WO2004000115A1 - Elimination des artefacts presents dans des electroencephalogrammes - Google Patents

Elimination des artefacts presents dans des electroencephalogrammes Download PDF

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Publication number
WO2004000115A1
WO2004000115A1 PCT/NZ2003/000124 NZ0300124W WO2004000115A1 WO 2004000115 A1 WO2004000115 A1 WO 2004000115A1 NZ 0300124 W NZ0300124 W NZ 0300124W WO 2004000115 A1 WO2004000115 A1 WO 2004000115A1
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Prior art keywords
signal
electrode
signals
signal path
artefact
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PCT/NZ2003/000124
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English (en)
Inventor
Christopher Edward Williams
Suded Mudhaffar Emmanuel
Mark Gunning
Sze Chung Woon
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Brainz Instruments Limited
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Priority to AU2003238754A priority Critical patent/AU2003238754A1/en
Publication of WO2004000115A1 publication Critical patent/WO2004000115A1/fr

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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
    • A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
    • A61B5/6801—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be attached to or worn on the body surface
    • A61B5/684—Indicating the position of the sensor on the body
    • A61B5/6841—Indicating the position of the sensor on the body by using templates
    • 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
    • A61B5/25—Bioelectric electrodes therefor
    • A61B5/279—Bioelectric electrodes therefor specially adapted for particular uses
    • A61B5/291—Bioelectric electrodes therefor specially adapted for particular uses for electroencephalography [EEG]
    • 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
    • A61B5/30—Input circuits therefor
    • A61B5/305—Common mode rejection
    • 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
    • A61B5/30—Input circuits therefor
    • A61B5/307—Input circuits therefor specially adapted for particular uses
    • A61B5/31—Input circuits therefor specially adapted for particular uses for electroencephalography [EEG]
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
    • A61B5/6801—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be attached to or worn on the body surface
    • A61B5/6843—Monitoring or controlling sensor contact pressure
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/72—Signal processing specially adapted for physiological signals or for diagnostic purposes
    • A61B5/7203—Signal processing specially adapted for physiological signals or for diagnostic purposes for noise prevention, reduction or removal
    • 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
    • A61B5/30—Input circuits therefor

Definitions

  • This invention relates to medical and veterinary diagnostic apparatus; more particularly the invention relates to electrode design and signal processing apparatus using electrophysiological signals from part of a mammal in order to determine condition and prognosis.
  • the invention refers to electroencephalography (EEG) and records made by that technique.
  • EEG electroencephalogram - typical signal level 10 microvolts
  • ECG electrocardiogram- typical signal level of interest 100-500 microvolts
  • reliable signals are useful.
  • EEGs are taken by non-specialist persons over long periods of time from infants or adults in intensive care
  • the output recording is liable to include many inadvertent and erroneous measurements as a result of the unintended inclusion of artefact signals of various origins in the event signal of interest.
  • 'artefact' denotes all non-event signals that contaminate the event signal of interest.
  • the precise nature and relative effect caused by any artefact signals will vary depending on the nature of the measuring instrument, the status of the patient, and the environmental conditions under which the measurements are taken.
  • a measurement instrument handles a measured signal comprised of the event signal of interest (which is usually available at a very low level only) along with a variable artefact component related to one or more non-event signals.
  • a measured signal comprised of the event signal of interest (which is usually available at a very low level only) along with a variable artefact component related to one or more non-event signals.
  • externally generated artefacts such as from electromagnetic fields
  • patient-generated artefacts such as signals from biological activity other than that being measured
  • equipment-generated artefacts such as those caused by noise, current fluctuations or overloading as well as mechanical artefacts, such as (d) caused by impact upon signal cables (connector noise, tribo-electric or microphonic effects) and (e) those caused by a shift of the electrode upon the underlying skin, as when the patient lies upon an electrode.
  • hum examples include mains leakage, imbalanced three-phase loads; harmonic currents of the mains frequency induced in any conductors as a result of coupling by magnetic fluxes or earth loops; switching and lightning-caused transients; diathermy/electrocautery machines, cellular telephones, computers, photonic interference and other sources of high-frequency interference; static electricity; aliasing; telemetry; salt bridges; and supply line transients.
  • Another application is in brain function assessment during and after open-heart surgery where diathermy, use of imaging machines, and general handling of the patients are likely to cause artefacts. Artefacts may be brief or continuous.
  • a hospital ward includes most of the above artefact sources and is an imperfect location for EEG recording, especially over a long period and where a neonatal patient requires continual care and frequent handling.
  • a long head cable is required, so that the EEG device can be kept out of the sterile incubator.
  • the signal is of very low amplitude and may fall further in certain disease processes.
  • the inventors are interested in making reliable EEG recordings in ordinary intensive-care wards by people without specialist skills and over a long period. People not especially trained in EEG techniques are required to make long-term EEG recordings, a task more difficult as the patient becomes worse. More severely brain-injured infants often show a low level of EEG activity and may exhibit much physical movement resulting in more artefacts so are more likely to be falsely diagnosed from a long-term EEG recording, made in order to assess the infant's chance of recovery.
  • the inventor's preferred devices include processes to derive evidence for seizures and to condense raw EEG data into a summarised form, both of which may be erroneous if interference is present.
  • the problem to be solved can be stated as "the need to recognise and exclude, on a continuous basis, corrupting signals from within an electrical signal (EEG) being collected from a patient”. This problem becomes more urgent as the patient's brain function decreases.
  • EEG electrical signal
  • Carim et al (US 6032060) condition the skin under a silver/chloride / gel electrode by passing a current through the skin to lower the impedance (unsuitable for neonatal infants).
  • Taheri (US 6434421) provides a skin electrode including a dielectric layer like a "supercapacitor” to reduce current flow.
  • Sherwin (US 4678865) reduces triboelectric effects by coating the insulator of the screened signal-carrying wires with graphite.
  • the invention provides a device for assessment of a status of a mammal which monitors electrophysiological signals developed within the body of the mammal; the device including in functional connection a first signal path including at least one contact electrode, a first electrode circuit, first electrode coupling means, first signal amplification means, first signal processing means, and output means for presenting a useful first output to an assessor, wherein the device provides means for rejection of at least some interfering signals likely to interfere with the electrophysiological signals, the rejection means including means having a separate functional (second) signal channel for continuously monitoring the environment of the mammal, including the environment occupied by the device near the mammal being monitored in order to detect said interfering signals, and means for deletion of said interfering signals from the electrophysiological signals prior to presentation at the output means, so that the output after modification may be relied upon to a greater extent as a true indication of the status of the mammal being monitored.
  • usable assessment procedures are selected from a range including: EEG (electroencephalogram); EMG (electromyogram); ECG or EKG (electrocardiogram), including fetal ECG; EOG (electrooculogram); and cranial impedance.
  • EEG electroencephalogram
  • EMG electromagyogram
  • ECG or EKG electrocardiogram
  • fetal ECG EOG
  • ECG electrocardiogram
  • cranial impedance e.g., cranial impedance
  • the device is particularly adapted for monitoring, over a long period, electrophysiological signals developed within the brain of the mammal so that the state of the brain of the mammal may be presented; the signals may be indicative or predictive of secondary phase brain damage.
  • the signals are deleted by 105 interruption of the EEG during the presence of the artefact signal in the second signal path.
  • the second or artefact signal is subtracted from the first or patient signal within an analogue or a digital signal processing stage, so that the artefact is deleted from the patient signal.
  • the second signal is used to control a gate capable of passing or blocking the first signal, so that the first signal is blocked during a period when an artefact is present.
  • the second signal is taken to a decision machine capable of evaluating the amplitude of the second (artefact) signal during an epoch and setting an output accordingly, so that the epoch may be accepted or rejected accordingly, so that the output of the device is made substantially free of at least some artefacts capable of disturbing a procedure of recording an electrophysiological signal.
  • the invention provides an electrode array including a set of electrodes for the recording of electrical signals originating within a mammalian patient, wherein the set of electrodes is laid down in desired positions upon a flexible substrate; the electrode array includes an equivalent circuit capable of at least partially simulating the passive electrical properties of the patient; the equivalent circuit being positioned close to at least some of the set of electrodes; the
  • 120 electrode array further includes conducting means connected to the equivalent circuit, similar to and alongside the conducting means used in relation to the set of electrodes, leading to connecting means capable of releasably connecting both the set of electrodes and the equivalent circuit to signal processing means.
  • the set of electrodes is disposable.
  • the invention provides means for continuously monitoring the environment in terms of electromagnetically radiated interfering signals likely to be picked up within the body of the mammal, or a bed, or the signal cables, and so interfere with the electrophysiological signals, the means including (a) a second electrode circuit placed in proximity to the first electrode circuit, thereby comprising an electrode assembly, and (b) second electrode
  • coupling means e.g cable or other data link
  • a second signal amplification means the output of which is connected to (d) signal removal means capable of removing said interfering signals from the first output at about the occurrence of said electromagnetically radiated interfering signals.
  • this second circuit is capable of responding to internally carried (abnormal) interference 135 within the device, such as transients carried within power supply conductors or earth loops - including earth loops extending to the patient's bed.
  • the second electrode circuit is substantially electrically isolated from the body of the mammal and includes at least one selected electrical component connected to a second amplifier input; the at least one component being selected so as to simulate a typical electrical impedance 140 presented to the first electrode circuit by the body of the mammal, when being monitored.
  • the second electrode circuit is intended for use with the usual symmetrical input (instrumentation) signal amplification means and includes three electrical resistances; one in series with each input, connected together at a common junction to a reference input through a third resistance, so as to simulate (as referred to an amplifier input) the typical electrical properties of the 145 body of the mammal being monitored.
  • the equivalent circuit presents to the signal processing means a similar impedance to that presented by the patient to the patient signal processing means.
  • the equivalent circuit presents a higher impedance than that presented by the patient with freshly applied electrodes.
  • the preferred equivalent circuit comprises (a) a resistance of between five and 50, or more preferably about 30 kilohms attached between each of the two inputs of the signal processing stage, and a common junction, and (b) a resistance of about 10 times the magnitude of the input resistances (or more preferably about 150K ohms) connected between the common
  • the properties of the resistance network are rendered more closely similar to the electrical properties of the patient as contacted through at least one skin or needle electrode by provision of capacitative reactance and/or inductive reactance.
  • the physical position of the equivalent circuit is close to at least one of the active electrodes.
  • the second electrode circuit may be electrically connected to the body of the mammal and for example it may be situated so as to collect "natural” artefact signals such as the electrooculogram (EOG) and muscle action potentials from the heart (ECG), or eyelids or other voluntary 165 muscles.
  • EOG electrooculogram
  • ECG muscle action potentials from the heart
  • eyelids or other voluntary 165 muscles such as the electrooculogram (EOG) and muscle action potentials from the heart (ECG), or eyelids or other voluntary 165 muscles.
  • the second circuit may comprise a set of accessible electrodes against which a gel-coated conductive surface may be placed, to better simulate a mammalian body.
  • one or more motion sensors incorporated into the second electrode circuit may be used to detect patient movement.
  • the electrode assembly including any electrical components, is supported upon a flexible electrode substrate material, including examples such as "Mylar” (TM) sheet, and appropriate fabrics.
  • TM Mylar
  • the invention provides means to detect mechano-electrical (triboelectric) interference to the cable, likely to interfere with the electrophysiological signals; the detection 175 means including a second electrode circuit placed in proximity to the electrode assembly and coupled through a substantial replica of the first electrode coupling means, placed in close proximity to the first electrode coupling means, to a second signal amplification means, coupled to a signal removal means capable of removing said mechano-electrical (triboelectric) signals from the first output at about the time of occurrence of said signals.
  • the detection 175 means including a second electrode circuit placed in proximity to the electrode assembly and coupled through a substantial replica of the first electrode coupling means, placed in close proximity to the first electrode coupling means, to a second signal amplification means, coupled to a signal removal means capable of removing said mechano-electrical (triboelectric) signals from the first output at about the time of occurrence of said signals.
  • detection means for recognising artefact signals polluting the wireless transfer process includes a second electrode circuit placed in proximity to the electrode assembly and coupled through a substantial replica of the first wireless electrode coupling means to a second
  • signal amplification means coupled to a signal removal means capable of removing said electromagnetic interference signals from the first output at about the time of occurrence of said signals.
  • a second wireless channel may be generated without being based upon a simulated electrode array in a second electrode circuit as previously described within this section.
  • the invention provides an impedance-based sensor of likely artefacts originating at an electrode as a result of change of electrical impedance when connected to the body of the mammal, wherein the assembly includes (a) means for continuously monitoring the electrical impedance, (b) means to identify any abrupt change in the electrical impedance as an indication of likely concurrent artefact, and (c) means to exclude the bio-electrical signal at about the time when
  • the means for continuously monitoring the electrical impedance comprises injection of a small alternating-current test signal into the circuit at a frequency high enough to be separable from the electrophysiological signals after amplification within bio-electrical signal processing means, 200 measuring the resulting voltage, and identifying any abrupt change in the voltage, thereby providing the separate functional signal channel previously mentioned in this section.
  • the invention (if based on digital computation) provides software capable through an output device of providing notification to an operator or assessor that, describes the amount of artefactual rejection activity in existence, and advises at least one appropriate remedy in 205 the case of an undesirable amount of artefacts.
  • the programme includes means to at least partially recognise one or more forms of artefact signal according to criteria, and to interrupt the first signal path during occurrence of said artefact signal, and to provide upon a display device information alerting an assessor to the nature and extent of the artefact signal, so that a relatively untrained assessor may take steps to reduce and 210 adverse effect of the artefact signal.
  • Fig 1 shows some flying-lead EEG electrodes in appropriate places on a human head.
  • Fig 2 comprises a schematic view of an electrode array 200 and a head stage 201 according to 220 the invention. A left channel and a right channel are shown here.
  • Fig 3 shows the layout of an example printed electrode array laid onto a flexible substrate and for use as a first signal path, and including a passive ("equivalent") circuit (the second signal path) mimicking the typical impedance of a patient.
  • Fig 4 shows the layout of another example printed electrode array also laid onto a flexible 225 substrate.
  • Fig 5 shows a different version of artefact-detecting circuit including a motion sensor.
  • Fig 6. is a basic circuit in terms of analogue electronics, showing impedance measurement.
  • Fig 7. is a basic circuit showing use of an RF link which might pick up artefacts, between a headstage and a device.
  • Fig 8. Trace (with stable impedance) showing the temporal relationship between step changes in impedance and artefactual signals in a range of frequency bands from neonatal EEG recordings. Top trade: impedance. Second trace: differentiated impedance. Further traces: 5, 15, 25, 60, 80 and 95 Hz. Fig 9. Trace (with unstable impedance) showing the temporal relationship between step changes 235 in impedance and artefactual signals in a range of frequency bands from neonatal EEG recordings. As Fig 8.
  • this invention is devised to clean up a clinical electrophysiological signal such as an EEG from most or all artefacts (interference) by a process of separately collecting and recognising each kind of artefact as far as possible given that they may be of unpredictable origin, and then
  • the invention thus provides a sensor for the detection of artefacts attributable to external or environmental noise, and takes or suggests appropriate action.
  • Most Examples provided herein have a physically distinct channel (the second signal path) for sensing of artefacts, although one (Example 4 - impedance) merges an artefact-sensing signal with the clinical signal during amplification, and then separates
  • the separate path may be a replicated input channel sensing signals across a "dummy patient” or “equivalent load” placed between electrodes (Example 1) best placed adjacent to the skin electrodes
  • the invention when used with wireless channels to transfer signals from a patient to a device may include an "artefact channel" OBxample 3) to collect wireless
  • interference whether electromagnetic interference or light waves. If the equivalent load is also in contact with the patient near an eye or the heart, physiological artefacts may be deleted.
  • This invention is particularly though not exclusively directed to use with / within EEG type apparatus known as a Brain Rescue Monitor or Brain Monitor (BM) as previously described by the inventors.
  • BM Brain Monitor
  • the BM provides for automated inspection of the digitised records particularly in relation to calculated parameters such as (the upper) "Spectral Edge” - a frequency in Hz related to brain function and trends of brain function over time.
  • the BM is mainly used with neonatal or pre-term infants under intensive care, but the same approach can be scaled for use with adult humans such as those
  • prior art EEG electrodes are shown in simplified format, applied to an infant head 100 in Fig 1.
  • Two pairs of electrode assemblies 101 + 102 and 104 + 105 are placed over the parasagittal region/fronto-parietal-occipital cortex. Each is coupled via a flexible, shielded cable to a connector 108.
  • a ground reference pad 103 is likewise coupled to the connector 108.
  • the flying-lead electrodes indicated in Fig 1 are likely to be placed wrongly and it is particularly useful in a long-term recording to have consistent placement if the electrodes must be replaced by different people during the recording period.
  • the skin contact electrodes eg 103, 105) are shown with slanted shading.
  • the BM invention has always been capable of operating with one electrode pair on one 275 side of the head although more reliable and useful results are obtained by monitoring both sides if possible. It will be evident to the skilled reader that this invention is not limited to the illustrated left pair and right pair of electrodes used together. Either pair on its own will suffice but we prefer to provide symmetrical pairs in our arrays (see below).
  • Fig 2 shows a block diagram of this form of the invention.
  • Numeral 200 indicates the electrode array, 108 indicates a connector, and the dashed block 201 indicates an appropriate head stage amplifier, containing amplifiers 202X, optional frequency limiting circuitry (not shown), a multiplexer and analogue to digital converter 203, and a serial input/output interface 204 connected to a communications line 205 running to a suitably programmed computer.
  • amplifiers containing amplifiers 202X, optional frequency limiting circuitry (not shown), a multiplexer and analogue to digital converter 203, and a serial input/output interface 204 connected to a communications line 205 running to a suitably programmed computer.
  • 202L and 202R are standard signal (instrumentation) amplifiers connected to patient electrodes - the two pairs of patient skin (or sometimes subcutaneous) electrodes 101 with 102, 104 with 105, and 103 as a reference or ground electrode.
  • 202AL and 202AR are also standard signal (instrumentation) amplifiers connected instead to the simulated impedances, A passive resistor matrix serving as an equivalent circuit is shown in duplicate; resistors 206L and 207L are connected
  • resistors 206R and 207R are connected to inputs of another amplifier and grounded by resistor 208R, in a "Y" configuration with one resistor included in each limb.
  • Optical isolation is desirable at the interface, in order to avoid passing currents through the patient.
  • the communications line is at present an RS-232 protocol cable, but may instead conform to other protocols even those employing wireless links. It
  • Example 2 there are several parts to the Example; there is an EEG electrode array 200 constructed upon a 300 flexible base by a conductor-printing technique (as is known in the art) but also including a "simulated patient” made of an “equivalent circuit” carried upon the flexible base and connected to similar amplifiers and signal processing means to that used for the EEG itself (201), and there is a signal processor 210 (here, placed within the BM) for acting on the EEG signal whenever supra- threshold signals appear from the simulated patient. It will be appreciated that the cost of 305 duplication is minimal when flexible printed-circuit manufacturing techniques are used in construction.
  • Various flexible electrode arrays (200, with similar versions in Fig 3 and Fig 4) are primarily intended to provide bilateral recording of the EEG from skin electrodes applied to the cranium of a neonatal or pre-term infant.
  • the array is adapted by size and shape in order to be positionable over
  • Array 310 the areas of the brain most likely to exhibit pathological changes and is intended for long-term use over some days.
  • Dimensions of an example array (Fig 3) for the above purpose is 22 cm from the connector 108 to the far edge of the reference electrode 103, and the centres of the skin electrodes 101 and 104 are 8.5 cm apart, though even within this specific application sizes may be varied. Arrays for use in adult humans or with other mammals may have other appropriate dimensions. As
  • the array includes two pairs of symmetrical pads (electrodes 101 with 102, and 104 with 105) intended for use with the usual balanced (instrumentation-type) low-level amplifiers.
  • the contact areas of the pads are preferably made of chlorided silver as is known in the art, although other conductive materials may be used such as graphite, gold, or stainless steel.
  • a "HydroGel" (TM) patch covers each electrode 101, 102, 103, 104, and 105.
  • Each pair of pads is placed to a side of a central axis and at an angle of about 45 degrees (as illustrated).
  • the reference (ground) electrode of a similar material is at the end of an extended conductor on a long flexible strip 305 along the central axis. All conductors on the flexible substrate are shown here as black lines such as 306, leading to reference pad 103 which has a sticky tab 301 at its end.
  • the preferred material for the substrate is polyethylene terephthalate ("Mylar” TM) although other substances suitable for use in flexible printed circuit manufacture may be used. (We are now considering woven cloth substrates which may be flexed in two directions, and insulated multi- strand copper wire in conjunction with robotic assembly).
  • the conductive strips are preferably made of silver, which is not expensive. Copper tracks result in a stiffer electrode array.
  • the connector comprises part of a head stage amplifier 201, locatable close to the patient and including all the analogue amplification equipment and analogue-to-digital conversion devices needed for operation of the BM so that a conventional serial cable link (205) carries data to the computer processor itself.
  • an array of this type may also include the sensing elements for an artefact sensor as described elsewhere in this specification.
  • the extra contacts used in this example are linked to the equivalent circuit mounted upon the substrate and as described below.
  • This electrode array may also or alternatively include devices for sensing other modalities, such as temperature, or a patient motion sensor. Patient motion, whether caused by nursing or by the patient's own activity often
  • EMG electromyogram
  • a transcranial optical density measurement (or trend) sensor for example may be provided as an emitter and sensor (one on each side) of pulsed or steady visible or infra-red light for trans-cranially sensing blood flow.
  • Hydrogel being transparent and clinically acceptable is also a useful optical coupling medium.
  • An outer electrical (“Faraday”) screen (209 in fig 2) of conductive silver for example may be applied over the "cable" part 107 of the electrode array and along each arm up to the position of the resistors (206L, 207L, 208L), which allows higher resistor values to be used, and a foam covering 355 (not shown) may be applied over the entire object except the electrode contact surfaces so that the device seems softer and is less likely to cause trauma.
  • Fig 4 shows a different example configuration of electrode array (at a different scale to Fig 3) having similar sensing pads (101, 102, 104, and 105 with reference 103) on a flexible substrate.
  • the on-substrate tracks between the connector 108 and each pad are not shown for clarity.
  • 360 rejection circuit or at least part thereof, as previously described, is preferably mounted upon the substrate as in the case of example 3.
  • the reference electrode 103 When applied on to a cranium, the reference electrode 103 would be placed medially towards the forehead while the pairs of sensing electrodes (101 with 102, 103 with 104) would lie on each side of the median line over an area of the brain to be monitored.
  • the pairs of sensing electrodes (101 with 102, 103 with 104) would lie on each side of the median line over an area of the brain to be monitored.
  • the sensing electrodes may be best placed over the areas of the brain supplied by the middle cerebral arteries, and the dimensions of the electrode array would be adjusted to suit. These particular designs do not show any means to collect eye- related natural artefacts, mainly because our preferred recording sites are well back on the head from the forehead.
  • the preferred equivalent circuit comprises a passive set of resistive elements mounted upon the substrate and sharing a similar geometry of connecting elements to those used by the active disc electrodes 101, 102 and 104, 105, so that external sources of artefactual signals have a similar effect on both the artefact channel and the patient signal channel.
  • the equivalent circuit is similarly prone to picking up mechanical and electrical interference in the same way as the EEG electrodes. It may
  • the example equivalent circuit (see Fig 2) comprises a "Y" or branched circuit. Two arms of the "Y” are each connected between an input of an instrumentation amplifier through a resistor (206L and 207L) to a common point; the common point being connected through a third resistor 208L to
  • the lead pickup effect becomes more effective as a capacitative pickup if the terminating resistors are increased in value.
  • the equivalent circuit is placed in a dedicated area included in the layout of the disposable electrode array (Fig 3) to be placed on the patient's head.
  • the preferred embodiment uses surface-mount resistors attached to pads in the usual way (using low melting point solder, or conductive paint) and the predominant electrical property is hence purely resistive though the entire circuit includes some capacitance to ground. Because some electrode material surfaces exhibit non-ohmic properties, the invention allows for the resistive elements to be supplemented with either or both capacitative and inductive elements in order to
  • 395 more closely simulate a patient's impedance at various AC frequencies.
  • stainless steel tends to behave as if there is a series capacitor between the electrode and the patient, particularly at low frequencies. This may be due to the thin film of oxide that forms on any surface of that metal.
  • the actual supplementation that is likely to be useful depends in part on the frequency band selected for operation of the subsequent amplifiers. More complicated networks than those described here
  • 400 may for example include several resistors in series with capacitors bridging some of them, in order to replicate the behaviour of particular types of skin electrode.
  • FIG. 5 A variation of the above artefact amplifier circuit is shown in Fig 5.
  • This circuit 500 is intended to enhance differences between signals at the input whereas the previous amplifier was constructed to be as symmetrical as possible in which case those signals picked up along the lead 107 (fig 3) might 405 be the predominant type of artefact signal passed on for processing.
  • the instrumentation amplifier 501 is itself preferably mounted remotely from the parts 502-507 which are preferably upon the electrode array.
  • the amplifier block 101 is preferably an instrumentation-type amplifier capable of rejecting common-mode signals, (although a single-ended amplifier might suffice, with a rearranged circuit).
  • the non-inverting input includes two resistors 502 and 505, preferably together having the same value as the resistor 503 in the inverting input.
  • Resistor 508 mainly serves to provide a return path for input bias currents.
  • One asymmetrical input is an unscreened capacitative pickup plate 504, in dimensions like an electrode pad 101 (etc) but coated with insulation and not in contact with the patient, is attached to the resistor chain and in turn to one side (in an asymmetrical
  • This plate assists in collecting changing electric field signals such as from unscreened mains cables.
  • Another asymmetrical input is an open coil 507 is optionally wired across the free end of the resistors in order to convert changing local magnetic fields into a differential input to the amplifier 501.
  • the coil is shunted with a resistor (not shown) in order to reduce any undesired resonance effects. The orientation of this coil (perhaps 20-
  • 420 50 turns is preferably one that best collects flux from those changing magnetic fields that also cause interference within the patient/electrode/cable circuit.
  • a permanent magnet 506 perhaps made of a ferrite, is resiliently mounted in or beside the coil 507 so that mechanical movement of the magnet in relation to the coil generates a differential input. That movement may occur if the electrode array is accelerated.
  • the output 509 of the amplifier is more likely to carry derivatives of electromagnetic or mechanical artefacts, and the amplifier may be operable at a lower gain and consequently in a more reliable way.
  • the instrumentation amplifier used for amplifying artefacts is located alongside the amplifier used 430 for EEG signal processing and is provided with similar filters for the setting of passbands in terms of low and high frequencies and is typically run at the same gain.
  • the EEG amplifier is operated so that it does not enter saturation as a result of amplified DC offset levels. (The artefact amplifier should not experience DC offsets, being kept apart from electrochemical effects).
  • the second approach, more suitable for large level artefact signals is to use the artefact signal to control a gate in order to interrupt the data signal during the presence of the interference. Gating may be carried out in either an analogue (as with a sample-and-hold module), or in a digital signal processing stage.
  • the third approach which has been adopted within the BM 210 is a kind of gating process. It comprises additional software processing in or about the existing BM process for handling the EEG signals in (typically) four-second blocks.
  • the software tests a number of parameters as shown in the table below. This approach is compatible with simultaneous use of other methods to sense error conditions such as the saturated amplifier or the disconnected electrode.
  • the preferred 450 method treats data to be deleted as a missing data point that is interpolated using medians or averages, or with large blocks rejects an entire block and flags it if any problem is detected during a four second epoch.
  • the artefact sensing approach described herein will not see artefacts developed within the patient (eg heart or voluntary muscle activity) or within the patient signal processing chain (eg amplifier saturation) as signals within the artefact channel.
  • an electrode assembly may include a motion sensor to detect physical movements of the electrode sensor array, such as when the patient moves, the incubator is bumped, or nursing care is being given.
  • motion sensors include: the low-impedance group such as magnet & coil assemblies, (possibly connected within the passive resistor array between resistor 206x and 207x so that signals appear as artefact signals), the
  • high-impedance group such as electret microphones and piezoelectric devices
  • the active group of integrated circuits for example including structures capable of detecting movement such as accelerometer devices.
  • a circuit path is not shown in Fig 2, nor is a motion sensor shown in Fig 3. Because the electrode array of silver and including a resistor array costs only about NZD 1.50 and is essentially disposable, a motion sensor should be preferably selected with cost versus benefit in
  • the appropriate method for controlling this form of artefact is to take care to extend the duplicated electrode assembly with a closely similar electrode cable assembly made of the same kind of cable materials running in parallel with the signal cable, and treat any signal arising from the duplicate cable as an artefact. This will also collect any electromagnetic interference that would be collected by the signal cable.
  • Software recognition may be largely based
  • a second channel may be implemented by procedures well-known to those skilled in the art such as time or frequency multiplexing.
  • Electrode impedance is not a constant. It may rise as the hydrogel dries out, if the electrode is partly 495 detached, if the skin may sweat or desquamate, or other changes occur with time. Impedance is liable to change a lot if the patient is lying on or pressing against a skin electrode. (It should be noted that needle electrodes exhibit worse electrical connection properties such as that the impedance is more likely to change than chlorided silver gel electrodes. Typical needle electrode impedances are about 100K ohms as against 10 K ohms, and the oxide on the stainless steel surface 500 causes non-linear resistance effects at low voltages. They are more affected by patient movement).
  • Figs 8 and Fig 9 illustrate two different patient records for each of which the top curve is of impedance Z, next is dZ/dt, then EEG recordings at 5, 15, 25, 60, 80, and 95 Hz, all against time.
  • the impedance trace lacks step changes and the EEG trace 505 is relatively free of artefact.
  • different traces have different content as would be expected for an EEG recording.
  • the impedance trace includes many step changes and the differentiated impedance trace spikes can be correlated with spikes in all the frequency bands together and each of those cross-band sets is timed together with a step change of impedance.
  • Fig 6 shows the principles of impedance sensing. It should be noted that the diagram illustrates the principle of the invention in terms of analogue electronic modules, whereas many of the functions are likely to be realised in software during signal processing. A sine wave of a fixed frequency
  • module 602 is separated from the EEG signal by means such as high-pass filtering with capacitor 607 and synchronous rectification within module 602, and its level is assessed.
  • Module 602 may be a Signetics NE 5521 or equivalent). Whenever the level changes rapidly the EEG signal is interrupted. In this illustration we use a coupling capacitor 608 to pass only rapid changes to an input of a window comparator 603 the other input of which is connected within a voltage divider
  • a preferred analogue deletion circuit is a sample and hold circuit in which the "hold” function serves as a deletion mode. As shown by the coincidence between electrode change and artefacts in Fig 8, this process should always trap an artefact signal so
  • the selected sine wave frequency is above the used range of EEG signal frequencies and where more than electrode is being measured, a different frequency is used in each different circuit.
  • the comparator output may also be taken to a display device 606 used to indicate to an operator how frequently the electrode impedance is altering in a significant way, and in general to indicate
  • Devices 603, 604, and 606 at least may be replaced by software routines within a software version of the device, for example as part of a spectral edge detection module for the Brain Monitor. That 560 improvement permits a greater range of criteria to be taken into account, as shown in the following non-limiting table which shows some of the criteria taken into account at the Data Validation step in current software for the BM. Criteria could be expressed in absolute or in relative terms.
  • Data validation criteria include:
  • the software alters the operator's control panel display in accordance 565 with the fault detected, if any, and displays the percentage of 4 second epochs rejected per minute.
  • the software is preferably capable of producing at least one advisory message to a user when the likely presence of at least one artefact is established.
  • This advisory message can comprise 570 one or more of (a) naming the type or source of at least one artefact, or (b) the magnitude of at least one artefact, (c) the total artefact magnitude and possibly (d) the option to remove the part of the signal or signals attributable to artefact(s).
  • Use of helpful and/or advisory displays is in accord with the intention that the machine can be operated by persons not skilled in collecting EEG recordings. Ways to determine in software where the origin of artefact signals may be found, so that a remedial 575 message can be put on a computer screen, include the following elimination process.
  • 580 interference is present in the radio link.
  • the frequency content of the equivalent resistor channel may be helpful. Lower frequencies are more likely to relate to movement artefacts etc and higher frequencies suggest interference such as electrocautery.
  • Detection of periodic artefact signals such as ventilator hum, heart activity, or breathing movements may be based on frequency measurements.
  • an electromyogram procedure used in physiotherapy or sports medicine is particularly likely to be affected by motion-induced interference.
  • the artefact channel may be converted into a 605 presence/absence digital form within the head stage hence substantially reducing the volume of data sent, to the BM.
  • a threshold may from time to time be programmed into the head stage from the BM, using the radio link - if it is bidirectional.
  • the invention provides a simple, relatively cheap, user-transparent apparatus and method for 610 reduction of the total content of artefacts within a signal collected from a patient.
  • the invention is capable of detection and rejection of externally generated artefacts.
  • An advantage of extensive monitoring of artefacts is that the electrode impedance status itself may be reported to a person so that electrodes can be replaced or re-coated as required before the connection fails completely.
  • the invention therefore enhances the reliability of data collected from a patient and so increases the relationship between information gleaned from the data and clinical procedures undertaken in response.
  • the information enhances the reliability of a brain rescue monitor used to 620 monitor the activity of a patient's brain over possibly a long period.

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Abstract

Cette invention se rapporte à un dispositif pour l'affichage et l'analyse de signaux cliniques d'électroencéphalographie (EEG) qui recueille les signaux d'artéfacts dans une voie de signaux séparée et les utilise après traitement pour en débarrasser l'électroencéphalogramme. La duplication de l'amplificateur, du câble et des électrodes et l'utilisation d'une charge d'entrée (factice) équivalente fournit un canal d'artéfacts qui recueille les interférences électromagnétiques provenant de la zone contenant les signaux du patient et les signaux triboélectriques provenant des câbles à signaux du patient. L'impédance des conducteurs d'électrodes peut être suivie en continu pour détecter les variations rapides d'impédance, qui sont réputées être la cause des artéfacts. Un logiciel peut servir à fournir des messages correctifs à l'utilisateur.
PCT/NZ2003/000124 2002-06-19 2003-06-19 Elimination des artefacts presents dans des electroencephalogrammes WO2004000115A1 (fr)

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Cited By (27)

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WO2006111876A1 (fr) 2005-04-19 2006-10-26 Philips Intellectual Property & Standards Gmbh Systeme et procede de mesure des signaux bioelectriques d'un utilisateur
WO2007109745A2 (fr) * 2006-03-22 2007-09-27 Emotiv Systems, Pty Ltd. Électrode et casque d'électrodes
WO2008086565A1 (fr) 2007-01-15 2008-07-24 Impedimed Limited Système de surveillance
WO2010129026A3 (fr) * 2009-04-29 2011-02-03 Bio-Signal Group Corp. Ensemble pour électroencéphalographe
US8103337B2 (en) 2004-11-26 2012-01-24 Impedimed Limited Weighted gradient method and system for diagnosing disease
US20120143020A1 (en) * 2009-04-29 2012-06-07 Bio-Signal Group Corp. Eeg kit
US8233974B2 (en) 1999-06-22 2012-07-31 Impedimed Limited Method and device for measuring tissue oedema
GB2499595A (en) * 2012-02-21 2013-08-28 James Roche Infant EEG electrode system
US8761870B2 (en) 2006-05-30 2014-06-24 Impedimed Limited Impedance measurements
US8836345B2 (en) 2007-11-05 2014-09-16 Impedimed Limited Impedance determination
US9149235B2 (en) 2004-06-18 2015-10-06 Impedimed Limited Oedema detection
US9392947B2 (en) 2008-02-15 2016-07-19 Impedimed Limited Blood flow assessment of venous insufficiency
US9504406B2 (en) 2006-11-30 2016-11-29 Impedimed Limited Measurement apparatus
US9585593B2 (en) 2009-11-18 2017-03-07 Chung Shing Fan Signal distribution for patient-electrode measurements
US9615767B2 (en) 2009-10-26 2017-04-11 Impedimed Limited Fluid level indicator determination
US9615766B2 (en) 2008-11-28 2017-04-11 Impedimed Limited Impedance measurement process
US9724012B2 (en) 2005-10-11 2017-08-08 Impedimed Limited Hydration status monitoring
US10136862B2 (en) 2012-05-30 2018-11-27 The Board Of Trustees Of The Leland Stanford Junior University Method of sonifying brain electrical activity
US10188307B2 (en) 2012-02-23 2019-01-29 Bio-Signal Group Corp. Shielded multi-channel EEG headset systems and methods
US10307074B2 (en) 2007-04-20 2019-06-04 Impedimed Limited Monitoring system and probe
CZ308124B6 (cs) * 2018-07-09 2020-01-15 Deymed Diagnostic S.R.O. Registrační elektroda pro měření elektrofyziologického signálu
US10555670B2 (en) 2017-07-10 2020-02-11 International Business Machines Corporation Adaptive filtration of sweat artifacts during electronic brain monitoring
WO2020049430A1 (fr) * 2018-09-04 2020-03-12 Johnson & Johnson Consumer Inc. Appareil et procédé pour évaluer l'émotion des nourrissons et des jeunes enfants
CN112043262A (zh) * 2020-09-28 2020-12-08 南京伟思医疗科技股份有限公司 一种新生儿脑电信号伪差的识别系统和方法
US11471088B1 (en) * 2015-05-19 2022-10-18 The Board Of Trustees Of The Leland Stanford Junior University Handheld or wearable device for recording or sonifying brain signals
US11660013B2 (en) 2005-07-01 2023-05-30 Impedimed Limited Monitoring system
US11737678B2 (en) 2005-07-01 2023-08-29 Impedimed Limited Monitoring system

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US6487295B1 (en) * 1998-09-25 2002-11-26 Ortivus Ab Adaptive filtering system and method
EP1050270A1 (fr) * 1999-05-07 2000-11-08 Bruker Medical SA Procédé et dispositif pour l'acquisition d'un électrocardiogramme
WO2003000128A2 (fr) * 2001-06-21 2003-01-03 Aspect Medical Systems, Inc. Systeme et procede de detection et de suppression d'un artefact de bruit de radiofrequence a partir de signaux biopotentiels

Cited By (34)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US8233974B2 (en) 1999-06-22 2012-07-31 Impedimed Limited Method and device for measuring tissue oedema
US9149235B2 (en) 2004-06-18 2015-10-06 Impedimed Limited Oedema detection
US8103337B2 (en) 2004-11-26 2012-01-24 Impedimed Limited Weighted gradient method and system for diagnosing disease
US8150489B2 (en) 2005-04-19 2012-04-03 Koninklijke Philips Electronics N.V. System and method for measuring bioelectrical signals of a user
WO2006111876A1 (fr) 2005-04-19 2006-10-26 Philips Intellectual Property & Standards Gmbh Systeme et procede de mesure des signaux bioelectriques d'un utilisateur
US11737678B2 (en) 2005-07-01 2023-08-29 Impedimed Limited Monitoring system
US11660013B2 (en) 2005-07-01 2023-05-30 Impedimed Limited Monitoring system
US9724012B2 (en) 2005-10-11 2017-08-08 Impedimed Limited Hydration status monitoring
US11612332B2 (en) 2005-10-11 2023-03-28 Impedimed Limited Hydration status monitoring
WO2007109745A3 (fr) * 2006-03-22 2008-07-24 Emotiv Systems Pty Ltd Électrode et casque d'électrodes
WO2007109745A2 (fr) * 2006-03-22 2007-09-27 Emotiv Systems, Pty Ltd. Électrode et casque d'électrodes
US8761870B2 (en) 2006-05-30 2014-06-24 Impedimed Limited Impedance measurements
US9504406B2 (en) 2006-11-30 2016-11-29 Impedimed Limited Measurement apparatus
WO2008086565A1 (fr) 2007-01-15 2008-07-24 Impedimed Limited Système de surveillance
AU2008207332B2 (en) * 2007-01-15 2013-05-23 Impedimed Limited Monitoring system
US10307074B2 (en) 2007-04-20 2019-06-04 Impedimed Limited Monitoring system and probe
US8836345B2 (en) 2007-11-05 2014-09-16 Impedimed Limited Impedance determination
US9392947B2 (en) 2008-02-15 2016-07-19 Impedimed Limited Blood flow assessment of venous insufficiency
US9615766B2 (en) 2008-11-28 2017-04-11 Impedimed Limited Impedance measurement process
US9408575B2 (en) 2009-04-29 2016-08-09 Bio-Signal Group Corp. EEG kit
WO2010129026A3 (fr) * 2009-04-29 2011-02-03 Bio-Signal Group Corp. Ensemble pour électroencéphalographe
US20120143020A1 (en) * 2009-04-29 2012-06-07 Bio-Signal Group Corp. Eeg kit
US9615767B2 (en) 2009-10-26 2017-04-11 Impedimed Limited Fluid level indicator determination
US9585593B2 (en) 2009-11-18 2017-03-07 Chung Shing Fan Signal distribution for patient-electrode measurements
WO2013124366A1 (fr) * 2012-02-21 2013-08-29 James Roche Système d'électrodes d'électroencéphalogramme
GB2499595A (en) * 2012-02-21 2013-08-28 James Roche Infant EEG electrode system
US10188307B2 (en) 2012-02-23 2019-01-29 Bio-Signal Group Corp. Shielded multi-channel EEG headset systems and methods
US10136862B2 (en) 2012-05-30 2018-11-27 The Board Of Trustees Of The Leland Stanford Junior University Method of sonifying brain electrical activity
US11471088B1 (en) * 2015-05-19 2022-10-18 The Board Of Trustees Of The Leland Stanford Junior University Handheld or wearable device for recording or sonifying brain signals
US10555670B2 (en) 2017-07-10 2020-02-11 International Business Machines Corporation Adaptive filtration of sweat artifacts during electronic brain monitoring
CZ308124B6 (cs) * 2018-07-09 2020-01-15 Deymed Diagnostic S.R.O. Registrační elektroda pro měření elektrofyziologického signálu
WO2020049430A1 (fr) * 2018-09-04 2020-03-12 Johnson & Johnson Consumer Inc. Appareil et procédé pour évaluer l'émotion des nourrissons et des jeunes enfants
CN112043262A (zh) * 2020-09-28 2020-12-08 南京伟思医疗科技股份有限公司 一种新生儿脑电信号伪差的识别系统和方法
CN112043262B (zh) * 2020-09-28 2023-01-31 南京伟思医疗科技股份有限公司 一种新生儿脑电信号伪差的识别系统和方法

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