiological signals or for diagnostic purposes for noise prevention, reduction or removal
    • A61B5/7207Signal processing specially adapted for physiological signals or for diagnostic purposes for noise prevention, reduction or removal of noise induced by motion artifacts

Description

P:\opeak\48744.-97 rcspo~.doc-I14/O2O I SYSTEM AND METHOD FOR MONITORING A HEARTBEAT The present invention relates to a system and method for monitoring the heartbeat of a living being without having to be fitted to the living being, in particular when the living being is a baby.

Systems have been developed for home and hospital use to monitor the presence of a baby in a cot or a pram, for example by monitoring a heartbeat or breathing of the baby, which set off an alarm when the baby is removed by an unauthorised person.

Such systems must be capable of being applied to a number of living beings simultaneously, for instance, in a hospital ward where a number of cots or beds would be present.

15 Monitoring systems have been developed which use various types of sensors which are connected to the body of the living being. The sensors are then typically connected to a suitable form of processing facility. However, in such systems it is inconvenient to have to attach and detach the living being from the sensors when they are moved. Also, the attachment of sensors to a baby invariably requires the use of wires which may become 20 entangled in with the baby's limbs or around a baby's neck.

.GB 2,150,332 discloses a heartbeat monitor which is attached to the chest of a baby, for example by being fitted in a pocket of a close fitting vest which pocket lies over the chest aof the baby. The monitor comprises a microphone for picking up cardiac sounds and 25 avoids the use of wires to connect the monitor to a processing facility by using a radio link.

However, this system would not immediately be able to detect the removal of a baby from a cot or pram by an unauthorised person and has the inconvenience of having to repeatedly fit the monitor to a baby.

SEquipment for monitoring a heartbeat has to be able to detect a signal having a very short pulse duration and if the sensor is not directly fitted to the living being will have to pick c out the heartbeat signal of very small amplitude from a lot of background movement or noise including movement or noises made by the living being, such as breathing, vocal noises and limb movements as well as movement or noises emanating from the surroundings of the living being.

P.'perkkaX48744-97 rmpo ns.dm- 14/011) 2 US 5, 479,932 and US 5,470,932 disclose heart rate monitors which comprise processing circuitry for filtering signal shaving typical heart rate frequencies and sounding alarms when a signal within the heart rate frequency range is not detected. However, there is a continual requirement to improve the reliability and sensitivity of such monitors in order to improve the detection of problems and to avoid false alarms.

GB 2,165,979 discloses a monitor apparatus which describes a system which monitors breathing by sensing pressure changes in an air envelope on which a baby rests. The air envelope is designed to couple the signal of interest which may also comprise a heartbeat to a transducer signal which communicates with the air pocket. However, GB 2,165,979 does not disclose in detail how the air envelope is designed to discriminate between the signal of interest and other movement or noises occurring in the local environment. The transducer signal is amplified, rectified and integrated and then the resultant signal is compared with a control signal. If the resultant signal drops below the control signal for a predetermined period of time then an alarm is activated.

e• Accordingly, the present invention provides a monitor system for monitoring the heartbeat of a living being, comprising a transducer responsive to the heartbeat to generate a 20 heartbeat signal in the form of spaced heartbeat pulses, a filter circuit for filtering the heartbeat signal, and processing circuitry for processing the output of the filter circuit, wherein the filter circuit comprises an oscillating element responsive to each heartbeat pulse having a duration in a predetermined range, said duration corresponding to a half cycle of a sinusoidal signal within a corresponding predetermined frequency range, to generate a sinusoidal signal of decaying amplitude having a half cycle of a duration which approximates to the duration of the heartbeat pulse.

Monitor systems according to embodiments of the present invention may be capable of reliably distinguishing the heartbeat signal from a composite signal including signals generated by other noises or movements, in that, as long as the heartbeat signal is present, R1 the sinusoidal signal generated by the oscillator element will pass through the filter to the processing 3 the oscillator element will pass through the filter to the processing circuitry. If the heartbeat stops the sinusoidal signal generated by the oscillator element will decay to zero and so the amplitude of the signal passing through the filter to the processing circuitry will drop. The processing circuitry can be arranged to set off an alarm when the signal passing from the filter drops below a predetermined level. Preferably the oscillating element is an electrical resonator circuit with a gain of less than unity.

In a preferred embodiment the system comprises a transducer responsive to the heartbeat to generate an electrical heartbeat signal. In this case the oscillating element may be an electrical resonator circuit, for example an active filter, with a gain approaching unity such that the oscillations generated by the oscillator element decay slowly.

Conveniently, the oscillating element and the filter comprise an active filter. When exited an active filter will oscillate at the frequencies within the bandwidth of the filter and so can perform both the functions of the oscillating element and the filter.

Before reaching the oscillator element-and/or filter it is preferred to pass the electrical heartbeat signal through a high pass filter which passes frequencies greater than approximately 5 to 7.5 HIz and so blocks lower frequencies in order to prevent swamping of the low amplitude heartbeat signal by high amplitude breathing and/or limb movement signals.

In a preferred embodiment, which can utilise low cost passive low pass filters the active filter comprises; a first filter which passes frequencies below the bottom end of the selected range of frequencies, a second filter which passes frequencies below the top end of the selected range of frequencies, and a subtraction element for subtracting the first signal from the second signal.

Alternatively, the oscillating element comprises a mechanical oscillator. A flexible board can be designed so that it oscillates in response to a heartbeat signal so that a piezo device Sfixed to the board generates a sinusoidal signal of decaying amplitude having a half cycle Swhich approximates to the heartbeat signal. In this case the baby's heartbeat can provide AMENDED SHEET P:\OPER\KAT48744-97 179 28/6/99 -4a regular stimulus to maintain the oscillation of the board. The oscillations form a continuous sinusoidal signal so long as the heartbeat is present and so are much easier to detect that the short duration intermittent pulse of the heartbeat. Similarly, the filter can comprise a mechanical filter, for example if a board as described above has a resonant frequency close to that of a sinusoidal signal having a half cycle which approximates to the heartbeat signal, it will transmit that frequency in a preference to other frequencies and hence act as a filter.

In order to aid detection of the heartbeat signal, the electrical signal generated by the transducer preferably passes through at least one DC amplification stage.

In order to generate a sinusoidal oscillation having a half cycle which approximates to the heartbeat signal the oscillator element is preferably responsive to and the filter preferably passes frequencies in the range of 6.8Hz to 20Hz. The selected range of frequencies are preferably centred on a frequency of between 10 and 15Hz, preferably 12.5Hz.

Preferably, the processing circuitry comprises a threshold detector which activates an alarm when a signal passed through the filter rises or falls past a pre-set threshold. More preferably, the threshold detector comprises a comparator for comparing the signal passed by the filter with a control signal.

In order to give a good indication of the overall health of the living being, preferably, the monitor system also detects other forms of physical activity associated with a living being to es generate a signal which is passed to the processing circuitry. In this case it is preferable that the processing circuitry is responsive to all the signals it receives when generating a signal to 25 actuate an alarm.

o* According to a second aspect of the present invention there is provided a monitor system for monitoring the heartbeat of a living being, comprising a transducer responsive to the heartbeat to generate a heartbeat signal in the form of spaced heartbeat pulses, a filter circuit for filtering the heartbeat signal, and processing circuitry for processing the output of the filter circuit, wherein the filter circuit comprises an oscillating element responsive to each heartbeat R pulse having a duration within a predetermined range to generate a sinusoidal signal of decaying amplitude and a frequency within a predetermined range of frequencies centred on P:\OPER\KAT\48744-97.179- 28/6/99 a frequency of between 10Hz and According to a third aspect of the present invention there is provided a method for monitoring the heartbeat of a living being, remote from the living being, including the steps of: generating a heartbeat signal in the form of spaced heartbeat pulses, each pulse corresponding to one sensed heartbeat, and processing the heartbeat signal by generating a sinusoidal oscillation in response to each heartbeat pulse having a duration within a predetermined range, said sinusoidal oscillation having a decaying amplitude and a half cycle of a duration which approximates to the duration of the heartbeat pulse.

Embodiments of the present invention will now be described, by way of example only, with reference to the accompanying figures in which: Figure 1 shows schematically an embodiment of a system for monitoring a heartbeat 15 of a living being; Figure 2 shows the electronic circuitry used to process the signals from a transducer to distinguish between various forms of physical activity, including a heartbeat, associated with a living being; 9*9: Figure 3 shows a plurality of signals associated with the circuitry of Figure 2; and 0 0 '9 g 9 9 9o9 WO 98/19596 PCT/GB97/03024 6 Figures 4a to 4d schematically illustrate embodiments of support boards on whicha transducer is mounted.

Referring to Figure 1, there is shown a schematic embodiment of a monitor system for detecting physical activity, including heartbeat, associated with a baby. A cot (20) for a baby has underneath the mattress (30) a transducer arrangement The transducer arrangement is exited by one or more physical activities associated with a baby, such as a heartbeat, breathing or limb movement, and produces a signal having components derived from or related to any such physical activities.

The transducer arrangement (40) is coupled, via a suitable signal transmission medium to a cot unit The cot unit (50) comprises circuitry for processing the signals received from the transducer arrangement (40) to distinguish between various forms of physical activity emanating from or associated with a baby in the cot The cot unit (50) is, directly or indirectly, connected to and can trigger the activation of an alarm (60) in the event that the signal from the transducer arrangement (40) indicates that at least a selectable one of a plurality of physical activities associated with the baby has changed or terminated. For example, the cot unit (50) may activate an alarm if a determination is made to the effect that the signal no longer contains a component indicative of heartbeat. Various thresholds can be set which monitor not only the presence of a particular component of the signal but also the level or rate of that component.

The alarm (60) is typically located in a central location where it has a high probability of attracting the attention of a responsible adult during home use or nursing staff for hospital use. The alarm (60) may produce an audio output or a visual indication, for example, where it is undesirable to disturb other babies or patients in a hospital.

In one embodiment, the transducer arrangement comprises a suitably flexible support board (70) (see Figures 4a to 4d) having a piezo-ceramic device (80) centrally disposed thereon which produces a voltage when stressed or flexed. The piezo-ceramic device WO 98/19596 PCT/GB97/03024 7 is in the form of a disc. The support board (70) is constructed, for example, a flexibleplastic board as shown in Figure 1. Manufacturing the board from a suitable plastic can increase the sensitivity of the transducer arrangement as a whole to the physical activities of a baby.

Preferably the support board is made from ABS plastic due to the low cost and ability to shape and work the plastic. Alternative embodiments can be realised in which the flexible board is manufactured from metal, fibre board, hard board or other forms of plastic.

In a preferred embodiment mechanical means are utilised which increase the sensitivity of the transducer arrangement to the movement of the mattress or baby by locating a fulcrum (96) for the support board (70) directly below the piezo-electric element.

The flexible support board such as that shown in figure 4a can be designed so that it oscillates in response to a heartbeat signal so that the piezo device generates a sinusoidal signal of decaying amplitude having a half cycle which approximates to the heartbeat signal. In this case the baby's heartbeat can provide a regular stimulus to maintain the oscillation. The oscillations form a continuous sinusoidal signal so long as the heartbeat is present and so are much easier to detect than the short duration intermittent pulse of the heartbeat.

Optionally, the support board (70) is formed with, for example, a plurality of discontinuities, such as slots (90) (see Figures 4b to 4d). In a further embodiment the support board (70) utilises an arrangement of grooves on at least one of either the top or bottom surfaces thereof. The discontinuities ensure that the board is flexible and so will readily distort in response to the physical activities of the baby but is also strong enough to support the mattress and the baby.

In a preferred embodiment (see in Figures 4b to 4d) the slots (90) are radially disposed with respect to a central portion of the support (70) board where the piezo device (80) is located. A further embodiment (Figure 4d) also comprises further slots (90) disposed around the periphery of the support board In figure 4d the support board WO 98/19596 PCT/GB97/03024' 8 comprises a total of eight slots having at the ends thereof a hole which reduces the stresses conventionally associated with the slots.

The support board (70) is generally rectangular although other shapes are also possible, for example square or circular. Still further, a plurality of support boards may be utilised having piezo devices connected therebetween which produce electrical signals in response to relative movement of the support boards.

Preferably the lower surface of the support board (70) is held in an elevated position above and not in contact with the bottom of the cot. This enables the support board to deform independently of the rigid surface of the bottom of the cot and so increases its sensitivity to physical activity. Also, in certain embodiments it will enable the board to oscillate.

In the embodiments shown in Figures 4a to 4d, the degree by which the plastic support board (70) can flex is increased by using strategically placed feet (95) (shown in dotted lines) arranged to support the support board (70) such that movement thereof is not impeded by, for example, the bottom of the cot. The feet (95) are regularly disposed around the periphery of the support board (70) and one foot (96) is centrally disposed so as to provide a fulcrum support for the piezo device. Therefore, as the baby moves, including breathing and heartbeat movements, the board flexes which, in turn, causes the piezo device to produce a signal indicative of such movement.

The piezo device is situated at the position on the support board (70) which flexes the most and therefore stressed the piezo device the most. This position has been found to be typically the centre of the board, particularly if a fulcrum support is provided at the centre of the board.

An alternative embodiment can be realised in which the feet are omitted. According to this alternative embodiment, the plastic support board is supported at its edges by the frame of the cot such that the board if free to flex or oscillate and such movement is not impeded by the bottom surface, if any, of the cot.

WO 98/19596 PCT/GB97/03024 9 The monitoring system according to the present invention will detect all voluntary and involuntary movements of the living being, however, during deep sleep, the only physical activities which are present are the breathing and the heartbeat.

Optionally, the support board (70) comprises a removable protective covering (not shown) to guard against damage, for example, by bodily or other fluids.

The piezo-ceramic device (80) is connected to the cot unit (50) using co-axial cable (100).

Co-axial cable is preferred as it is less susceptible to mains interference than most cables.

However, as an alternative, suitable screened twisted pair may be utilised.

With reference to Figure 2, there is shown a diagram of a circuit (200) implementing detection means for distinguishing between various components, including heartbeat, of the signal derived from the transducer arrangement The circuit (200) detects signals in two main bandwidths of interest. A first circuit (202) determines whether or not the signal from the transducer arrangement (40) contains a component indicative of or derived from breathing or limb movement. A second circuit (204) determines whether or not the signal from the transducer arrangement contains a component indicative of or derived from the heartbeat of the baby.

The piezo device (80) is connected in parallel with a 20 M ohm resistor (206), to a DCvoltage amplifier (208). The amplifier is arranged to amplify the DC component of the signal from the piezo device by a factor of fifteen.

The first circuit (202) comprises a 5 Lh order low pass filter (210) designed to pass frequencies less than or equal to approximately one hertz, more particularly, frequencies below between a quarter of one hertz and one hertz.

The breathing and other low frequency signals, such as those generated by limb movement, are passed by the 51 order low pass filter (210).

WO 98/19596 PCT/GB97/03024 A DC correction is added to the signal from the DC amplifier (208) to counteract the DC signal offset introduced to the signal when it passes through the amplifier (208) and the low pass filter (210). The DC correction is generated in a conventional way by amplifying the signal from the low pass filter (210) by a factor of ten using a further DC amplifier (212) and then using an integrator (214) having an open loop gain and an RC time constant of five seconds. A feedback resistor (216) is utilised to provide a feedback current of 2 micro-amps. In an embodiment of the present invention, the resistor is a M ohm resistor and the capacitor is a 0.47 microfarad capacitor.

A threshold detector (218) is used to ultimately determine whether or not the output from the low pass filter (210) is indicative of the presence of breathing or limb movement. The threshold detector can be realised as a single comparator using an Op-amp (222) with controlled positive feedback (224) to provide the threshold and the stability of a Shmitt trigger circuit to eliminate false signals.

The output (220) of the threshold detector is connected to a microprocessor or other processing circuit within the cot unit (50) for further processing.

Referring to the lower portion of Figure 2, there is shown circuitry for the detection of a heartbeat. The output from the DC amplifier (208) is fed to a high pass passive filter (226) which passes all signals having a frequency of five hertz or greater. This high pass filter blocks low frequencies and so prevents the low amplitude heartbeat signal from being swamped by the high amplitude breathing and limb movement signals. It also isolates subsequent circuitry from the DC offset signal generated when the signal passed through the amplifier 208.

The output of the high pass filter (226) is amplified by a factor of two using a DC amplifier (228).

The output of the DC amplifier (228) is fed to an active band-pass filter (230) which acts as an oscillating element which because of the bandwidth selected is responsive to the WO 98/19596 PCT/GB97/03024 11 heartbeat signal to generate a sinusoidal signal of decaying amplitude having a half cyclewhich approximates to the heartbeat signal. The filter (230) passes this oscillation.

Because the band-pass filter (230) is an active filter when it is exited it will oscillate at the frequencies within the bandwidth of the filter. The bandwidth is selected to incorporate those frequencies that correspond to twice the duration of a typical heartbeat pulse.

Referring to Figure 3, the heartbeat signal is shown at When this signal enters the active band-pass filter (230) it will be masked by other signals associated with physical activity of the baby. Each pulse of the heartbeat signal has a duration of which will vary to some extent from baby to baby. Therefore, the active band-pass filter (230) is set to pass a bandwidth centred on a frequency of where t is the typical duration of a baby's heartbeat pulse. Thus, when a signal having a heartbeat signal component (a) enters the filter (230) it will cause the filter to oscillate at the frequency of 1/(2T) and so will generate a sinusoidal oscillation shown at in Figure 3 which sinusoidal oscillation is passed by the filter (230) and has a frequency of The active filter (230) acts as an oscillator with a gain of less than one and so between heartbeats the sinusoidal oscillation will decay. However, each time a heartbeat pulse enters the filter, the sinusoidal oscillation will be reinforced, as shown in figure 3.

In other words, the active band-pass filter (230) is responsive to a heartbeat signal to generate a sinusoidal signal of decaying amplitude having a half cycle (shaded portion in signal which approximates to the heartbeat signal (shaded portion in signal and passes only those frequencies in a selected range close to the frequency of the sinusoidal signal generated by the filter (230).

It has been found that the best results are achieved when the selected range of frequencies that the oscillator is exited by and which the filter passes is centred on between 10Hz and preferably 12.5Hz.

Preferably, the sinusoidal oscillation generated by one heartbeat pulse is still detectable when the filter (230) is exited by the next heartbeat pulse as shown in the signal in 12 Figure 3. However, the amplitude decay profile (330) is such that the signal decays to zero within a few seconds.

Using such filter (230) tuned to the heartbeat signal as described above enables the heartbeat to be reliably monitored.

Therefore, the short duration pulses of the heartbeat signal which are difficult to detect are used to generate a continuous sinusoidal signal which endures as long a heartbeat signal is present and so is easier to detect.

The active band-pass filter (230) has been implemented using two low-pass filters. The first low pass filter (232) is arranged to pass frequencies of less than 6.8 Hz while the second low pass filter (234) is arranged to pass frequencies of less than 20 Hz. The active band-pass filter (230) is constructed by inverting the output of the first low pass filter (232) and combining the inverted signal with the output of the second low pass filter in order to cancel all signal frequencies except those between 6.8 Hz and 20 Hz which are thus passed by the filter (230).

The frequency range 6.8Hz to 20Hz corresponds to a range of durations for a heartbeat pulse which are typical for a baby.

A threshold detector (236) is used to ultimately determine whether or not the output from the active filter (230) is indicative of the presence of a heartbeat. The threshold detector can be realised as a single comparator using an Op-amp (238) and a voltage divider (240) comprising two resistors to set the threshold level.

The output (250) of the threshold detector is connected to electronic circuitry or a microprocessor within the cot unit (50) for further processing.

The electronic circuitry or microprocessor is suitably designed or programmed to S determine whether or not it is necessary to sound the alarm. The presence or absence of AMENDED SHEET 13 the signals relating to heartbeat, breathing or limb movement can be utilised monitoring whether or not the baby is present in the cot. For example, the alarm may be sounded as soon as a determination has been made that the breathing/limb movement and/or heartbeat signals are not present.

The microprocessor and or electronic processing circuitry can be provided within the cot unit However, other embodiments can be realised in which the processing is performed remotely by, for example, a computer.

With further reference to Figure 1, in this embodiment which is suitable for monitoring a number of cots in a hospital ward, the cot unit (50) is connected via communication link (102) to a computer or a system controller (107). Also, a relay output unit (110) is provided under the control of the cot unit (50) and/or the system controller (107) to perform various functions, such as to lock the doors to a maternity ward to prevent a baby being stolen, send a signal to a pager informing the holder of the pager of the problem, or to sound an alarm.

The system controller (1'07) receives and displays status information associated with a plurality of cots. each having its own transducer arrangement (40) and associated cot unit The cot units (50) and the system controller (107) can operate an alarm independently. If the system controller (107) does not receive an appropriate response after interrogating a cot unit (50) via the communication link (102) it will go into alarm immediately. Likewise each cot unit (50) detects or monitors interrogation by the system controller (107) and will sound an alarm if it fails to be interrogated regularly. This will highlight hardware failure and guard against leads being cut.

Responsible adults that are authorised to remove a baby from a cot can be disable by a security device such as a magnetic swipe card device (112) or a security key-pad device.

AMENDED

SHEET

P.\oper\kat\48744-97 rspons.doc- 14/20A)I 14 In the version of the monitor for domestic use it is useful for the cot unit to include an audio-microphone to detect audible sounds made by the baby. The cot unit can then also incorporate a radio transmitter which transmits a radio signal carrying the audible sounds plus any alarm signal to a remote radio receiving unit which also incorporates a loud speaker. The receiving unit is mobile and can be carried by and located in the neighbourhood of an adult responsible for the baby. Therefore, if the baby cries, the crying noise will be transmitted by the receiving unit and the responsible adult can act appropriately. Further, if the heartbeat, breathing and/or limb movement activity of the baby ceases an audible alarm signal will be emitted by the receiving unit to alert the responsible adult to the danger.

Although the above embodiments have been described in relation to babies, it will be appreciated that the present invention can equally be applied to other living mammals such as adults, small children and even animals.

For example, in a hospital for patients suffering from senile dementia or similar illnesses, the monitor system could be used to warn nursing staff when such patients get out of bed during the night. In this case, it may be necessary to use two transducer arrangements spaced apart under the mattress in order to reliably detect the presence of an adult patient.

Throughout this specification and the claims which follows, unless the context requires otherwise, the word "comprise", or variations such as "comprises" or "comprising", will be understood to imply the inclusion of a stated integer or group of integers but not the exclusion of any other integer or group of integers.

The reference to any prior art in this specification is not, and should not be taken as, an acknowledgment or any form of suggestion that that prior art forms part of the common general knowledge in Australia.

Claims (14)

1. A monitor system for monitoring the heartbeat of a living being, comprising a transducer responsive to the heartbeat to generate a heartbeat signal in the form of spaced heartbeat pulses, a filter circuit for filtering the heartbeat signal, and processing circuitry for processing the output of the filter circuit, wherein the filter circuit comprises an oscillating element responsive to each heartbeat pulse having a duration in a predetermined range, said duration corresponding to a half cycle of a sinusoidal signal within a corresponding predetermined frequency range, to generate a sinusoidal signal of decaying amplitude having a half cycle of a duration which approximates to the duration of the heartbeat pulse.
2. A monitor system according to claim 1 wherein thesystem comprises a transducer responsive to the heartbeat to generate an electrical heartbeat signal. S 15 3. A monitor system according to claim 2 wherein the oscillating element is an electrical resonator circuit with a gain of less than unity.
4. A monitor system according to claim 3 wherein the filter circuit comprises an active o* filter.
5. A monitor system according to claim 4 wherein the active filter comprises: a first filter which passes frequencies below the bottom end of the predetermined frequency range; a second filter which passes frequencies below the top end of the predetermined 25 frequency range; and a combining element for combining the outputs of the first and second filters.
6. A monitor system according to any one of claims 2 to 5 wherein the electrical signal RAZ passes through at least one DC amplifier stage. -T O, 7. A monitor system according to claim 1 wherein the oscillating element comprises a (r op~ mechanical oscillator. P:\OPER\KAT48744-97.179- 28/6/99 -16-
8. A monitor system according to claim 1 or claim 7 wherein the filter comprises a mechanical filter.
9. A monitor system according to any preceding claim wherein said predetermined frequency range is from 6.8Hz to A monitor system according to any preceding claim wherein said predetermined frequency range is centred on a frequency of between 10Hz and
11. A monitor system according to any preceding claim wherein the processing circuitry comprises a threshold detector.
12. A monitor system according to claim 11 wherein the threshold detector comprises a comparator for comparing the signal passed by the filter circuit with a control signal.
13. A monitor system according to claim 11 or claim 12 and further comprising an alarm responsive to the output of the threshold detector.
14. A monitor system according to any one of claims 1 to 12 wherein the monitor system also detects other forms of physical activity associated with a living being to generate a signal(s) which is(are) passed to the processing circuitry.
15. A monitor system according to claim 14 and further comprising an alarm responsive to an output of the processing circuitry.
16. A monitor system for monitoring the heartbeat of a living being, comprising a transducer responsive to the heartbeat to generate a heartbeat signal in the form of spaced heartbeat pulses, a filter circuit for filtering the heartbeat signal, and processing circuitry for processing the output of the filter circuit, wherein the filter circuit comprises an oscillating S element responsive to each heartbeat pulse having a duration within a predetermined range to generate a sinusoidal signal of decaying amplitude and a frequency within a predetermined 0' range of frequencies centred on a frequency of between 10Hz and 1. I P:\OPER\KAT\48744-97.179 28/6/99 -17-
17. A method for monitoring the heartbeat of a living being, remote from the living being, including the steps of: generating a heartbeat signal in the form of spaced heartbeat pulses, each pulse corresponding to one sensed heartbeat, and processing the heartbeat signal by generating a sinusoidal oscillation in response to each heartbeat pulse having a duration within a predetermined range, said sinusoidal oscillation having a decaying amplitude and a half cycle of a duration which approximates to the duration of the heartbeat pulse. DATED this 28th day of June, 1999 MOVEMENT CONTROL SYSTEMS LIMITED By its Patent Attorneys 15 Davies Collison Cave 0 00 ".0
AU48744/97A 1996-11-06 1997-11-04 System and method for monitoring a heartbeat Ceased AU735569B2 (en)

Priority Applications (3)

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GB9623077A GB9623077D0 (en) 1996-11-06 1996-11-06 System and method for monitoring physical activity
GB9623077 1996-11-06
PCT/GB1997/003024 WO1998019596A1 (en) 1996-11-06 1997-11-04 System and method for monitoring a heartbeat

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CA (2) CA2269712A1 (en)
GB (1) GB9623077D0 (en)
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ZA (2) ZA9709924B (en)

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Publication number Priority date Publication date Assignee Title
ES2150381B1 (en) * 1998-10-01 2001-06-16 Asensio Pedro Monagas Device detection and warning the physical condition of babies and disabled perso nas and their usual environment.
JP4899117B2 (en) * 2004-11-02 2012-03-21 株式会社ユニークメディカル Heart rate / respiration sensor and biological monitoring apparatus using the same

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US3413573A (en) * 1965-06-18 1968-11-26 Westinghouse Electric Corp Microelectronic frequency selective apparatus with vibratory member and means responsive thereto
GB2150332A (en) * 1983-10-06 1985-06-26 Tranter Michael John Heartbeat monitor
US5479932A (en) * 1993-08-16 1996-01-02 Higgins; Joseph Infant health monitoring system

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US4595023A (en) * 1981-11-16 1986-06-17 Kenneth Bonnet Apparatus and method for detecting body vibrations
US4657025A (en) * 1981-12-09 1987-04-14 Carl Orlando Heart and breathing alarm monitor
GB2165979A (en) 1984-10-12 1986-04-23 John Michael Wood Monitor apparatus
GB2192460B (en) 1986-07-08 1990-08-01 John Keith Millns Respiratory movement sensing assemblies and apparatus
DE4001574A1 (en) * 1990-01-20 1991-07-25 Walz Elektronik Gmbh Vital organ's functioning tester for new born baby - has contactless pick=up providing signals subjected to Fourier transformation so that upper harmonics of heart beat can be evaluated
NZ238563A (en) * 1990-06-14 1994-09-27 Lesbar Pty Ltd Piezo-electric movement transducer for respiratory monitor

Patent Citations (3)

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US3413573A (en) * 1965-06-18 1968-11-26 Westinghouse Electric Corp Microelectronic frequency selective apparatus with vibratory member and means responsive thereto
GB2150332A (en) * 1983-10-06 1985-06-26 Tranter Michael John Heartbeat monitor
US5479932A (en) * 1993-08-16 1996-01-02 Higgins; Joseph Infant health monitoring system

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EP0938275A1 (en) 1999-09-01
EP0938274A1 (en) 1999-09-01
WO1998019596A1 (en) 1998-05-14
ZA9709926B (en) 1999-06-29
CA2269712A1 (en) 1998-05-14
ZA9709924B (en) 1999-06-29
AU4874597A (en) 1998-05-29
WO1998019597A1 (en) 1998-05-14
AU737561B2 (en) 2001-08-23
CA2269713A1 (en) 1998-05-14
GB9623077D0 (en) 1997-01-08
AU4874497A (en) 1998-05-29

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