WO2016161484A2 - Electrode to nerve distance estimation - Google Patents
Electrode to nerve distance estimation Download PDFInfo
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- WO2016161484A2 WO2016161484A2 PCT/AU2016/050263 AU2016050263W WO2016161484A2 WO 2016161484 A2 WO2016161484 A2 WO 2016161484A2 AU 2016050263 W AU2016050263 W AU 2016050263W WO 2016161484 A2 WO2016161484 A2 WO 2016161484A2
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/18—Applying electric currents by contact electrodes
- A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
- A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
- A61N1/3605—Implantable neurostimulators for stimulating central or peripheral nerve system
- A61N1/3606—Implantable neurostimulators for stimulating central or peripheral nerve system adapted for a particular treatment
- A61N1/36062—Spinal stimulation
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/18—Applying electric currents by contact electrodes
- A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
- A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
- A61N1/3605—Implantable neurostimulators for stimulating central or peripheral nerve system
- A61N1/3606—Implantable neurostimulators for stimulating central or peripheral nerve system adapted for a particular treatment
- A61N1/36067—Movement disorders, e.g. tremor or Parkinson disease
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/18—Applying electric currents by contact electrodes
- A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
- A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
- A61N1/3605—Implantable neurostimulators for stimulating central or peripheral nerve system
- A61N1/36128—Control systems
- A61N1/36135—Control systems using physiological parameters
- A61N1/36139—Control systems using physiological parameters with automatic adjustment
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/18—Applying electric currents by contact electrodes
- A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
- A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
- A61N1/3605—Implantable neurostimulators for stimulating central or peripheral nerve system
- A61N1/3606—Implantable neurostimulators for stimulating central or peripheral nerve system adapted for a particular treatment
- A61N1/36071—Pain
- A61N1/36075—Headache or migraine
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/18—Applying electric currents by contact electrodes
- A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
- A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
- A61N1/3605—Implantable neurostimulators for stimulating central or peripheral nerve system
- A61N1/36128—Control systems
- A61N1/36146—Control systems specified by the stimulation parameters
- A61N1/36182—Direction of the electrical field, e.g. with sleeve around stimulating electrode
- A61N1/36185—Selection of the electrode configuration
Definitions
- a neuromodulation system applies an electrical pulse to tissue in order to generate a therapeutic effect.
- the electrical pulse is applied to the dorsal column (DC) of the spinal cord.
- DC dorsal column
- Such a system typically comprises an implanted electrical pulse generator, and a power source such as a battery that may be rechargeable by transcutaneous inductive transfer.
- An electrode array is connected to the pulse generator, and is positioned in the dorsal epidural space above the dorsal column.
- An electrical pulse applied to the dorsal column by an electrode causes the depolarisation of neurons, and generation of propagating action potentials.
- the fibres being stimulated in this way inhibit the transmission of pain from that segment in the spinal cord to the brain.
- stimuli are applied substantially continuously, for example at 100 Hz.
- Neuromodulation may also be used to stimulate efferent fibres, for example to induce motor functions.
- the electrical stimulus generated in a neuromodulation system triggers a neural action potential which then has either an inhibitory or excitatory effect.
- Inhibitory effects can be used to modulate an undesired process such as the transmission of pain, or to cause a desired effect such as the contraction of a muscle.
- a stimulus is of an amplitude and/or peak width and/or has other parameter settings which put it below the recruitment threshold, delivery of such a stimulus will fail to recruit any neural response.
- it is necessary to maintain stimuli amplitude or delivered charge above the recruitment threshold. It is also necessary to apply stimuli which are below a comfort threshold, above which uncomfortable or painful percepts arise due to increasing recruitment of ⁇ fibres which are thinly myelinated sensory nerve fibres associated with joint position, cold and pressure sensation.
- the stimulus waveforms employed can recruit action potentials on other classes of fibres which cause unwanted side effects, such as muscle contraction if motor fibres are recruited.
- the task of maintaining appropriate stimulus amplitude is made more difficult by electrode migration and/or postural changes of the implant recipient, either of which can significantly alter the neural recruitment arising from a given stimulus, depending on whether the stimulus is applied before or after the change in electrode position or user posture. Postural changes alone can cause a comfortable and effective stimulus regime to become either ineffectual or painful.
- the present invention provides a method of estimating a nerve-to-electrode distance, the method comprising:
- the present invention provides an implantable device for estimating a nerve-to-electrode distance, the device comprising:
- At least one stimulus electrode and at least one sense electrode at least one stimulus electrode and at least one sense electrode
- a processor configured to apply from the or each stimulus electrode to a nerve at least one stimulus having defined stimulus parameters, obtain from the measurement circuitry a plurality of neural measurements of at least one compound action potential evoked by the at least one stimulus, process the plurality of neural measurements in order to estimate an originating state of stimulation, the originating state of stimulation exhibiting at least one observable characteristic defined by a single fibre size; and apply a single fibre model to the estimated originating state of stimulation and the stimulus parameters, in order to produce a measure of the nerve-to-electrode distance.
- the originating state of stimulation may be considered as a threshold condition of stimulation, at which a single fibre or a single fibre size dominates or defines the nature of the evoked neural response.
- the present invention recognises that by estimating the originating state of stimulation, it is possible to isolate at least one characteristic which is defined by a single fibre size. Knowledge of an evoked characteristic which is defined solely or largely by a single size of neural fibre in turn enables a single fibre model of recruitment to be applied, in order to estimate the nerve-to-electrode distance.
- the present invention thus operates to eliminate complicating effects arising from propagation of a compound action potential along a group of neural fibres of distinct size.
- Any suitable single fibre model may be applied to the originating state of stimulation in order to produce the measure of nerve-to-electrode distance.
- the single fibre model may comprise a lookup table matching the observed characteristic and the stimulus parameters to a corresponding nerve-to-electrode distance.
- the measure of the nerve-to electrode distance may comprise an absolute measure of distance, or a relative measure reflecting a change in distance from a previous time, or a measure of a rate of change of distance.
- the method may comprise the further step of adjusting a therapeutic stimulus regime in response to an observed change in the nerve-to- electrode distance.
- the method may be performed intra- operatively, as part of a surgical procedure, for example to progressively monitor a position of a structure bearing the electrodes relative to the nerve.
- the method may be conducted as part of a postoperative fitting procedure of a neurostimulator.
- the originating state of stimulation may comprise an estimate of the ECAP peak width at the stimulus site.
- the applying comprises applying a single stimulus in order to evoke a single ECAP, and the plurality of neural measurements are obtained from at least two sense electrodes each at a unique distance away from the stimulus electrode.
- an ECAP comprises a compound response made up of contemporaneous action potentials evoked on a plurality of individual nerve fibres, and that each nerve fibre exhibits a conduction velocity which depends at least partly on the diameter of that fibre, so that the ECAP peak width widens at an approximately linear rate as each individual action potential propagates away from the stimulus site at a unique velocity.
- Such embodiments preferably estimate an originating ECAP peak width by extrapolating the first and second ECAP measures back to the stimulus site, given that a distance from the stimulus electrode to the first and second sense electrodes is known.
- the originating ECAP peak width can be assumed to be dominated by that single fibre recruited at the stimulus site which had the broadest action potential peak width, typically comprising the recruited fibre of largest diameter as larger fibers are more excitable than smaller diameter fibers.
- the nerve-to-electrode distance can in turn be estimated from the originating ECAP peak width because of the dependence of originating ECAP dispersion upon the fibre to electrode distance.
- Such embodiments which estimate the originating ECAP peak width or dispersion, may be particularly suitable in applications where the stimulus and sense electrodes are well aligned alongside a neural pathway, such as in the case of SCS.
- the measure of ECAP peak width may comprise a half-height peak width, being a measure of a width of an ECAP peak as observed at an amplitude which is half the amplitude of the peak amplitude of the observed ECAP peak.
- the measure of ECAP peak width may comprise a time between the Nl and PI peaks of the observed response, and/or a time between the PI and P2 peaks.
- the measure of ECAP peak width may comprise a time between a zero crossing preceding the Nl peak and a zero crossing following the Nl peak.
- the ECAP peak width may be measured or assessed by extracting frequency components of the neural measurements, for instance fast Fourier transform.
- the neural measurements are first windowed to exclude discontinuities or like stimulus effects and/or measurement effects.
- the frequency domain information of the respective neural measurements may then be used to extract a measure of the dispersion.
- a profile of the frequency domain spectrum of the neural measurements may be assessed for a roll-off or decay with frequency, whereby a faster roll-off of higher frequency components reflects a more dispersed ECAP peak, that is, a peak which is more dominated by lower frequency components.
- a slope or rate of decay of the frequency roll-off may then be determined for each neural measurement, and used to estimate an originating state of stimulation namely the frequency roll-off present in the evoked response at the site of stimulation.
- Such embodiments may be advantageous in measuring dispersion in noisy neural measurements, as a frequency roll-off can be averaged or fitted over a relatively wide spectral range.
- Such embodiments may further be advantageous in enabling a measure of dispersion to be obtained without reliance on the amplitude of the ECAP, for example in embodiments where manual user feedback or automated feedback operates to control recruitment at a substantially constant level.
- the measure of ECAP peak width may comprise a function of one or more such measures, or may comprise any measure which reflects dispersion of the ECAP over time.
- neural measurements may be obtained of both orthodromic and antidromic ECAPs, to permit an averaged or more robust estimate of the originating state of stimulation, and thus of the nerve-to-electrode distance estimate, to be obtained.
- the originating state of stimulation may in some embodiments comprise a stimulus threshold such as the Rheobase.
- a stimulus threshold is preferably determined at at least two differing stimulus pulse widths, from which the Rheobase can be calculated.
- the conduction velocity is preferably measured and used to determine a fibre diameter recruited at threshold. Fitted relationships of the modelled single fibre Rheobase to the electrode-to-nerve separation are then used to determine the separation.
- Such embodiments may be particularly advantageous in applications providing or permitting only one measurement electrode, as may occur in the brain which does not comprise a single longitudinal neural pathway.
- the originating state of stimulation may in some embodiments be selectively explored in relation to a sub-population of fibres as defined by refractory period.
- the originating state of stimulation may be estimated in relation to a specific sub- population of the fibres selected for different refractory periods, for example by applying a stimulus sequence comprising a first stimulus referred to as a masker stimulus which recruits all the fibres of interest, and then a short duration later applying a second stimulus referred to as a probe stimulus.
- the duration between the masker and probe stimuli is selected to be longer than the refractory period of some fibres, but shorter than the refractory period of other fibres.
- Embodiments of the invention may thus be applied in neural stimulation applications where the separation between the responding fibres and the stimulating electrode varies often or even continuously with patient movement, whereby knowledge of the fibre-to-electrode distance or at least of incremental changes thereof, would be valuable.
- Other embodiments of the invention may be applied in relation to locating responding fibres three dimensionally in space in order to avoid or locate them during a surgical or imaging procedure for example.
- Such embodiments may further comprise identifying a target nerve fascicle within a larger nerve bundle, at differing locations along the nerve bundle, in order to detect variation in position of the fascicle within the bundle.
- the ECAP measurements are further used to estimate the distribution of fiber diameters present in an ECAP.
- An indication of the distribution or spread of fiber diameters can provide a useful validation for computer models and may be used to inform device and algorithm design to improve outcomes for SCS.
- the present invention provides a method of estimating a distribution of fibres recruited by a stimulus, the method comprising
- the present invention provides a device for estimating a distribution of fibres recruited by a stimulus, the device comprising
- At least one stimulus electrode and at least two sense electrodes configured to be spaced apart along a neural pathway
- measurement circuitry for obtaining a neural measurement from each sense electrode; and a processor configured to obtain from the at least two sense electrodes respective measurements of a compound action potential propagating along the neural pathway, determine a conduction velocity of the compound action potential from the latency between the measurements, determine from the conduction velocity a dominant recruited fibre diameter, determine a rate of dispersion of the compound action potential between the sense electrodes, and determine from the rate of dispersion a distribution of diameters of the recruited fibre population.
- the rate of dispersion may be determined in any suitable manner described herein, including any one or more of the observed ECAP peak width, ECAP peak spacing, ECAP zero crossings, ECAP half-height peak width or ECAP spectral content.
- the third and fourth aspects of the invention recognize that the overall distribution of fibre diameters, the distribution of fibre diameters recruited by a given stimulus, and/or the recruited fibres' conduction velocities may vary from one subject to the next. Moreover, some embodiments further recognize that variations in such characteristics may be correlated with the neurological condition which brought about the need for neurostimulation: for example, changes in conduction velocity and distribution of fibre diameters in dorsal columns have been recorded in mouse models of neuropathic pain as a result of central sensitization. Some embodiments of the third and fourth aspects of the present invention may thus further comprise treating the neurological condition by administering or modifying a therapy in a manner responsive to the determined distribution of diameters of the recruited fibre population, or responsive to a change in the determined distribution over time.
- the present invention provides a non-transitory computer readable medium for estimating a nerve-to-electrode distance, comprising instructions which, when executed by one or more processors, causes performance of the following:
- the present invention provides a non-transitory computer readable medium for estimating a distribution of fibres recruited by a stimulus, comprising instructions which, when executed by one or more processors, causes performance of the following:
- Figure 1 schematically illustrates an implanted spinal cord stimulator
- Figure 12 is a plot of the slope of peak widths relative to four selected population distributions;
- Figure 13 illustrates single fibre responses as superimposed at the stimulus site;
- Figure 18 is a plot of the width of the Nl peak plotted against the recording channel number, from the data of Figure 17;
- Figure 26 is a plot of the Rheobase current against electrode to fibre separation
- Figure 27 is a plot of a Rheobase-to-height fitting constant against fibre diameter
- Figure 28 presents simulated plots of the relationship of increasing separation upon Rheobase
- Figure 29 schematically depicts Rheobase measurement
- FIGS 30a-30d illustrate another embodiment in which electrode-to-nerve separation is measured by extracting frequency components of neural measurements. Description of the Preferred Embodiments
- FIG. 1 schematically illustrates an implanted spinal cord stimulator 100.
- Stimulator 100 comprises an electronics module 110 implanted at a suitable location in the patient's lower abdominal area or posterior superior gluteal region, and an electrode assembly 150 implanted within the epidural space and connected to the module 110 by a suitable lead.
- Numerous aspects of operation of implanted neural device 100 are reconfigurable by an external control device 192.
- implanted neural device 100 serves a data gathering role, with gathered data being communicated to external device 192.
- FIG. 2 is a block diagram of the implanted neurostimulator 100.
- Module 110 contains a battery 112 and a telemetry module 114.
- any suitable type of transcutaneous communication 190 such as infrared (IR), electromagnetic, capacitive and inductive transfer, may be used by telemetry module 114 to transfer power and/or data between an external device 192 and the electronics module 110.
- Module controller 116 has an associated memory 118 storing patient settings 120, control programs 122 and the like. Controller 116 controls a pulse generator 124 to generate stimuli in the form of current pulses in accordance with the patient settings 120 and control programs 122. Electrode selection module 126 switches the generated pulses to the appropriate electrode(s) of electrode array 150, for delivery of the current pulse to the tissue surrounding the selected electrode(s). Measurement circuitry 128 is configured to capture measurements of neural responses sensed at sense electrode(s) of the electrode array as selected by electrode selection module 126.
- FIG. 3 is a schematic illustrating interaction of the implanted stimulator 100 with a nerve 180, in this case the spinal cord however alternative embodiments may be positioned adjacent any desired neural tissue including a peripheral nerve, visceral nerve, parasympathetic nerve or a brain structure.
- Electrode selection module 126 selects a stimulation electrode 2 of electrode array 150 to deliver an electrical current pulse to surrounding tissue including nerve 180, and also selects a return electrode 4 of the array 150 for stimulus current recovery to maintain a zero net charge transfer.
- Delivery of an appropriate stimulus to the nerve 180 evokes a neural response comprising a compound action potential which will propagate along the nerve 180 as illustrated, for therapeutic purposes which in the case of a spinal cord stimulator for chronic pain might be to create paraesthesia at a desired location.
- the stimulus electrodes are used to deliver stimuli at 30 Hz.
- a clinician applies stimuli which produce a sensation that is experienced by the user as a paraesthesia. When the paraesthesia is in a location and of a size which is congruent with the area of the user's body affected by pain, the clinician nominates that configuration for ongoing use.
- the device 100 is further configured to sense the existence and intensity of compound action potentials (CAPs) propagating along nerve 180, whether such CAPs are evoked by the stimulus from electrodes 2 and 4, or otherwise evoked.
- CAPs compound action potentials
- any electrodes of the array 150 may be selected by the electrode selection module 126 to serve as measurement electrode 6 and measurement reference electrode 8.
- Signals sensed by the measurement electrodes 6 and 8 are passed to measurement circuitry 128, which for example may operate in accordance with the teachings of International Patent Application Publication No. WO2012155183 by the present applicant, the content of which is incorporated herein by reference.
- the present invention recognises that the amplitude and morphology of an ECAP measurement depends on a number of factors, including the quantity of recruited fibres contributing to the compound response, the conduction velocity or diameter of each recruited fibre, the separation of the electrode from the fibres in both the radial direction and the axial direction relative to an axis of the fibre, and the separation of the measurement electrode(s) from the stimulus electrode(s).
- the CAP profile takes a typical form and can be characterised by any suitable parameter(s) of which some are indicated in Figure 4.
- a normal recorded profile may take an inverse form to that shown in Figure 4, i.e. having two negative peaks Nl and N2, and one positive peak PI .
- the alteration or decay in the morphology of the observed neural response as it travels is also in part due to a spreading of the compound response across the cross section of the spinal cord 502 due to the variation in depth of the recruited fibres within the cord 502 at different positions along the cord.
- the compound response passes sense electrode E2 and is recorded as having an amplitude and duration indicated at 512, which differs from the form of the response at 510 in that response 512 is of reduced amplitude and greater width or duration.
- the compound response passes sense electrode E3 and is recorded as having an amplitude and duration indicated at 514.
- Observed response 514 is of lesser amplitude but greater duration then observed response 512.
- the compound response passes electrode E4 and is recorded as having a further decreased amplitude and increased duration as indicated at 516.
- Observed response 516 is of lesser amplitude but greater duration then observed response 514.
- each observed response is illustrative.
- the decay and spreading observed in any neural response will depend at least upon the characteristics of the fibre population actually recruited by the stimulus, the neurophysiology of the subject, and the distance of the electrodes from the fibres.
- electrodes E2 and E3 are used to obtain a first measurement 512 and a second measurement 514 of the neural response evoked by the stimulus, via measurement circuitry 522, 524 respectively.
- the evoked CAP measurements in this embodiment are made by use of the neural response measurement techniques set out in International Patent Publication No. WO2012/155183, with two data channels recording simultaneous data from the two electrodes E2 and E3.
- An improved knowledge of the electrophysiological response may lead to explanations of the large variability which is observed in outcomes from SCS and may provide valuable insight into electrode and device design, and improved stimulation algorithms.
- h is the distance of the measurement electrode from the fibre
- x n is the x co-ordinate of each node of Ranvier
- Im is the current produced by each node t is time
- v is the conduction velocity of the fibre.
- the field amplitude is inversely proportional to h, as the field is dominated by a single node of Ranvier.
- the shape of the action potential also changes with distance to the measuring electrode.
- the action current I m is weighted and summed at the measurement electrode, but with different delays for each of the nodes x n .
- the weights change because of the increase in distance from the node to the electrode. This looks like a filter (I/r).
- Figure 6 is a plot of computed single fibre action potentials, for 10 different fibre diameters from 19 ⁇ to 8.7 ⁇ .
- plot 602 shows the computed single fibre action potential for a 19 ⁇ diameter fibre
- plot 604 shows the computed single fibre action potential for a 8.7 ⁇ diameter fibre.
- the large diameter fibres conduct at the highest velocity and the smaller diameter fibres have progressively longer latency and are progressively smaller in size.
- SFAP single fiber action potential
- Figure 8 is a plot of each of the single fibre potentials, scaled by the population distribution of Figure 7 for the modelled fibre diameters, at a single location.
- the electrode-to- nerve distance was modelled as 6 mm
- Figure 9 illustrates the synthetic compound action potential calculated at multiple electrode locations by summation of the single fibre responses at each electrode location such as those shown in Figure 8 for a single location.
- Figure 9 shows such a synthetic compound action potential as observed at each of the electrodes positioned along the nerve and 6 mm away from the nerve, and at a distance of 35mm to 84mm away from the stimulus site, respectively.
- plot 902 shows the computed compound action potential as observed at the electrode 35 mm away from the stimulus site
- plot 904 shows the computed compound action potential as observed at the electrode 84 mm away from the stimulus site, with interposed plots shown for respective interposed electrodes.
- the simulated compound action potential decays (reduces in amplitude) and disperses (widens) as it travels away from the stimulus site.
- a convenient measure of the dispersion of the ECAP is to measure width of the Nl peak at half height, as indicated at 410 in Figure 4.
- the observed dispersion is related to the separation of the measurement electrode from the fibre, whereby for a given single action potential or compound action potential a narrower dispersion is observed at a smaller electrode- to-fibre separation and a wider dispersion is observed at a larger separation. This is a result of the previously discussed effect that the closer the electrode is to the fibre, the more the signal observed by the sense electrode is dominated by the nodes of Ranvier that are closest to the electrode. As the electrode-to-fibre distance increases, the signal present at the sense electrode becomes influenced by more nodes of Ranvier positioned along the fibre, dispersing the observed response.
- Figure 10 illustrates the calculated dispersion for a single fibre, being the width 410 of the Nl peak at half height, for a number of differing electrode-to-fibre separations. The relationship is linear and varies by a factor of 4 over the range of separations calculated.
- the plot of dispersion of the ECAP varies considerably with changes in the recruited fibre population, even for unchanged electrode-to-nerve separation.
- synthetic observations 1110 which all relate to an electrode-to-nerve separation of 6mm
- the variation in recruited fibre population can give dispersion as little as 50 between channel 5 and 16 in the case of observation 1112, or as large as 100 between channel 5 and 16 in the case of observation 1114.
- the modelled fibre population distributions at each height comprise a distribution width of 6, 7, 8 or 9 ⁇ , whereby a distribution with an increased number of smaller fibres, and having fibres of a smaller diameter, gives rise to an increased slope of the width at half height of the Nl peak in relation to the propagation distance.
- Similar variation can be seen in the synthetic observations 1120, which all relate to an electrode-to-nerve separation of 3 mm, for the same four selected fibre distributions.
- Figure 11 shows that the width at half depth of the Nl peak, and thus the CAP dispersion, has a linear dependence on the propagation distance, increasing with propagation distance due to impact of the smaller diameter fibres travelling at slower speeds and increasing the width or dispersion of the peak.
- Figure 12 is a plot of the slope, in ms per channel, of the peak widths relative to the four selected population distributions from the same data as Figure 11. As can be seen, as the population distributions are widened by the addition of smaller fibres, the resulting dispersion increases.
- embodiments further provide for an estimation of the absolute value of the distance d, as follows. These embodiments are based on the recognition that the ECAP peak width at Channel 0 (being the stimulus location) is dominated by the width of the single fibre action potential of the largest recruited fibre contributing to the response. For a given nerve, the largest recruited fibre is typically the most easily recruited and can thus be assumed to have been recruited if any ECAP at all is evoked.
- the action potential peak width of the largest recruited fibre is a constant, but will be observed as a broader peak with increasing fibre to electrode distance d.
- the peak width of the observed response at channel 0 is dependent on the separation d but is substantially independent of the population distribution of the fibres recruited, at least for the range of populations simulated in figure 11.
- Figure 13 shows the action potentials calculated for individual fibres over a range of fibre diameters from 18 micron (SFAP 1302) to 23 micron (SFAP 1304), with intervening fibres' action potentials shown but not labelled.
- the sum of the SFAPs produces the larger CAP 1306.
- the larger diameter fibres produce the largest SFAP responses.
- the smaller diameter fibres at Channel 0 contribute responses to the compound response 1306 which are enveloped by, or do not significantly affect some key characteristics of, the single fibre response 1304 of the largest contributing fibre diameter.
- recording electrodes positioned both caudally and rostrally of the stimulus electrode(s) may be used to provide both orthodromic and antidromic estimates of ECAP dispersion to give a combined estimate of the originating ECAP peak width and the electrode height.
- electrodes spanning a single vertebral segment and recordings were made across 4 vertebral segments. It is evident when comparing the upper and lower portions of Figure 19c, and of Figure 19d, that both the dip or cornerpoint in the amplitudes and the change in slope of the dispersion plot correspond with the fibres crossing from one verterbral segment to the other.
- the conduction velocity observed in Figure 15a enables a determination to be made as to the diameter of the most abundant fibre in the recruited fibre population, in this case 21 ⁇ .
- the slope of the width at half height observed in Figure 16a and 16b enables the relationship shown in Figure 12 to be used to estimate the distribution of recruited fibres.
- a profile of the distribution of recruited fibres may be produced. This involves taking a nominal distribution profile, and summing the individual fibre contributions to a simulated ECAP using a chosen single fibre model, and fitting the simulated ECAP to an observed ECAP by trial and error adjustment of the nominal profile, until a best fit is found.
- Figure 21 the best fit fibre distribution profile determined in this manner is shown in Figure 21.
- Figure 22 comprises plots 2202 of the simulated ECAP resulting from single fibre modelling and summation of a recruited fibre distribution having the profile shown in Figure 21, together with plots 2204 of the actual observed sheep ECAP data, as observed at electrodes at distances from 35 mm to 84 mm away from the stimulus site.
- Any suitable fitting technique such as a pointwise least squares fitting, may be applied to determine which nominal fibre distribution profile gives the best fit to an observed ECAP.
- some embodiments of the invention may additionally or alternatively seek to use response dispersion to estimate the recruited fibre population's dominant fibre size, and also the width of the distribution of fibre sizes recruited.
- the total number of fibres recruited is simply the integral of the population distribution curve and for the sheep spinal cord the total number of recruited fibres is 2080 fibres at 1.0mA, 1780 fibres at 0.9 mA, 1440 fibres at 0.8mA and 545 fibres at 0.7mA.
- a technique which can be used to estimate the nerve-to- electrode distance d involves probing the Rheobase by delivering appropriate stimuli and measuring the neural responses thereto.
- Fig 25 comprises an alternative representation of the strength duration curve of Figure 24, by plotting applied charge against pulse width, for a 10 micron diameter fibre. Further, this figure includes a plot at a number of electrode separations from the fibre, namely a plot 2502 for a separation of 3 mm, 2504 for 4 mm, 2506 for 5 mm, 2508 for 6 mm, 2510 for 7 mm and 2512 for 8 mm. In this representation of the strength duration curve, each curve is substantially linear and the slope is equal to the Rheobase current.
- this embodiment applies stimuli of varying pulse width from a first stimulus electrode to determine at least two points on the strength-duration curve, as it exists for the unknown separation h. From two such points, the Rheobase R for the first-recruited fibre can be calculated in respect of the first stimulus electrode. Because fibre diameter D is unknown, the Rheobase R alone does not yield h.
- Figure 28 shows simulated plots of the relationship of increasing separation upon the expected Rheobase value.
- Rheobase generally increases as electrode-to-nerve distance increases.
- the relationship follows a curve and not linear, and moreover at any given separation the Rheobase value of one fibre diameter differs from a differing fibre diameter.
- the observed response is a compound action potential
- the first-recruited fibre will always be the same, being the largest most proximal fibre to the stimulus electrode. That is, the separation vs Rheobase relationship for the observable compound response will be the same as the curve 2802 of the largest most easily recruited fibre.
- a curve may be fitted to the data points of Figure 27 to improve B estimation, and such embodiments are within the scope of the present invention.
- the Rheobase current can be estimated from the slope of the charge duration curve.
- the slope estimation requires at least two points along this curve, and to obtain these two points requires estimation of the threshold of response for two different stimulus durations.
- the threshold measurement can be made in a number of ways, and a simple way to make this measurement, schematically depicted in Figure 29, is to measure the slope of the amplitude of the ECAP with respect to stimulation current, to estimate a threshold current.
- the stimuli sequence could be applied continuously and the Rheobase calculated continuously and averaged over time, or further signal processing techniques applied to improve the SNR of this measure.
- the conduction velocity needs only be measured infrequently and for many applications can be measured only once, or on rare occasions, to provide the remaining constant.
- Figures 30a-30d illustrate another embodiment of the invention, in which ECAP dispersion, and electrode-to-nerve separation, are measured or assessed by extracting frequency components of the neural measurements, by fast Fourier transform.
- the neural measurements are first windowed to exclude discontinuities or like stimulus effects and/or measurement effects.
- the frequency domain information of the respective neural measurements may then be used to extract a measure of the dispersion.
- Figure 30a plots simulations of the ECAP of a 12 ⁇ diameter fibre measured 35mm away from the stimulating site and at separations of 2,3,4,5 and 6 mm, respectively, between the electrode and the fibre. Once again, both the amplitude and the dispersion of the observed response changes with separation, with larger separations producing smaller more dispersed responses.
- Figure 30b shows the Fourier spectrum of the data from the first figure (Haming window).
- the present embodiment operates by noting that the decay in the frequency response of each observed ECAP at frequencies higher than the peak is linear. It is also noted that the peak amplitude of each curve in Figure 30b, and the spectral spread of each curve, reflects the sharpness of the observed response, and either or both such measures may thus be used as a measure of the inverse of response dispersion.
- Figure 30c shows the slope of the decay of frequency contributions to each respective observed response, at frequencies higher than the peak of the respective curve. The present embodiment further notes that the slope of the decay of each curve is proportional to the separation of the fibre from the electrode, whereby a steeper decay slope corresponds to greater dispersion and thus greater separation.
- Figure 30d is a plot of decay slope against separation, indicating the monotonic nature of this relationship in the separations observed, and for example Figure 30d may be reflected in a lookup table whereby the spectral decay slope observed in a given response may be used to look up electrode- to-nerve separation.
- Such embodiments may be advantageous in measuring dispersion in noisy neural measurements, as a frequency roll-off can be averaged or fitted over a relatively wide spectral range.
- Such embodiments may further be advantageous in enabling a measure of dispersion to be obtained without reliance on the amplitude of the ECAP, for example in embodiments where manual user feedback or automated feedback operates to control recruitment at a substantially constant level.
- An image so produced could in turn be used to guide a surgical procedure, such as the removal of tissue with little or no response such as is performed in DREZ lesion surgery, or detection and removal of aberrantly responding tissue such as the removal of brain lesions responsible for focal origin epilepsy.
- the geometry of the sensing stimulating electrodes need not be planar but may be circumferential to a neural structure such as those employed in cuff electrodes. Electrodes spaced around the circumference of a major nerve, for instance the vagal nerve could use the techniques described above to provide estimates as to the locations of individual fascicles within the nerve bundle. It is highly desirable to be able to address individual fascicles with stimulation and a knowledge of the fascicle geometry and arrangement could, via current steering or other means, provide selective stimulation.
- fascicles in major nerves do not run a linear course through the nerve. For example, examination of serial cross sections of the nerve at different positions along the nerve would reveal that individual fascicles at the centre of the bundle in one section could be found at the edges in another section. This observation, combined with the herein described techniques to map the separation of electrode to active tissue, could be used to choose effective electrodes or be used to appropriately place a cuff electrode on a nerve during surgery.
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CA2973855A CA2973855A1 (en) | 2015-04-09 | 2016-04-08 | Electrode to nerve distance estimation |
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JP2017546830A JP7071121B2 (en) | 2015-04-09 | 2016-04-08 | Estimating the distance between the electrode and the nerve |
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AU2021201010A AU2021201010B2 (en) | 2015-04-09 | 2021-02-16 | Electrode to nerve distance estimation |
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