WO2007054700A1 - Mesure du spectre de frequence de l'impedance electrique - Google Patents

Mesure du spectre de frequence de l'impedance electrique Download PDF

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Publication number
WO2007054700A1
WO2007054700A1 PCT/GB2006/004185 GB2006004185W WO2007054700A1 WO 2007054700 A1 WO2007054700 A1 WO 2007054700A1 GB 2006004185 W GB2006004185 W GB 2006004185W WO 2007054700 A1 WO2007054700 A1 WO 2007054700A1
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WO
WIPO (PCT)
Prior art keywords
sample
output
transfer function
digital
analogue
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PCT/GB2006/004185
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English (en)
Inventor
Shady Didier Gawad
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University Of Southampton
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Publication of WO2007054700A1 publication Critical patent/WO2007054700A1/fr

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    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
    • G01R27/00—Arrangements for measuring resistance, reactance, impedance, or electric characteristics derived therefrom
    • G01R27/02—Measuring real or complex resistance, reactance, impedance, or other two-pole characteristics derived therefrom, e.g. time constant
    • G01R27/26—Measuring inductance or capacitance; Measuring quality factor, e.g. by using the resonance method; Measuring loss factor; Measuring dielectric constants ; Measuring impedance or related variables

Definitions

  • This invention relates to methods and apparatus for measuring the electrical impedance frequency spectrum of devices or samples, etc.
  • the invention relates particularly, but not exclusively, to methods and apparatus for measuring the electrical impedance spectrum of a device or array of devices, such as an electric component, electric network, material or sample when dry or in a liquid, preferably with provision for recording the impedance frequency spectrum as a function of time. Electrical signals applied to the object being inspected may be subject to a compensation transfer function.
  • sample' has been used herein to refer where appropriate to any such device, array of devices, material/s, sample, tissue, organ or biological entity, or combination thereof, in vitro or in vivo, being measured.
  • a method for measuring the AC electrical parameters of a sample comprising generating a pseudo random binary sequence and using the sequence to control a voltage or current electrical signal applied to the sample, using a digital to analogue converter (D/ A) or equivalent, or the digital signal itself, measuring the response of the sample to said electrical signal by subjecting the output from the sample to an analogue to digital converter (AfO) or equivalent, and processing the output of the A/D with a Hadamard Transform in conjunction with a Fast Fourier Transform (FFT) to produce a measurement of the complex impedance frequency response of the sample.
  • D/ A digital to analogue converter
  • AfO an analogue to digital converter
  • FFT Fast Fourier Transform
  • the pseudo random binary sequence is modified by a compensation transfer function before being applied to the sample, the compensation transfer function having been configured to compensate for at least some unwanted response component of the sample under test.
  • the apparatus comprising a generator for generating a pseudo random binary sequence, a digital to analogue [OIA) unit or equivalent, or other means to output the sequence in digital or analogue format, first connection means for connecting the output of the generator to the input of the D/A, sample input connection means adapted to apply the output of the D/A to the sample, sample output connection means for connecting a sample output to an analogue to digital converter (A/D) or equivalent, and an output processing unit being configured for subjecting the output of the A/D to a Hadamard Transform followed by a Fast Fourier Transform (FFT) for producing in use a measurement of the complex impedance frequency response of the sample.
  • a generator for generating a pseudo random binary sequence
  • a digital to analogue [OIA) unit or equivalent or other means to output the sequence in digital or analogue format
  • first connection means for connecting the output of the generator to the input of the D/A
  • sample input connection means adapted to apply the output of the D/A to the sample
  • Embodiments of the present invention relate to the acquisition of the impedance frequency spectrum (calculated from the measured transfer function) of a system in a very short time, typically 1 microsecond to 5 seconds. Such a method is faster than traditionally used sweep frequency techniques because the signal used to interrogate the system has a broad spectrum, thus interrogating the system simultaneously over the complete spectrum of interest.
  • the signal can be processed with minimal time delay.
  • the signal applied to the system is subject to compensation to cancel noise from other non-correlated noise sources.
  • the signal processing uses a Hadamard Transform to compute the impulse response of the system.
  • the compensation will generally comprise both amplitude and phase compensation applied to the signal prior to its use to interrogate the system. This is done using a transfer function on the signal so configured as to compensate a posteriori (with previous knowledge) for some or all, measured, known or chosen properties of the system spectrum or for parasitic effects.
  • the device or system being measured is an electric component, an electric network or circuit, a material organic or inorganic, a biological tissue, organ or part of the human body in vivo or in vitro, biological cell or cells or other particles, biological particles or powders, dry or wet, in liquid, gas, or vacuum.
  • the device or system is connected to the instrument through wires and contacts or electrodes, preferably microelectrodes.
  • the electrical impedance of these contacts, electrodes or wires can affect the measured impedance over a wide spectrum.
  • the transfer function can then be configured on the basis of the measurements made in the setting up procedure and/or on the basis of knowledge of the system being tested to compensate for these artef actual or parasitic effects such as, but not limited to, electrode polarization and can thereby improve the sensitivity of the measurement.
  • the coherent demodulator does not use knowledge of the applied sequence to suppress noise from uncorrelated noise all over the spectrum.
  • the uncompensated technique which has an associated low dynamic range is also not suitable if the measurement has to be carried over a few decades in frequency simultaneously on systems which comprise a frequency dependent equivalent impedance element (such as a capacitor like element) .
  • Figure Ia is a block diagram showing, in the upper part thereof, apparatus for providing a compensated MLS signal to a D/A connected to the system to be measured, and an A/D connected to the system output to provide a digitised output, and in the lower part thereof output signal processing means for providing a complex spectrum response.
  • an impedance calculation unit is shown for providing compensation to control the compensation transfer function
  • Figure Ib shows the detail of the measured system in Figure Ia for the typical case of two electrodes used to measure a liquid including particles in suspension or some contaminants
  • Figure 2 shows a system for differential measurement which can be used with two or more electrodes associated with the sample under test
  • Figure 3 shows a system for multiple measurements in a multiple input, multiple output system
  • Figure 4 shows in the upper half a system suitable for an array, and in the lower half a modification to that system suitable, inter alia, for impedance tomography,
  • Figure 5 shows schematically an application of the invention to impedance flow cytometry
  • Figure 6 shows a spectrogram of a time varying system measured using the apparatus of Figure 5 ,
  • Figure 7 schematically shows application of the invention to a cell positioned on top of one of the electrodes
  • Figure 8 shows measurements being made of a cell located over a hole with electrodes placed on each side of the hole
  • Figures 9 and 10 show the application of the invention to the measurement of monolayers which may contain membrane proteins.
  • a binary maximum length sequence MLS is generated in unit 1 using a circular shift register of order n.
  • Unit 2 is an optional unit arranged to convert the binary sequence produced by 1 to a bipolar sequence replacing all zeros of the original sequence by ones and all ones by minus 1. Use of a bipolar sequence is preferred so as to reduce the signal offset.
  • the bipolar or binary sequence is passed in normal use through a filter 3 which is preferably a digital filter of the (finite impulse response) FIR type acting as a compensation transfer function, Bypass switches are provided to enable unit 3 to be bypassed so as to generate, when required, a flat signal spectrum in the cases when the response spectrum of the sample is relatively flat or when knowledge of an unknown system is being acquired.
  • the signal is converted to an electric signal using a digital to analogue (D/A) converter 4.
  • the clock frequency of the conversion performed by D/A 4 determines the frequencies at which the system is measured.
  • the amplitude of the analogue signal can be additionally controlled at this stage.
  • the signal from the output of the D/ A 4 is passed through the system 5 to be measured.
  • the systems include all wires and connection to the device of interest.
  • Figure Ib shows the electrodes used to measure the spectrum response of a liquid including particles.
  • the system can be a time variant system.
  • An optional signal amplification stage 6 can be used to adapt the output response of system 5 for the subsequent digitalization.
  • the response is digitized by A/D 7 in order to be further processed.
  • module 8 the digitized response from the output of A/D 7 is processed using a Fast-M-Transform (FMT) which comprises a Hadamard
  • the impulse response of the system is processed using a
  • FFT 9 to obtain the complex spectrum response of the system.
  • the complex spectrum response is converted in block 10 to the impedance spectrum of the system.
  • the filter parameters for the compensation transfer function 3 can be calculated in a setting up procedure in which the bypass to unit 3 is employed.
  • a time averaging filter can be used at this stage to suppress slow variation of offset in the impedance spectrum if one wants to recover the variance in time of the system.
  • the measurements in Figure Ia use a Pseudo-Random Binary Sequence (PRBS) generated in unit 1, preferably a Maximum Length Sequence (MLS) which can be logically generated using an implementation of a shift register or by software [4] .
  • PRBS Pseudo-Random Binary Sequence
  • MLS Maximum Length Sequence
  • the order of the shift register is typically between 4 and 16.
  • the length of the sequence is thus typically between 15 and 65535.
  • the logical binary sequence is preferably converted to a numerical bipolar sequence of selected amplitude.
  • the sequence is then converted to a voltage or current electrical signal using the digital-to-analogue D/A converter 4 and applied to the device 5, material or sample using one, two or more excitation contacts or electrodes as will be described hereafter. A number of contact or electrodes are used to obtain the response from the system.
  • the logical signal can also be applied to the device 5 using an operational amplifier circuit, or a transistor, which produces an analogue signal with the same pattern and frequency as the digital signal but with a defined selectable amplitude and offset.
  • the power spectrum of the generated signal is flat up to the Nyquist frequency (which is half the frequency of the clock frequency used in the D/A converter) .
  • the Hadamard transform of unit 8 is used to compute the impulse response from the system response. Its computation is further described by people knowledgeable in room acoustic measurements [5] .
  • the invention is concerned with compensating at least in part for the impedance spectrum of the system being measured ( Figure Ia) .
  • This compensation uses a transfer function which is applied to the binary sequence or a derived sequence to compensate for a frequency dependent behaviour of the measured system, measuring electronics, contacts or contacts leads. It was found advantageous to place this compensation before the system so as to modify the signal being applied and obtain significant signal amplitude for frequencies where the system impedance is large, rather than applying a signal having a flat frequency spectrum, and then trying to compensate for small response amplitude of the system at certain frequencies.
  • the generated bipolar numerical sequence or a derived sequence can be passed through a transfer function which compensates a posteriori for certain measured or known electrical parameters or transfer function of the device, material or sample.
  • the compensation can be bypassed when required to measure the uncompensated system.
  • the waveform generated using the digital-to-analogue converter no longer has a flat power spectrum.
  • the transfer function can be made to compensate for the frequency behaviour of the electrical double layer polarization which usually takes the form of a capacitor or a constant phase element.
  • the interfacial impedance generated by the double layer can be very large at low frequencies compared with the rest of the system and thus can screen the measurement at those frequencies.
  • Compensating for such an interfacial impedance in series with some resistive elements of interest can be done by using a transfer function which proportionally increases the voltage of the low frequency components of the sequence. In the case of a bipolar voltage applied to a device material or sample using two electrodes, this compensates for the smaller signal amplitude measured at the lower end of the frequency spectrum where the voltage drop through the series resistive elements is small compared to the voltage drop through the interfacial capacitance .
  • the compensation transfer function can also compensate for, but not limited to, parasitic stray capacitors, series resistors or other electrical elements either in parallel or series with or inherent to the device, material or sample being measured. These parasitic effects can have an influence on a part or the whole measured spectrum, the compensation transfer function can thus be used to compensate for those effects by modifying the spectrum of the applied sequence so as to cancel their effect on the measured spectrum.
  • a linear, square or logarithmic, or other non-linear amplification stage can be used to scale the output amplitude of the digital-to-analogue converter.
  • the uncompensated measured spectrum can be used to select the parameters of the compensation transfer functions, or be used directly for measurement when the spectrum over the frequency range of interest is found to be relatively flat.
  • the compensation transfer function can also be used to compensate for distortions in the spectrum introduced by an analog-to-digital or a digital- to-analogue converter, by analogue filters, or by one or more signal amplification stages. Any unwanted frequency dependent or independent phase effect can also be compensated by the transfer function. Interface to the device and differential measurement
  • a set of one, two or more electrodes can be used to make electrical contact to the device, material or sample being measured.
  • a differential measurement using a second set of one, two or more electrodes applied to a different part of the same or to a different reference device, material or sample can be used simultaneously or at a different time.
  • the user In prior art instruments (typically called impedance analyzers) the user generally chooses a fixed voltage which is applied throughout the whole frequency sweep of the spectrum. If the equivalent of a frequency-dependent impedance element is present in the measured system, the measured response amplitude, in this case a current, can vary over the frequency spectrum by many order of magnitude. This consequently requires adapting the gain of the amplification stage of the instruments as a function of the measured frequency range in order to avoid saturation or achieve a required resolution.
  • Modifying the synthesized flat broad spectrum sequence being generated to compensate for the system measured or known transfer function using the compensation transfer function enables selected parts of the applied spectrum to be changed up or down in magnitude or phase.
  • This compensation method does amongst other advantages suppress the need to adapt the amplification stage gain as a function of frequency and thus enables to simplify its embodiment as an instrument compared to prior art, while offering a good dynamic range over the measured spectrum.
  • the compensation transfer function can be adapted in real-time by a computer, a DSP or other means to compensate for drift in the system, such as changes in the interface between electrodes and liquid.
  • This compensation transfer function can be a Finite Impulse Response (FIR) filter with delays and gains as tunable parameters.
  • FIR Finite Impulse Response
  • IIR Infinite Impulse response
  • a compensation transfer function assembly comprises two functions 1 and 2.
  • Compensation transfer function 1 is used in the reference branch of the differential measurement. It can be adapted in real-time by the computer to compensate for common effects found in the two branches.
  • Compensation transfer function 2 is used in the measured branch of the differential measurement and can compensate for differences between the measured branch and the reference branch.
  • the system of Figure 2 may contain additional differentially measured branches according to the system to be measured.
  • the compensation transfer functions 1 and 2 of unit 1 can be adapted in real-time by a computer, a DSP or other means to compensate for drift in the system, such as changes in the interface between electrodes and liquid, common mode and differences between the different branches.
  • the sequences for the reference and measured branches are passed through separate digital-to-analogue converters 12, and the signals are applied to the same system 13 or to a related system.
  • the signals output from the system 13 are differentially amplified by amplifier 14 or somehow compared to the reference.
  • the differential response of the system is converted by A/D 15 to a digital response and post processed.
  • the sequence can be passed through two or more separate transfer functions to compensate for common mode and differences in the different elements of the system.
  • Compensation transfer functions of compensation transfer unit 16 1 to n are used for each individual branch of an array type of measurement. They can be adapted in real-time by a computer, a DSP or other to compensate for common mode and differences between the n different branches.
  • the signals for the different branches are converted through separate digital-analogue converters 17.
  • the system 18 being measured can be an array of samples or a single sample measured with multiple electrodes.
  • the multiple responses are optionally amplified individually by amplifiers 19.
  • the multiple responses of the system or systems are converted to a number of digital responses by A/D'S 20 and post processed using a computer or DSP,
  • the response from each element can be amplified, digitized and processed as individual channels. This can be considered a multiple input multiple output system.
  • a single channel can be used instead in the amplification with time multiplexing if the different elements of the array need not be measured simultaneously.
  • This can be considered a multiplexed input - demultiplexed output system. In this case it is still possible to apply differential compensation for each measurement by changing the filter transfer function synchronously with the time multiplexing for each element.
  • compensation transfer function 21 is used to compensate for common mode or can be related to the electrode role.
  • the sequence is passed through a single digital to analogue converter 22.
  • the system 23 being measured can be an array of samples sharing a common contact or electrode or with one or more contact or electrodes connected to the same sequence, or as shown in the lower part of Figure 4, the system 23 bis being measured can also be connected using contacts or electrodes whose respective role (excitation or measurement) can be exchanged in time. In the case illustrated in the modification of 23 bis there is one excitation contact or electrode and multiple measurement contact or electrodes.
  • the response signals are optionally amplified by amplifiers 24.
  • the multiple responses of the system or systems are converted to a number of digital responses by A/Ds 25 and post processed using a computer or DSP.
  • the same signal can be applied to all the sensors simultaneously.
  • Using multiple detection channels allows for simultaneous recording of the impedance in the sensor but multiplexing can also be used.
  • the sequence is applied to 1 electrode the other electrodes are used to measure the different responses of the system the respective role of the electrodes can be changed in time so as to apply the sequence to the system using a different electrode and measure the response from all others.
  • a different compensation can be used each time the role of the electrodes is exchanged.
  • Uncompensated or partly compensated measurement of the impedance or differential impedance of the device, material or sample can be used to gain knowledge of the compensation transfer function. For instance, if the inverse transfer function of a measured system (with the digital filter disabled) is then used in the compensation, the measured spectrum of the system will be made flat, provided the system is time invariant.
  • the transfer function parameters can also be adapted in real time through a feed-back loop to follow changes in the measured spectrum. This is typically done by using a time average filter on the measured spectrum with a time constant which is long compared to the change in frequency spectrum which is being monitored. This permits to adjust the parameters of the compensation transfer function while it is active by compensating for relatively long term change to the system impedance. Provisions are made to record the transfer function used in the digital filter compensation as it contains the slowly changing or time invariant properties of the device, material, sample as well as contact and wire information.
  • the sequence can be applied between two excitation electrodes either by applying the sequence to one electrode and keeping a fixed potential the other or by applying the sequence to one electrode and the phase opposed signal to the other.
  • Two or more measurement electrodes are used to obtain the voltage drop between two or more points of the device, material or sample.
  • the sequence is applied to one or more electrodes and one or more measurement electrodes are connected to a virtual ground.
  • the current passing through the virtual ground is measured for each measurement electrode and is subsequently converted to a voltage using a trans-impedance amplification stage or by measuring the voltage drop across a resistor placed in series with the sample.
  • the role of the electrodes can optionally be changed rapidly which enables performing fast time resolved impedance tomography.
  • the compensation can be changed synchronously with the change of the roles of the electrode so that each possible electrode role configuration can use a different compensation.
  • the measured response is optionally amplified electronically. In certain configuration it can be amplified differentially.
  • analogue to digital converter clocked synchronously to the digital to analogue converter at the same frequency, or at a divider of two of the digital to analogue converter frequency.
  • the rest of the processing can be done using any type of computing means, a computer, a digital signal processor (DSP) or an integrated circuit.
  • the digitized response data is organized into successive time frames comprising 1 digitized response samples. Each of those response frames corresponds in time to a generated sequence. This is possible as the converters work synchronously.
  • the digitized response is transformed into the impulse response of the device, material or sample using a Fast M Transform (FMT) comprising a Hadamard Transform or Fast Hadamard Transform (FHT) .
  • FMT Fast M Transform
  • FHT Fast Hadamard Transform
  • the FMT computation involves only a fraction of the FFT computation.
  • the impulse response is optionally padded with a zero before being • transformed into the complex frequency response using a Fast Fourier Transform.
  • time averaging can be performed if one is interested in changes in the measured spectrum, thus removing low frequency drifts and offsets in the measured spectrum.
  • FIG. 6 A typical example is found in impedance spectroscopy flow cytometry [6- 9] Figure 5 where the user is primarily interested in the rapid changes to the system due to the cell passing, and other time independent or slowly time dependent information are only secondary.
  • a spectrogram of a time varying system measured using the disclosed method is shown in Figure 6. In this case, a differential complex spectrum is measured for 512 different frequencies every millisecond. Only the real part of the spectrogram is shown, it is additionally corrected for offset using time averaging.
  • the system comprises particles passing in a capillary channel between a specific electrode arrangement according to the literature [6, 7] .
  • Knowledge on the dielectric properties of passing particles or cells can be retrieved by looking at the change in time of the measured spectrum. Additional processing such as time and spectrum filtering can be used. Single cell parameters extraction can be done using spectrum fitting algorithm or by matching the measured data to previously acquired data.
  • cell as the sample are by no mean limited to but include measurement of cell on a surface or on top of one of the electrodes Figure 7.
  • Knowledge of the device, material or sample can be retrieved as a complex impedance spectrum using the complex frequency response of the system and the applied signal spectrum.

Abstract

La présente invention concerne un appareil qui permet de mesurer les paramètres électriques du courant alternatif d'un échantillon, tel qu'un élément électrique, un réseau électrique, un matériau à l'état sec ou sous forme liquide, ledit appareil comprenant un générateur qui génère une séquence binaire pseudo-aléatoire, une unité numérique-analogique (N/A) ou similaire ou d'autres moyens de production de la séquence dans un format numérique ou analogique, un premier moyen de connexion qui sert à connecter la sortie du générateur à l'entrée de l'unité N/A, un moyen de connexion de l'entrée de l'échantillon prévu pour appliquer la sortie de l'unité N/A à l'échantillon, un moyen de connexion de la sortie de l'échantillon servant à connecter une sortie d'échantillon à un convertisseur analogique-numérique (A/N) ou similaire et une unité de traitement de la sortie qui est configurée pour soumettre la sortie du convertisseur A/N à une transformée d'Hadamard puis à une transformée de Fourier rapide (TFR) pour produire, en utilisation, une mesure de la réponse en fréquence de l'impédance complexe de l'échantillon. L'appareil selon l'invention peut effectuer l'acquisition du spectre de fréquence de l'impédance (calculé à partir de la fonction de transfert mesurée) d'un système en un temps très court, qui est généralement de l'ordre de 1 microseconde à 5 secondes.
PCT/GB2006/004185 2005-11-10 2006-11-09 Mesure du spectre de frequence de l'impedance electrique WO2007054700A1 (fr)

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GB0522888A GB0522888D0 (en) 2005-11-10 2005-11-10 Measurement of the electrical impedance frequency spectrum
GB0522888.7 2005-11-10

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EP2565654A2 (fr) 2011-08-30 2013-03-06 Tallinn University of Technology Procédé et dispositif d'analyse à large bande des systèmes et substances
EP2717063A1 (fr) * 2012-10-04 2014-04-09 Bender GmbH & Co. KG Procédé de surveillance et de mesure d'une résistance d'isolation à l'aide d'un signal de mesure résistant au brouillage
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US8838395B2 (en) 2010-09-09 2014-09-16 S.E.A. Medical Systems, Inc. Systems and methods for intravenous drug management using immittance spectroscopy
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US9317055B2 (en) 2011-10-24 2016-04-19 Honda Motor Co., Ltd. Method for sequentially measuring impedance, measurement device, and fuel cell system
US20170071552A1 (en) * 2015-09-14 2017-03-16 Stichting Imec Nederland Bio-Impedance Spectroscopy System and Method for Bio-Impedance Measurement

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Cited By (12)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US8728025B2 (en) 2008-03-10 2014-05-20 S.E.A. Medical Systems, Inc. Intravenous fluid monitoring
US9014775B2 (en) 2008-03-10 2015-04-21 S.E.A. Medical Systems, Inc. Multi-parametric fluid determination systems using complex admittance
US9173600B2 (en) 2009-03-09 2015-11-03 S.E.A. Medical Systems, Inc. Systems and methods for the identification of compounds in medical fluids using admittance spectroscopy
US9052276B2 (en) 2009-06-08 2015-06-09 S.E.A. Medical Systems, Inc. Systems and methods for the identification of compounds using admittance spectroscopy
US8838395B2 (en) 2010-09-09 2014-09-16 S.E.A. Medical Systems, Inc. Systems and methods for intravenous drug management using immittance spectroscopy
EP2565654A2 (fr) 2011-08-30 2013-03-06 Tallinn University of Technology Procédé et dispositif d'analyse à large bande des systèmes et substances
US10698023B2 (en) 2011-08-30 2020-06-30 Tallinn University Of Technology Method and device for broadband analysis of systems and substances
US9317055B2 (en) 2011-10-24 2016-04-19 Honda Motor Co., Ltd. Method for sequentially measuring impedance, measurement device, and fuel cell system
EP2717063A1 (fr) * 2012-10-04 2014-04-09 Bender GmbH & Co. KG Procédé de surveillance et de mesure d'une résistance d'isolation à l'aide d'un signal de mesure résistant au brouillage
US9632131B2 (en) 2012-10-04 2017-04-25 Bender Gmbh & Co. Kg Method for monitoring and measuring an insulation resistance with interference-resistant measuring signal
US20170071552A1 (en) * 2015-09-14 2017-03-16 Stichting Imec Nederland Bio-Impedance Spectroscopy System and Method for Bio-Impedance Measurement
US11096629B2 (en) * 2015-09-14 2021-08-24 Stichting Imec Nederland Bio-impedance spectroscopy system and method for bio-impedance measurement

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