WO2006011128A1 - Appareil de surveillance de perfusion cerebrale - Google Patents

Appareil de surveillance de perfusion cerebrale Download PDF

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Publication number
WO2006011128A1
WO2006011128A1 PCT/IL2005/000632 IL2005000632W WO2006011128A1 WO 2006011128 A1 WO2006011128 A1 WO 2006011128A1 IL 2005000632 W IL2005000632 W IL 2005000632W WO 2006011128 A1 WO2006011128 A1 WO 2006011128A1
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WO
WIPO (PCT)
Prior art keywords
current
electrode
electrodes
head
voltage
Prior art date
Application number
PCT/IL2005/000632
Other languages
English (en)
Other versions
WO2006011128A8 (fr
Inventor
Aharon Shapira
Alon Rappaport
Shlomi Ben-Ari
Yosef Reichman
Ofer Barnea
Original Assignee
Orsan Medical Technologies Ltd.
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Priority claimed from US10/893,570 external-priority patent/US7998080B2/en
Application filed by Orsan Medical Technologies Ltd. filed Critical Orsan Medical Technologies Ltd.
Priority to JP2007520969A priority Critical patent/JP4904263B2/ja
Priority to PCT/IL2005/000632 priority patent/WO2006011128A1/fr
Priority to EP05752203A priority patent/EP1786316B1/fr
Priority to CN2005800310897A priority patent/CN101052344B/zh
Priority to US11/572,141 priority patent/US8187197B2/en
Priority to PCT/IB2006/050174 priority patent/WO2006134501A1/fr
Priority to DE602006010378T priority patent/DE602006010378D1/de
Priority to AT06701857T priority patent/ATE447886T1/de
Priority to JP2008516457A priority patent/JP5225080B2/ja
Priority to PT06701857T priority patent/PT1895902E/pt
Priority to US11/921,937 priority patent/US8512253B2/en
Priority to ES06701857T priority patent/ES2336137T3/es
Priority to CN200680029920XA priority patent/CN101242781B/zh
Priority to EP06701857A priority patent/EP1895902B1/fr
Priority to DK06701857.2T priority patent/DK1895902T3/da
Publication of WO2006011128A1 publication Critical patent/WO2006011128A1/fr
Publication of WO2006011128A8 publication Critical patent/WO2006011128A8/fr
Priority to US11/610,553 priority patent/US8211031B2/en
Priority to US13/484,519 priority patent/US20130109979A1/en
Priority to US13/941,587 priority patent/US20140163404A1/en

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/02—Detecting, measuring or recording pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure
    • A61B5/026—Measuring blood flow
    • A61B5/0295—Measuring blood flow using plethysmography, i.e. measuring the variations in the volume of a body part as modified by the circulation of blood therethrough, e.g. impedance plethysmography
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/02—Detecting, measuring or recording pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure
    • A61B5/026—Measuring blood flow
    • A61B5/0261—Measuring blood flow using optical means, e.g. infrared light
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/02—Detecting, measuring or recording pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure
    • A61B5/026—Measuring blood flow
    • A61B5/0265—Measuring blood flow using electromagnetic means, e.g. electromagnetic flowmeter
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/05—Detecting, measuring or recording for diagnosis by means of electric currents or magnetic fields; Measuring using microwaves or radio waves 
    • A61B5/053—Measuring electrical impedance or conductance of a portion of the body
    • A61B5/0535—Impedance plethysmography
    • 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
    • A61B5/242—Detecting biomagnetic fields, e.g. magnetic fields produced by bioelectric currents
    • A61B5/245—Detecting biomagnetic fields, e.g. magnetic fields produced by bioelectric currents specially adapted for magnetoencephalographic [MEG] signals
    • 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
    • A61B5/6813—Specially adapted to be attached to a specific body part
    • A61B5/6814—Head
    • 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
    • A61B5/6813—Specially adapted to be attached to a specific body part
    • A61B5/6814—Head
    • A61B5/6815—Ear
    • A61B5/6817—Ear canal
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B2562/00—Details of sensors; Constructional details of sensor housings or probes; Accessories for sensors
    • A61B2562/16—Details of sensor housings or probes; Details of structural supports for sensors
    • A61B2562/164—Details of sensor housings or probes; Details of structural supports for sensors the sensor is mounted in or on a conformable substrate or carrier

Definitions

  • the field of the invention relates to measuring blood flow in the head.
  • data regarding the quantity of blood flow in the brain, and the changes in flow rate may be important in evaluating the risk of injury to the brain tissue and the efficacy of treatment.
  • the availability of such data may enable the timely performance of various medical procedures to increase, decrease, or stabilize the cerebral blood flow, and prevent permanent damage to the brain.
  • Cerebral blood flow may also be inferred indirectly by monitoring neurological function, but since neurological dysfunction is often irreversible by the time it is detected, it is more desirable to detect changes in cerebral blood flow directly, while its effects on brain function are still reversible.
  • TCD trans-cranial Doppler
  • IPG electric impedance plethysmography
  • PPG photoplethysmography
  • US patent 6,819,950, to Mills describes the use of PPG to detect carotid stenosis, among other conditions.
  • US patent 5,694,939, to Cowings describes biofeedback techniques for controlling blood pressure, which include the use of IPG in the lower leg and PPG in the finger.
  • US patent 5,396,893, to Oberg et al states that PPG is superior to IPG for monitoring patients' cardiac and respiration rates.
  • US patent 6,832,113, to Belalcazar describes the use of either IPG or PPG to measure blood flow, for purposes of optimizing a cardiac pacemaker.
  • US patent 6,169,914, to Hovland et al describes the use of various types of sensors, including IPG and PPG, for monitoring female sexual arousal with a vaginal probe, and describes using different types of sensors in combination.
  • An aspect of some embodiments of the invention relates to estimating cerebral blood flow, by 1) using IPG to obtain a measure of the combined change in cerebral and possibly including scalp blood volume during a cardiac cycle; 2) using PPG or another method, including surface IPG or ultrasonics, to obtain a measure of the change mainly in scalp blood volume; and 3) combining the two measurements to find the change in cerebral blood volume.
  • the cerebral blood flow is then optionally found from the time derivative of the cerebral blood volume. Since there is generally a component of cerebral blood flow that is not associated with varying cerebral blood volume, in addition to a component associated with the variation in cerebral blood volume over a cardiac cycle, using the time derivative of the cerebral blood volume may only give an indication of the relative cerebral blood flow, rather than the absolute cerebral blood flow.
  • the time-varying part of the cerebral blood volume is found by subtracting a weighted or normalized PPG signal from the IPG signal, to obtain a measure that depends primarily on the time-varying part of the cerebral blood volume, with relatively little dependence on the time-varying part of the scalp blood volume.
  • the weighting factor is estimated by using the fact that there is a time delay between the cerebral blood flow and the scalp blood flow, in each cardiac cycle, and assuming that in a later part of each cardiac cycle, for example the last third of each cycle, when the blood pressure is decreasing, the IPG signal is dominated by the time-varying part of the scalp blood volume.
  • the weighting factor is estimated by using the power spectra and cross-power spectrum of the IPG and PPG signals.
  • the cross-power spectrum is used to find a range of frequencies for which the IPG and PPG signals are similar, and the weighting factor is set equal to the square root of the ratio between the power spectrum of the IPG signal integrated over those frequencies, and the power spectrum of the PPG signal integrated over those frequencies.
  • the IPG measurement is made by placing IPG electrode units on two sides of the head, for example on the left and right temples.
  • one or both of the IPG electrode units is combined with a PPG sensor, in a single unit.
  • the IPG electrode units include separate current-carrying and voltage- measuring electrodes.
  • the current-carrying electrode may be in the form of a concentric ring surrounding the voltage-measuring electrode, or vice versa.
  • An aspect of some embodiments of the invention relates to estimating cerebral blood flow by using characteristics of the IPG signal alone.
  • the cerebral blood flow is estimated from the peak value of the IPG signal in each cardiac cycle, or from the peak rate of rise of the IPG signal after the beginning of each cardiac cycle, or from the height of the first local peak or inflection point in the IPG signal after the beginning of each cardiac cycle.
  • the beginning of each cardiac cycle is defined, for example, by the peak of the R- wave of an ECG, or by the time of the minimum in the IPG or PPG signal, or by the time of the diastolic pressure.
  • the rapid initial rate of rise in the IPG signal may be dominated by the cerebral blood flow, even if the IPG signal during the rest of the cardiac cycle is largely influenced by the scalp blood volume, since the scalp blood volume, as indicated by PPG data, generally rises more slowly, and with a delay, at the beginning of each cardiac cycle.
  • PPG data is also obtained, to confirm that the scalp blood volume is rising slowly initially, and that the rapid initial rise of the IPG signal is indeed due mostly to the cerebral blood flow.
  • Some embodiments of the invention may be particularly useful for monitoring premature infants, for example those with weight under 1.5 kg, who generally have poor ability to maintain constant blood flow to the brain due to the immaturity of their cerebral blood flow autoregulation system.
  • Abrupt changes in blood flow to the brain can be caused by changes in respiration, changes in blood pressure, and manipulation of the infants by medical staff.
  • Such abrupt changes in cerebral blood flow if not immediately detected and treated, can cause severe brain injury, including injuries caused by cerebral hemorrhage which occurs in 10% to 30% of premature babies.
  • the invention may also be useful in monitoring mature babies who may be at risk of brain hemorrhage or ischemia for various reasons.
  • the invention may also be useful for monitoring cerebral blood flow in 1) patients undergoing surgery of the carotid arteries, in which a clamp is applied to one of the carotids, potentially reducing blood flow to the brain; 2) patients with stenosis or occlusion of the carotid arteries or cerebral arteries, particularly if they are undergoing procedures such as intra-arterial catherization or stent application in the affected arteries; 3) brain injury patients, in whom brain edema might cause a decrease in blood perfusion, and herniation of the brain; 4) neurosurgery patients, during and for a few days after the surgery, when cerebral blood flow is often impaired; 5) patients undergoing other major surgery, including heart surgery, in which massive bleeding and resulting hypotension could lead to a decrease in cerebral blood flow. In all of these categories of patients, monitoring of cerebral blood flow could lead to prompt intervention before brain injury occurs.
  • An aspect of some embodiments of the invention relates to a probe including both electrical and scalp blood flow measurement sensors.
  • the probe is configured so that when placed at a certain (optionally pre-determined) location on the skull, for example, the temple, the blood flow measurement probe will be aimed at the vascular bed (e.g., source) of the location where electric field will be sensed.
  • the vascular bed e.g., source
  • a method of estimating cerebral blood flow comprising: a) obtaining a measure of time-varying blood volume in the head, using impedance plethysmography; b) obtaining a measure of time-varying blood volume in the scalp; and c) using the measure of time-varying blood volume in the head and time- varying blood volume in the scalp to estimate the cerebral blood flow.
  • obtaining a measure of time-varying blood flow in the scalp comprises using photoplethysmography
  • estimating the cerebral blood flow comprises estimating the relative cerebral blood flow as it changes over time.
  • using the measures of time- varying blood volume comprises finding a difference between weighted measures of time-varying blood volume.
  • the measures of time-varying blood volume are weighted to have at least approximately the same value at a time in the cardiac cycle when the blood pressure is falling.
  • the measures of time-varying blood volume are weighted to have approximately equal power spectra at frequencies for which the cross-power spectrum between the measures of time-varying blood volume is relatively high.
  • obtaining a measure of blood volume in the head using impedance plethysmography comprises: a) passing a current through the head using two current-carrying electrodes; and b) measuring a voltage across the head, associated with the current, using two voltage-measuring electrodes.
  • the method includes applying to the head an annular electrode surrounding at least one of the current-carrying electrodes, and maintaining the annular electrode at a same voltage as the current-carrying electrode it surrounds, thereby suppressing radial current from said current-carrying electrode.
  • the voltage-measuring electrodes are distinct from, and substantially electrically decoupled from, the current-carrying electrodes.
  • obtaining a measure of blood volume in the head using impedance plethysmography comprises placing the two current-carrying electrodes on the left and right temples respectively.
  • obtaining a measure of blood volume in the head using impedance plethysmography comprises placing each of the two voltage -measuring electrodes on the head in a position adjacent to a different one of the current-carrying electrodes.
  • obtaining a measure of blood volume in the scalp using photoplethysmography comprises placing a photoplethysmography sensor on the head adjacent to one of the current-carrying electrodes and to the voltage-measuring electrode which is adjacent to said current-carrying electrode.
  • a method of estimating cerebral blood flow comprising: a) measuring an impedance across the head as a function of time in a cardiac cycle; and b) estimating the cerebral blood flow from a rate of change of the impedance during a time in the cardiac cycle when the blood pressure is rising.
  • a unit for estimating cerebral blood flow adapted for placing on the head, the unit comprising: a) at least one electrode adapted for impedance plethysmography; and b) a plethysmography sensor adapted for measuring blood flow in a scalp.
  • the senor is a photoplethysmography sensor.
  • the unit comprises a signal processor configured to process one or both of data from the photoplethysmography sensor and impedance plethysomography data from the electrode.
  • the at least one electrodes comprise: a) a current-carrying electrode adapted for injecting current through the head when it is placed on the skin; and b) a voltage-measuring electrode adapted for measuring voltage across the head when it is placed on the skin, and when the current-carrying electrode is injecting current.
  • the current-carrying and voltage-measuring electrodes are configured such that the voltage measuring electrode will measure a potential substantially equal to a potential at the dermis, largely excluding the voltage drop across the epidermis, when the current-carrying electrode is injecting current.
  • the unit is adapted for use in patients of a range of degree of maturity, wherein the current-carrying electrode comprises an annulus surrounding the voltage-measuring electrode, and the radial thickness of the annulus and the gap between the current-carrying and voltage- measuring electrodes are each at least twice as great as a typical thickness of the epidermis in patients of said range of degree of maturity.
  • the radial thickness of the annulus and the gap between the current-carrying and voltage-measuring electrodes are each at least lmm.
  • the radial thickness of the annulus and the gap between the current-carrying and voltage-measuring electrodes are each at least 2 mm.
  • the unit includes an annular electrode surrounding the current-carrying electrode, thereby suppressing radial current from the current-carrying electrode when the annular electrode is maintained at the same voltage as the current-carrying electrode.
  • a system for estimating cerebral blood flow comprising: a) at least one unit as described herein; b) an impedance measuring unit comprising at least one electrode adapted for placing on the head and performing impedance plethysmography; c) a power supply adapted for passing current across the head between one of the at least one electrodes of the one unit and one of the at least one electrodes of the impedance measuring unit, when said units are placed on different sides of the head; and d) a data analyzer which calculates a cerebral blood flow using impedance data obtained from a voltage difference measured between one of the at least one electrodes of the one unit and one of the at least one electrodes of the impedance measuring unit, and from photoplethysmography data generated by the photoplethysmography sensor.
  • the impedance measuring unit is also a unit as described herein.
  • Figs. IA, IB and 1C show schematic views, respectively from the side, the back, and the face, of a unit combining IPG electrodes and a PPG sensor, according to an exemplary embodiment of the invention
  • Fig. ID is a schematic view of IPG electrodes according to another exemplary embodiment of the invention
  • Fig. 2 is a schematic perspective view showing placement on the temples of the units shown in Figs. IA- 1C, according to an exemplary embodiment of the invention
  • Fig. 3 is a schematic cut-away view of the head with the units placed on it as in Fig. 2, showing current paths through the scalp and through the brain, produced by the IPG electrodes;
  • Fig. 4 shows a schematic plot of IPG and PPG signals as a function of time, generated by the units placed on the head as in Fig. 2;
  • Fig. 5 shows a schematic plot of the variation in cerebral blood volume as a function of time during two cardiac cycles, derived by taking a difference between the IPG signal and the PPG signal shown in Fig. 4;
  • Fig. 6 shows a schematic plot of IPG and PPG signals as a function of time, similar to the signals shown in Fig. 4, but extending over a longer time interval and measured while the subject is hyperventilating;
  • Fig. 7 shows a schematic plot of an IPG signal as a function of time, illustrating a method of estimating changes in cerebral blood flow according to an exemplary embodiment of the invention
  • Fig. 8 shows a schematic plot of an IPG signal and its time derivative as a function of time, illustrating a method of estimating changes in cerebral blood flow according to another exemplary embodiment of the invention.
  • Figs. IA, IB, and 1C respectively show side, back, and face views of a unit 100 which optionally combines a current electrode 102 and a voltage electrode 104 for impedance plethysmography (IPG), and a sensor 106 for photoplethysmography
  • IPG impedance plethysmography
  • Fig. 1C is the side that is placed against the skin, as shown in Fig. 2.
  • two such units placed for example on opposite sides of the head, are optionally used for IPG, passing current from one unit to the other and measuring the voltage between them.
  • alternating current is generally used.
  • PPG sensor 106 measures the color of the skin to determine a degree of perfusion of oxygenated blood in the skin adjacent to unit 100, as described, for example, by J. Webster, "Measurement of Flow and Volume of Blood,” in John G. Webster (ed.), Medical Instrumentation: Application and Design (Wiley, 1997), the disclosure of which is incorporated herein by reference.
  • PPG sensor 106 incorporates a digital signal processor which converts the raw sensor signal into a usable output signal.
  • unit 100 also includes a digital signal processor which processes voltage and/or current and/or photo reflection data of the electrodes and/or PPG in one or both units.
  • the raw signal from sensor 106 and/or data from the electrodes is processed partly or entirely by an external signal processor not located in unit 100.
  • unit 100 instead of having separate current and voltage electrodes, unit
  • the 100 has a single electrode, used both for carrying current and for measuring voltage.
  • using separate electrodes for carrying current and measuring voltage has the potential advantage that the measured voltage may not be very sensitive to a high contact resistance between the electrodes and the skin, or to a high resistance across the epidermis, one or both of which can dominate the voltage drop between the current electrodes on opposite sides of the head.
  • the contact resistance and the epidermis resistance have little or no dependence on blood flow, so it is generally desirable for the IPG signal not to be sensitive to the contact and epidermis resistance.
  • This goal is optionally achieved by using an annular shape for current-electrode 102, and locating voltage-electrode 104 in the center of the annulus, but substantially electrically decoupled from it.
  • the radial thickness of the annulus of electrode 102, and the gap between electrodes 102 and 104, are optionally at least somewhat greater than the thickness of the epidermis under the electrodes, for example at least twice as great.
  • the radial thickness of the annulus of electrode 102 is at least 2 mm, or at least 5 mm, or at least 1 cm.
  • the gap between electrodes 102 and 104 is at least 2 mm, or at least 5 mm, or at least 1 cm, or intermediate or smaller values.
  • this potential difference depends on the impedance of the dermis of the temples and the scalp, and the impedance of the cranium and the brain, as described below in connection with Fig. 3, rather than on the impedance across the epidermis.
  • FIG. ID An alternative configuration 108 for the voltage and current electrodes is shown in Fig. ID.
  • Current is injected through electrode 110, located in the center, and voltage is measured at electrode 112, in the form of an annulus surrounding electrode 1 10, which is electrically well isolated from electrode 110.
  • An additional electrode 114 also in the form of an annulus, surrounds electrode 112, and injects whatever current is necessary in order to remain at the same voltage as electrode 110.
  • only the current injected through electrode 110 is considered for purposes of finding the impedance.
  • the current from electrode 110 will be directed mostly into the head, and relatively more of this current will flow through the brain as opposed to flowing through the scalp, while most of the current flowing through the scalp will be injected by electrode 114, and may be ignored for purposes of measuring the impedance.
  • the impedance measurement will be more sensitive to the impedance of the brain, and less sensitive to the impedance of the scalp.
  • the thicknesses of electrodes 112 and 114, and the gaps between them and between electrodes 110 and 112 have the same possible dimensions as those mentioned above for electrodes 102 and 104.
  • the current through electrode 114 is also measured, and compared to the current through electrode 110, in order to estimate the ratio of the scalp path impedance to the cerebral path impedance.
  • This ratio may be used to find a weighting factor to be used for the PPG signal when subtracting the PPG signal from the IPG signal, instead of or in addition to the methods described above for finding the weighting factor.
  • any of the electrode configurations described in US patent application 10/893,570 is used, or any other electrode configuration is used in which the current electrode is adjacent to the voltage electrode. If the current electrode has dimensions that are large compared to the thickness of the epidermis, and the voltage electrode is separated from the current electrode by a similar distance, then the voltage electrode will measure a potential that tends to be close to the potential at the dermis under the voltage and current electrodes, largely excluding the voltage drop across the epidermis.
  • Fig. 2 shows a head 200 with units 202 and 204 placed on the temples on each side of the head, according to an exemplary embodiment of the invention.
  • each of units 202 and 204 is like unit 100 in Figs. IA- 1C, including both IPG electrodes and PPG sensors.
  • a power supply 206 passes current between the current- electrodes in units 202 and 204, and a voltage difference is measured between the voltage-electrodes in units 202 and 204, while PPG data is optionally supplied by the PPG sensors in both units.
  • PPG data is optionally supplied by the PPG sensors in both units.
  • a data analyzer 208 uses the voltage difference between the voltage electrodes, together with the PPG data, to estimate the cerebral blood flow, as will be described below in the description of Figs. 4 and 5.
  • a C-shaped spring device 210 connects units 202 and 204, and provides a force to keep units 202 and 204 in place on the temples, similar to headphones.
  • suction cups such as those used for electrocardiographs, are used to keep units 202 and 204 in place on the temples, or any other method known in the art, for example an adhesive, is used to keep units 202 and 204 in place on the temples.
  • units 202 and 204 are placed at other locations on the head, for example on the forehead and in the back of the head.
  • the two electrodes need not be placed on opposite sides of the head, placing them on at least approximately opposite sides of the head has the potential advantage that relatively more current goes through the interior of the skull, rather than through the scalp.
  • Placing the electrodes on the temples has the potential advantage that there is no need to shave the skin before placing the electrodes, and the skull is relatively thin at the temples, also causing relatively more of the current to go through the brain rather than through the scalp.
  • Placing an electrode over one of the closed eyelids, or over the foramen magnum at the base of the skull, or over the ears or inside the ear canal also allows current to get into the interior of the skull relatively efficiently.
  • the units there are more than two such units placed on the head, and, for example, current is passed between different pairs of units while the voltage difference is measured between different pairs of units, not necessarily the same units that current is being passed between.
  • Such an arrangement using impedance imaging algorithms, can provide additional information about the impedance distribution inside the head, but the data analysis is more complicated than with only two electrodes, and the electrodes take longer to place.
  • the units generally use alternating current, for example in the frequency range of a few kilohertz to several tens of kilohertz.
  • Frequencies above about 100 kHz may give impedance data that is less sensitive to blood flow than lower frequencies, since above about 100 kHz the currents can easily flow through the cell membranes, which act like capacitors, and across the interiors of the cells. At frequencies well below 100 kHz, the currents are largely confined to the extra-cellular fluid, and the impedance tends to be more sensitive to blood volume.
  • Fig. 3 shows a cut-away view of head 200, seen from the front, with units 202 and 204 on the two temples, as in Fig. 2.
  • a cross-sectional cut has been made most of the way through the head in Fig. 3, but in order to show the location of units 202 and 204 on the temples, the skin and skull of the temples have been left in place, in front of the cross-sectional cut.
  • Current between the current electrodes in units 202 and 204 can travel on different paths.
  • Scalp 302 has a relatively low resistivity beneath the epidermis, and a large part of the current travels through the scalp, on path 304, going around skull 306, which has a higher resistivity.
  • Interior 308 of the skull also has a relatively low resistivity.
  • the current electrodes are fairly wide, a significant part of the current goes through the skull and across the brain, on path 310, since the part of path 310 that goes through the high resistivity skull is relatively short and has wide cross- section, while path 304 through the lower resistivity scalp is much longer and has a much smaller cross-section.
  • configuration 108 shown in Fig. ID is used, then a relatively larger part of the current from electrode 110 will tend to go on path 310, through the brain, while a relatively larger part of the current from electrode 114 will tend to go on path 304, through the scalp.
  • the impedance R the ratio of voltage to current
  • AR Rs AR B + RB AR S R s + R B R s + R B to first order in AR B and AR 8 .
  • these impedances are mostly resistive at the frequencies typically used, well below 100 kHz, and this is especially true for the variations in the impedances over a cardiac cycle, since they depend on the volume of blood, which is located outside the cell membranes. Higher resistance is associated with a lower volume of blood, so - ⁇ i? B and - ⁇ Z? s are measures respectively of change in cerebral blood volume, and change in blood volume in the scalp.
  • the PPG signal also measures change in blood volume in the scalp, and is approximately a linear function of - AR 5 since the signals are small.
  • the cerebral blood volume varies during a cardiac cycle because the arterial blood flow into the brain is pulsatile, while the venous blood flow out of the brain is approximately uniform in time. There is some blood flow into the brain even at the time of diastolic pressure, and this baseline cerebral blood flow cannot be determined directly by measuring changes in cerebral blood volume. However, since the time- varying component is a significant fraction of the total cerebral blood flow, measuring the change in cerebral blood volume during a cardiac cycle may provide a clinically useful relative measure of cerebral blood flow.
  • Fig. 4 shows an exemplary plot 400 of the IPG signal - AR , labeled 402, shown as a solid curve, and a weighted PPG signal 404, shown as a dashed curve, as a function of time.
  • Signals 402 and 404 are both plotted in arbitrary units, and alternatively signal 404 could be considered the original PPG signal and signal 402 could be weighted, or both signals could be weighted, since only their ratio matters in plot 400.
  • An R-wave from an electrocardiogram, has peaks at times 406.
  • IPG signal 402 and PPG signal 404 both start to rise, as blood flows into the brain and into the scalp, but the rise in the IPG signal starts earlier, and is much more rapid initially, than the rise in the PPG signal. This is believed to be due to the fact that the arteries supplying blood to the brain have a larger diameter, and lower hydrodynamic resistance to blood flow, than the small arteries supplying blood to the scalp. Later in each cardiac cycle, when the blood has had time to flow into the scalp, we expect the IPG signal to be dominated by the blood volume in the scalp.
  • the weighting factor for PPG signal 404 has optionally been chosen so that weighted PPG signal 404 is approximately equal to IPG signal 402 during an interval late in each cardiac cycle, for example during the last third of each cardiac cycle, when the blood pressure and signals 402 and 404 are falling, before the next peak of the R-wave.
  • the weighting factor is chosen by other methods which evaluate, at least approximately, the ratio of current through the cranium to current through the scalp.
  • the weighting factor is set equal to the square root of the ratio of the power spectrum of the IPG signal, integrated over a range of frequencies, to the power spectrum of the PPG signal, integrated over the same range.
  • the range of frequencies is a range within which the PPG signal is similar to the IPG signal, as indicated, for example, by a high cross-power spectrum between the IPG and PPG signals.
  • the range of frequencies is centered at the peak of the cross-power spectrum, and extends to each side of the peak by an amount equal to or proportional to the rms width of the peak of the cross-power spectrum.
  • the range of frequencies is defined to include all frequencies for which the cross-power spectrum is greater than a certain fraction (for example, half) of the geometric mean of the magnitudes of the IPG and PPG power spectra.
  • the two power spectra are weighted within the range of frequencies, for example according to the value of the cross-power spectrum. In this case, the integration over frequency need not be over a limited range of frequencies.
  • Fig. 5 shows a plot 500 of a signal 502 equal to the difference between IPG signal 402 and weighted PPG signal 404, as a function of time.
  • the cerebral blood volume is estimated from the IPG signal alone. This may be justified because there is evidence that early in each cardiac cycle, and even up to the peak in the IPG signal, the time-dependent part of the IPG signal is largely dominated by changes in cerebral blood volume.
  • Fig. 6 shows a plot 600 of an IPG signal 602, plotted as a solid line, and a PPG signal 604, plotted as a dashed line, measured while the subject was voluntarily hyperventilating.
  • the hyperventilation produces large fluctuations in the peak value of the IPG signal from one cardiac cycle to another, and much smaller fluctuations in the peak value of the PPG signal from one cardiac cycle to another. Since the time dependence of the PPG signal is believed to be due almost entirely to changes in the scalp blood volume, the fact that the IPG signal behaves very differently from the PPG signal indicates that the IPG signal is not dominated by the changes in scalp blood volume, but by something else, presumably changes in cerebral blood volume.
  • One method of estimating the time varying part of the cerebral blood volume is just to assume that the change in cerebral blood volume is proportional to the peak value of the IPG signal for each cardiac cycle.
  • Fig. 7 illustrates another method of estimating the changes in cerebral blood volume, again using only the IPG signal.
  • Plot 700 shows an IPG signal 702 as a function of time, for four cardiac cycles.
  • the value of the IPG signal is measured at its first local peak following the minimum (or following the peak in the R-wave, which occurs at about the same time as the minimum in the IPG signal).
  • the value of. the IPG signal is measured at the inflection point. This is true, for example, in the third cardiac cycle shown in plot 700.
  • These values of the IPG signal for each cardiac cycle are indicated by small crosses 704 in plot 700.
  • Using these values of the IPG signal in each cardiac cycle may better reflect the change in cerebral blood volume than using the peak IPG signal in each cardiac cycle. This may be true, for example, because these values occur earlier in each cardiac cycle, when the IPG signal is more dominated by the time-dependent part of the cerebral blood volume, and is less sensitive to the scalp blood volume.
  • Fig. 8 illustrates yet another method of estimating the changes in cerebral blood volume, using only the IPG signal.
  • Plot 800 shows an IPG signal 802 as a function of time, for three cardiac cycles, and a signal 804 proportional to the time derivative of IPG signal 802.
  • the peak of signal 804 i.e. the peak rate of rise of IPG signal 802 is measured in each cardiac cycle, and indicated by small crosses 806 in plot 800.
  • the peak value of signal 804 may be a good indication of the change in cerebral blood volume during that cardiac cycle, perhaps a better indication than the peak value of the IPG signal.
  • the PPG signal is optionally recorded as well, for example to verify that the scalp blood volume is not changing very much early in each cardiac cycle, at the times when the IPG signal is used to estimate the change in cerebral blood volume.
  • two or more of the methods illustrated in Figs. 5-8 are used to estimate the change in cerebral blood volume, for example by taking a weighted average of the change in cerebral blood volume determined by each method. Different methods might work best for different patients who have different medical conditions.
  • a patient is suffering from a condition in which cerebral blood flow is likely to be reduced more than scalp blood flow
  • the changes in scalp blood flow may dominate the IPG signal even early in the cardiac cycle, and it may be best to use the method illustrated in Fig. 5, which makes use of both the PG signal and the PPG signal.
  • cerebral blood flow and scalp blood flow are likely to be reduced at the same time, for example in the case of a patient undergoing cardiac surgery, it may be better or easier to use one of the methods that depends only on the IPG signal.

Abstract

L'invention concerne une méthode destinée à estimer un flux sanguin cérébral et consistant à obtenir une mesure d'un volume sanguin variant dans le temps dans la tête au moyen d'une pléthysmographie par impédance (102 et 104), à obtenir une mesure du volume sanguin variant dans le temps dans le cuir chevelu, et à utiliser la mesure du volume sanguin variant dans le temps dans la tête et le cuir chevelu pour estimer le flux sanguin cérébral.
PCT/IL2005/000632 2002-01-15 2005-06-15 Appareil de surveillance de perfusion cerebrale WO2006011128A1 (fr)

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JP2007520969A JP4904263B2 (ja) 2004-07-15 2005-06-15 脳灌流監視装置
PCT/IL2005/000632 WO2006011128A1 (fr) 2004-07-15 2005-06-15 Appareil de surveillance de perfusion cerebrale
EP05752203A EP1786316B1 (fr) 2004-07-15 2005-06-15 Appareil de surveillance de perfusion cerebrale
CN2005800310897A CN101052344B (zh) 2004-07-15 2005-06-15 脑灌注监测器
US11/572,141 US8187197B2 (en) 2002-01-15 2005-06-15 Cerebral perfusion monitor
DK06701857.2T DK1895902T3 (da) 2005-06-15 2006-01-17 Apparat til overvågning af cerebral perfusion
JP2008516457A JP5225080B2 (ja) 2005-06-15 2006-01-17 脳潅流モニタ
CN200680029920XA CN101242781B (zh) 2005-06-15 2006-01-17 估计脑血流量的方法
AT06701857T ATE447886T1 (de) 2005-06-15 2006-01-17 Gerät zur überwachung der zerebralen perfusion
PCT/IB2006/050174 WO2006134501A1 (fr) 2005-06-15 2006-01-17 Appareil de surveillance de perfusion cerebrale
PT06701857T PT1895902E (pt) 2005-06-15 2006-01-17 Monitor de perfusão cerebral
US11/921,937 US8512253B2 (en) 2002-01-15 2006-01-17 Cerebral perfusion monitor
ES06701857T ES2336137T3 (es) 2005-06-15 2006-01-17 Monitor de perfusion cerebral.
DE602006010378T DE602006010378D1 (de) 2005-06-15 2006-01-17 Gerät zur überwachung der zerebralen perfusion
EP06701857A EP1895902B1 (fr) 2005-06-15 2006-01-17 Appareil de surveillance de perfusion cerebrale
US11/610,553 US8211031B2 (en) 2002-01-15 2006-12-14 Non-invasive intracranial monitor
US13/484,519 US20130109979A1 (en) 2002-01-15 2012-05-31 Non-invasive intracranial monitor
US13/941,587 US20140163404A1 (en) 2002-01-15 2013-07-15 Cerebral Perfusion Monitor

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DE602006010378D1 (de) 2009-12-24
CN101242781B (zh) 2010-09-29
PT1895902E (pt) 2010-01-28
WO2006011128A8 (fr) 2006-04-06
US20080275352A1 (en) 2008-11-06
US8512253B2 (en) 2013-08-20
DK1895902T3 (da) 2010-03-15
US20090227881A1 (en) 2009-09-10
US20140163404A1 (en) 2014-06-12
ATE447886T1 (de) 2009-11-15
JP4904263B2 (ja) 2012-03-28
JP2008546438A (ja) 2008-12-25
CN101242781A (zh) 2008-08-13
JP5225080B2 (ja) 2013-07-03
US8187197B2 (en) 2012-05-29
ES2336137T3 (es) 2010-04-08

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