Source: https://patents.google.com/patent/CN102971046B/en
Timestamp: 2020-07-02 10:18:00
Document Index: 491497594

Matched Legal Cases: ['art 12', 'art 12', 'art 12', 'art 12', 'art 12', 'art 12', 'art 12', 'art 12', 'art 12']

CN102971046B - Consider the cell durability estimation device of high current drain situation - Google Patents
Consider the cell durability estimation device of high current drain situation Download PDF
CN102971046B
CN102971046B CN201180033171.9A CN201180033171A CN102971046B CN 102971046 B CN102971046 B CN 102971046B CN 201180033171 A CN201180033171 A CN 201180033171A CN 102971046 B CN102971046 B CN 102971046B
CN201180033171.9A
CN102971046A (en
A·M·克雷斯皮
2010-07-06 Priority to US12/830,748 priority Critical
2010-07-06 Priority to US12/830,748 priority patent/US8452395B2/en
2011-06-13 Application filed by 美敦力公司 filed Critical 美敦力公司
2011-06-13 Priority to PCT/US2011/040179 priority patent/WO2012005880A1/en
2013-03-13 Publication of CN102971046A publication Critical patent/CN102971046A/en
2015-12-09 Publication of CN102971046B publication Critical patent/CN102971046B/en
230000000747 cardiac Effects 0.000 description 6
For estimating the system and method for the residual capacity of the battery of implantable medical devices.This implantable medical devices there is generation current and there is the battery of remaining battery capacity, this implantable medical devices is configured to use the electric current of relatively low quantities and in particular case, use the relatively large pulse of electric current.Processor is coupled to this battery, and is configured to, at least in part based on the generation of the particular case of the relatively large pulse of measured battery parameter and delivered current, calculate the estimation of remaining battery capacity.
Consider the cell durability estimation device of high current drain situation
The application relates to field of medical device, particularly, relates to the system and method for the residual capacity of the battery for estimating implantable medical devices.
The such as implantable medical devices of conversion device/defibrillator and so on is configured to treat arrhythmia by high-pressure energy pulse is passed to heart tissue usually.Implantable defibrillator is usually by being placed on electrodes transfer treatment in patient's heart or neighbouring.Such treatment comprises defibrillation treatment, and it utilizes suddenly, the pulse of high energy, and this pulse is designed to, and if when arrhythmia occurs, impact patient's heart and make it break away from arrhythmia.Implantable defibrillator is generally also in conjunction with pacing therapy, and it uses the very low energy impulse being designed to triggering cardiac and shrinking, and substitutes the abundant natural heart beating frequently of patient.
Implantable defibrillator generally in conjunction with power supply, such as battery, it provides operating energy to the componentry of defibrillator, comprises electronic unit, the function of electronic unit management equipment, monitor the implanted patient of wherein equipment situation and transmit treatment to patient.A lot of or most of functions of the equipments continuously and effectively operate, such as sense the heart condition of patient, or operate continually, the cardiac pacing therapy transmission such as in particular patient, and therefore consider stable, the measurable and general low level current drain of battery capacity.Defibrillation is treated, otherwise, generally very infrequently occur in Most patients, be generally separated by several months or several years between defibrillation treatment is transmitted, this is because the general spot of arrhythmia of needs treatment is infrequently.Therefore, from the angle of battery management, defibrillation treatment be on the battery of implantable defibrillator more greatly, suddenly, random in essence current drain.
Because implantable defibrillator often provides life-sustaining therapy to the patient of implanted defibrillator, may it is necessary that make patient understand battery be discharged to the point of reliable treatment can not be provided before battery can be expected to how long continue.As known in the art, the terminal voltage being used in the battery in implantable defibrillator is general to a certain extent, corresponding to the residual charge of battery.Such as, along with residual charge reduces, terminal voltage similarly reduces.But, terminal voltage may not and often not, with completely direct and predictable relation, corresponding to the residual charge in battery.
Specifically, it has been found that, although metastable current drain can cause relative measurable between terminal voltage with residual charge and relation accurately on battery, stable current drain adds that accidental unexpected, larger current drain can reduce the accuracy of the relation between terminal voltage and residual charge.For relatively short for this impact possibility persistent period of the accuracy of the prediction of battery residual charge based on the relation between terminal voltage and residual charge, but be proved to be the impact continued for being applied with certain.Unexpected, larger current drain on the low level current consumption on basis has been proved to be the relation for offset by terminal voltage and residual charge, thus terminal voltage continues to record the angle of residual charge in relative battery lower than expected result.
As a result, the skew in terminal voltage-residual charge relation can cause battery at real surplus electric charge fully low so that should be assessed as electric charge low and need to change or charging a period of time after, be assessed as so just now.In addition, show, compare longer a period of time after larger current consumes, after larger current consumption at once, the skew of the relation between terminal voltage and residual charge is relatively large.Such change can reduce further only based on the reliability of the battery measurement of terminal voltage.
By calculating with two important mode regulating cell ends, alleviate the impact being derived from the high current drain that defibrillation pulse is transmitted.First, the adjustment considering the frequency of high current drain event is incorporated in in battery end calculating.Determine, this adjustment can affect the quantity of electric charge that uses during high current occurrences and when battery manufacture or the original charge available of the early stage battery of battery life.The second, disperse analysis for battery residual charge to alleviate the relatively large impact of short term variations for terminal voltage-residual charge relation relative long period of time.
In one embodiment, system comprises implantable medical devices and processor.Implantable medical devices has generation current and has the battery of remaining battery capacity, and this implantable medical devices is configured to use the electric current of relatively low quantities and the relatively large pulse using electric current in particular case.This processor is operatively coupled to battery and is configured to, at least in part based on the generation of the particular case of the relatively large pulse of measured battery parameter and delivered current, calculate the estimation of remaining battery capacity.
In one embodiment, this processor is configured to, at least in part based on the frequency of the particular case of the relatively large pulse of measured battery parameter and delivered current, calculate the estimation of remaining battery capacity.
In one embodiment, this processor is configured to the estimation calculating remaining battery capacity further at least in part based on measured battery parameter, and then reduces the estimation of remaining battery capacity at least in part based on the number of times of the generation of the particular case of the relatively large pulse of delivered current.
In one embodiment, this processor is configured to, at least in part based on the function of the initial charge of the number of times of the generation of the particular case of the relatively large pulse of delivered current, the quantity of electric charge used in the relatively large pulse of electric current and battery, calculate the estimation of remaining battery capacity.
In one embodiment, this processor is configured to the initial charge being multiplied by charge ratio and the battery used in the relatively large pulse of electric current at least in part based on frequency, calculates the estimation of remaining battery capacity.
In one embodiment, this processor is configured to the estimation regulating remaining battery capacity at least in part based on the function of the remaining battery capacity recorded in a period of time.
In one embodiment, this period of time is at least one week.
In one embodiment, this period of time was at least two weeks.
In one embodiment, this period of time is at least surrounding.
In one embodiment, this period of time is at least ten two weeks.
In one embodiment, this period of time is at least two ten six weeks.
In one embodiment, this function is the equalization that the several remaining battery capacities obtained within this period of time are measured.
In one embodiment, measured battery parameter is cell output voltage.
In one embodiment, this processor is the assembly of implantable medical devices.
In one embodiment, this system comprises the external equipment comprising this processor further.
In one embodiment, disclose the method for the remaining battery capacity of the battery for estimating implantable medical devices, this implantable medical devices is configured to use the electric current of relatively low quantities and in particular case, use the relatively large pulse of electric current, the method use processor.The method comprises at least in part based on the generation of the particular case of the relatively large pulse of measured battery parameter and delivered current, calculates the step of the estimation of remaining battery capacity.
Fig. 1 is the diagram of implantable cardioversion defibrillator;
Fig. 2 is the functional schematic block diagram of the cardioversion defibrillator of Fig. 1;
Fig. 3 is the graph-based of the relation between the residual charge of implantable medical devices battery and terminal voltage; With
Fig. 4 is the flow chart of the residual capacity for estimating implantable medical devices battery.
Fig. 1 is the diagram of the implantable medical devices 10 of implanted patient.In the illustrated embodiment in which, implantable medical devices 10 is the heart defibrillators with pacing function.Pacing function can treat the bradycardia and can when chronic heart failure synchronous heart 12 again.Such defibrillator is called as cardiac resynchronization therapy defibrillator, CRT-D equipment of being known as in the art.In each embodiment, implantable medical devices 10 can be do not have pacing function or have pacing function but do not have the conversion device/defibrillator of cardiac resynchronization feature.In addition, implantable medical devices 10 can be combine any equipment from the high current drain of battery.Implantable medical devices 10 is coupled to heart 12 by coronary sinus lead 14, right atrial lead 16 and right ventricular lead 18.Contiguous block 20 receives the connector 22,24 and 26 being positioned at coronary sinus lead 14, right atrial lead 16 and right ventricular lead 18 near-end separately, and provides electrical connection between circuit in lead-in wire 14,16,18 and implantable medical devices 10.
In the illustrated embodiment, ring electrode 28, be retractably arranged on extensible screw electrode 30 in electrode tip 32 and coil electrode 34, be placed in right ventricular lead 18 and the insulated electric conductor be electrically coupled in right ventricular lead 18.As shown in the figure, right ventricular lead 18 is placed as and makes its far-end be positioned at right ventricle, for sensing right ventricle heart signal and pace-making or shock pulse being passed in right ventricle.The corresponding connector that the connector 26 that the near-end of insulated electric conductor is coupled to bifurcated carries, for providing electrical connection to implantable medical devices 10.
Right atrial lead 16 can comprise and is retractably arranged on ring electrode 36 in electrode tip 40 and extensible screw electrode 38, for sensing and pace-making right atrium.Right atrial lead 16 can comprise coil electrode 42 further to transmit high energy impact treatment.Right atrial lead 16 can be placed as its far-end be positioned at right atrium and superior vena caval near.Ring electrode 36, screw electrode 38 and coil electrode 42 can be connected to separately and be positioned at the intrinsic insulated electric conductor of right atrial lead 16.Insulated electric conductor can be coupled to bifurcated connector 24 at its near-end.
Coronary sinus lead 14 can comprise defibrillation coil electrode 44, and its can be combined coil electrode 34 or coil electrode 42 combinationally use to transmit surge for cardioversion and defibrillation treatment.Coronary sinus lead 14, via coronary sinus and great cardiac vein, can be pushed in the vascular system in the left side of heart 12.In embodiments, coronary sinus lead 14 also can comprise distal tip electrode 45 and ring electrode 47, for the pace-making in left side of heart chamber and sensing function.Coil electrode 44 is coupled to the intrinsic insulated electric conductor of lead-in wire 14.Insulated electric conductor can be coupled to connector 22 at its near-end.
Electrode 28,30,36 and 38 can be used bipolar right to be formed.Various like this bipolar to can be called as " most advanced and sophisticated to ring " right.Electrode 28,30,36 and 38 can be used in similarly independently to be had in monopolar configuration, and implantable medical devices shell 46 is used as neutral electrode, is commonly referred to as " tank " or " shell " electrode.Shell 46 also can be used as subcutaneous defibrillation electrode, with coil electrode 34,42 and 44 in the atrium 48,50 of one or more combinations for heart 12 or the defibrillation of ventricle 52,54.In embodiments, the lead system of the embodiment of alternate figures 1 can be carried out with optional lead system.The lead-in wire used together with single chamber, dual cavity or multi-chamber implantable medical devices can be used.
Fig. 2 is the functional schematic diagram of implantable medical devices 10.Splicing ear 56 provides and is electrically connected to shell 46, and shell 46 is used as neutral electrode in unipolar stimulation or detection process.Splicing ear 58,59 and 60 is provided to the electrical connection of coil electrode 44,42 and 34 respectively.Each of splicing ear 56,58,59 and 60, uses coil electrode 34,42 and 44 and one or more in one embodiment in shell 46, is coupled to high-voltage output circuit 62, helps high energy impact pulse to be passed to heart 12.
Splicing ear 64 and 66 provides the screw electrode 38 and ring electrode 36 that are electrically connected to and are arranged in right atrium separately.Splicing ear 64 and 66 is coupled to atrial sense amplifier 68 further for sensing the heart signal in the atrium being derived from heart 12.Such signal comprises atrial depolarization and is generally identified as the P-ripple in electrocardiogram.Splicing ear 70 and 72 is provided to the electrical connection of screw electrode 30 and ring electrode 28 respectively.Splicing ear 70 and 72 is coupled to ventricular sense amplifier 74 further for sensing ventricular cardiac signal.
Atrial sense amplifier 68 and ventricular sense amplifier 74 can take the form of the automatic gain controlled amplifier with scalable sensing threshold value.In one embodiment, the general operation of ventricular sense amplifier 74 and atrial sense amplifier 68 may correspond in the U.S. Patent No. 5,117 people such as Keimel, operation disclosed in 824.When the signal that atrium sensing amplifier 68 receives exceedes atrial sense threshold value, P-output signal line 76 can generate signal.When the signal that ventricle sensing amplifier 74 receives exceedes ventricular sense threshold value, signal can be generated to represent the sensing of ventricular depolarization on R-output signal line 78.
In one embodiment, use switch matrix 80 to come in choice electrode 28,30,34,36,38,42,44 which be coupled to broadband amplifier 82 for Digital Signal Analysis.Via data/address bus 86, the various electrodes in choice electrode 28,30,34,36,38,42,44 can be controlled by microprocessor 84, thus create electrode configuration.According to desired by the various sensings of implantable medical devices 10, pace-making, cardioversion and defibrillation function, electrode configuration can be changed.Multiplexer 88 can be provided to from the signal being selected for the electrode being coupled to bandpass amplifier 82, and be after this converted into multistation digital signal by A/D converter 90, for being stored in random access memory 92 under the control of direct memory access circuit 93.Microprocessor 84 can adopt Digital Signal Analysis technology to characterize the digitized signal be stored in random access memory 92, adopts identifying arbitrarily and the rhythm of the heart of classifying in the signal processing method of One's name is legion known in the art.
In one embodiment, once arrhythmia be detected, from the data that electrode 28,30,34,36,38,42,44 obtains, the respective annotations of event comprising EGM, the interval sensed and sense, can be stored in random access memory 92.The electric trace signal stored can from the near field be programmed and/or far field sensing electrode to sensed.Near field sensing electrode, to comprising, in one embodiment, is arranged in point electrode and the ring electrode of atrium 48,50 or ventricle 52,54, such as electrode 36 and 38 or electrode 28 and 30.In embodiments, far field sensing electrode is any to what can comprise in following example combinations: defibrillation coil electrode 32,42,44 right arbitrarily; Any and shell 46 of defibrillation coil electrode 32,42,44; Point electrode 30,38 and shell 46; Point electrode 30,38 and defibrillation coil electrode 34,42; Or atrial tip electrode 38 and ventricle ring electrode 28.Supplemantary electrode can be used to combine.
In each embodiment, implantable medical devices 10 can use and be positioned at lead-in wire outside chest and electrode.In such embodiments, electrode can sense far field heart signal, contrary with the near-field signals be positioned at or sense close to the electrode 28,30,34,36,38,42,44 of heart 12.Combine the implantable medical devices 10 that is positioned at lead-in wire outside chest and electrode known in the art be subcutaneous implantable cardioversion defibrillator, and mode that can be relevant to above-mentioned conventional defibrillator transmits the heart 12 of defibrillation treatment.
As conventional in implantable medical devices, by the mode of antenna 95, telemetric circuit 94 can receive the downlink telemetry from external programmer and can send up-link remote measurement to external programmer.Can to be provided by microprocessor 84 via address/data bus 86 to the data of programmable device and the control signal of telemetric circuit by up-link.Once have arrhythmia detection or being triggered by other monitoring algorithms, the electricity be stored traces data can use telemetric circuit 94 by up-link to external programmer.Received remote measurement can be provided to microprocessor 84 via multiplexer 88.The various telemetry systems be used in implantable equipment of One's name is legion well known in the prior art can be used.
Pacemaker sequential and control circuit 96 comprise programmable digital enumerator, it controls and various single, double or multi-chamber pacing mode, or the anti-tachyarrhythmia pacemaker that transmits in atrium or ventricle treat the elementary event interval be associated.Under the control of microprocessor 84, pacemaker circuits 96 also determines the amplitude of cardiac pacing pulse.
In pace-making process, once sense atrium and ventricular depolarization, that is, P-ripple and R-ripple, respectively as shown in the signal on line 76 and 78, the ease in pacemaker sequential and control circuit 96 is won interval counter and can be reset.According to selected pacing mode, generate pacemaker impulse by atrial pacemaker output circuit 98 and ventricular pace maker output circuit 100.Pacemaker output circuit 98 and 100 is coupled to desired electrode for pace-making via switch matrix 80.Once generation pacemaker impulse, the rich interval counter of ease is reset, and controls the basic sequential of heart pace-making function (comprising anti-tachyarrhythmia pacemaker) by this.
The persistent period at the rich interval of ease can be determined by microprocessor 84 via data/address bus 86.The count value presented in the rich interval counter of ease, when being reseted by sensed R-ripple or P-ripple, can be used to measure R-R interval and P-P interval for detecting various ARR appearance.
Microprocessor 84 comprises the ROM be associated of the program stored of wherein having stored the operation controlling microprocessor 84.A part for random access memory 92 can be configured to multiple recirculation buffer, and a series of measured interval can be kept to be used for being analyzed by microprocessor 84 predicting or diagnose arrhythmia.
In response to tachycardic detection, by being loaded in pacemaker sequential and control circuit 96 according to detected tachycardic type by the therapeutic scheme from microprocessor 84, anti-tachyarrhythmia pacemaker treatment can be passed.When needing more high-tension cardioversion or defibrillation pulse wherein, microprocessor 84 activates cardioversion and defibrillation control circuit 102, under the control of high-voltage charging control line 110, via charging circuit 108, initialize the charging of high-voltage capacitor 104 and 106.Voltage on high-voltage capacitor is via voltage capacitor line 112 (it is by multiplexer 88) monitoring.When voltage reaches the predetermined value of microprocessor 84 setting, be full of formation logic signal on line 114 at capacitor, stop charging.Via control bus 116, under the control of pacemaker sequential and control circuit 96, by output circuit 62, defibrillation or cardioversion pulse are passed to heart.Output circuit 62 determines the electrode and the shape of impulse wave that are used to transmission cardioversion or defibrillation pulse.
Battery 118 provides power supply to operate the electric assembly of implantable medical devices 10.Electricity assembly includes, but not limited to microprocessor 84, RAM92, telemetry module 94, pacemaker sequential and control 96, cardioversion/defibrillation controller 102 and high voltage charge circuit 108.In embodiments, battery 118 is selected from conventional implantable medical devices battery chemistries component, comprises nickel-cadmium and lithium ion, but can use other chemical constituents optional.
Fig. 3 is the diagram of the conventional relationship 119 between the terminal voltage 120 of battery 118 and the residual capacity 122 of battery 118.In embodiments, when battery 118 has complete electric charge, battery 118 produces the terminal voltage 120 of about 3.2 volts, that is, residual charge 122 equals the total capacity of battery 118.When the residual charge 122 of battery 118 is decayed, terminal voltage 120 also can decay.But terminal voltage 120 linearly may not decay with the decay of residual charge 122.Specifically, in most service life of battery 118, battery 118 can maintain about three (3) volts and to add deduct the terminal voltage 120 of about 0.25 volt.In one embodiment, when the residual charge of battery 118 drops on about less than 15% of its initial charge, terminal voltage can be less than about 2.75 volts, this point, implantable medical devices 10 can need to replace by pilot cell 118, such as by replacing implantable medical devices 10 completely or by replacing battery 118 itself, or in each embodiment combining recharging circuit wherein then pilot cell 118 need to recharge.
According to the above-mentioned estimation for residual charge 122, the average current come from battery 118 transmission can be calculated as battery charge over time, or:
Formula 1:I ave=dQ/dt.
Then, according to following formula, the measurement of the terminal voltage of the battery 118 in the very first time can be obtained:
Formula 2:V 1=f (Q 1, Q 1/ t 1)
And the second time measurement of the terminal voltage of the battery 118 of the second time can be defined as:
Formula 3:V 2=f (Q 2, (Q 2– Q 1)/(t 2– t 1))
In embodiments, terminal voltage 120 is enough to reach fully estimating accurately for residual capacity 122.But, according to the relation of formula 3, in an alternative embodiment, by solving different residual electricity charge values, relatively estimating more accurately for residual capacity 122 can be obtained.In such embodiments, implantable medical devices 10 directly according to the multiple factors relevant with battery 18, does not calculate residual capacity 122 according to terminal voltage 120.
In one embodiment, the inverse percentage ratio of residual capacity 122 is called as " depth of discharge ", estimated according to each battery parameter.In iterative formula, the total electrical charge Q before battery 188 transmits lastthe electric charge dQ of the estimation of transmitting within a period of time being coupled with the formula of the total electrical charge transmitted from battery 118 from a front iterated application est, and divided by when battery 118 manufactures or close to manufacture time battery 118 initial charge Q max.In one embodiment, dQ estbe directly proportional to the electric current transmitted from battery 118 on scheduled time frame.The calculating that depth of discharge is estimated can be represented according to formula 4:
Formula 4:DOD est=(Q last+ dQ est)/Q max
But, have been found that high electric current therapy, the transmission of such as defibrillation energy, the skew of the depth of discharge estimation that may continue in whole battery life 118 can be caused.Specifically, if implantable medical devices 10 transmits defibrillation treatment to heart 12, due to each is transmitted defibrillation pulse, battery 118 chemical constituent in increment change, the depth of discharge estimation possibility calculated by formula 4 is relatively too low (namely, compare depth of discharge estimation to propose, battery 118 can have more capacity residue).Specifically, the transmission of single defibrillation pulse can trend towards the DOD according to formula 1 estskew one value, this value approximates greatly as original battery capacity Q maxthe quantity of electric charge Q transmitted in defibrillation pulse of certain percentage ratio perCharge.Q perChargecan change based on the frequency of defibrillation pulse, electric current and persistent period.Therefore, formula 4 can be modified to following formula 5, and formula 5 can be used to obtain and consider the depth of discharge that the estimation of the times N be passed treated by defibrillation.In embodiments, defibrillation treatment can in conjunction with charge transfer, from about 7.5 milliamperes-hour to about 100 milliamperes-hour.
Formula 5:DOD estDefib=(Q last+ dQ est)/Q max+ (N*Q perCharge)/Q max
Equipment that can be battery-powered wherein realizes formula 5 when having high current drain (wherein transmitting electric charge from about 7.5 milliamperes-hour to about 100 milliamperes-hour within about 20 (20) seconds or shorter relatively short time frame).In an alternative embodiment, reducible five (5) milliamperes of high current drain scope-hour or higher.
Formula 5 can by a period of time inner iteration should be used for obtaining the multiple measurements reflecting during this period of time battery 118 characteristic depth of discharge estimate.In embodiments, formula 5 can be applied more than twice with being iterated.In one embodiment, formula 5 is employed more than 1,000 times or until meet stability criterion, obtains final depth of discharge estimation.In one embodiment, if based on the output current recorded of battery 118 and the estimation terminal voltage V of the battery 118 of depth of discharge estimated estthe terminal voltage V recorded measuredthreshold tolerance in, then meet stability criterion.In one embodiment, this threshold tolerance is 0.1 millivolt.
In an embodiment, more than one stability criterion can be applied, be included in from battery 118 largest tolerable current drain be used to calculate above-mentioned estimation terminal voltage V estbattery 118 the output current recorded between difference be less than threshold current value.In one embodiment, threshold current value is 0.01% of largest tolerable electric current.In one embodiment, the largest tolerable electric current from battery 118 is about 0.4 ampere.In an alternative embodiment, largest tolerable electric current is from the scope of 0.3 ampere to 0.5 ampere.In one embodiment, if the stability condition relating to the terminal voltage that records or the difference between largest tolerable electric current and the output current recorded of battery 118 is satisfied, if or meet setting quantity iteration (in the above-described embodiments, 1,000), then closing-styled 5 iterative.
In order to applying equation 5 iteratively, within the time between the previous iteration and current iteration of next-door neighbour, be iteration each time, the electric current that usable-battery 118 transmits obtains to be measured.Time dependent electric current is applied as the change dQ of electric charge in time est, then it be applied to the new iteration of formula 5.As mentioned above, then dQ is used estnew value applying equation 5 iteratively, until meet the iteration of stability condition or maximum quantity.The value that is final, that obtain iteratively of depth of discharge estimation can be applied to the electric charge residue of estimating battery 118.
Even if after the iterative estimation of the depth of discharge of battery 118, in a particular embodiment, advantageously, not the decision made on single, the iterative estimation of depth of discharge about replacing battery 118.Such iterative estimation can be recorded, even if carried out 1,000 iteration, in any case and therefore can the short-term transition of chemical constituent of the sensitive battery 118 in causing due to the high current drain on battery 118 within several seconds or several minutes.In the specific passing embodiment of offset characteristic not recognizing the short-term calculated for the electric charge residue of implantable medical devices application, the estimation of some electric charge residue is averaged on the time period of two weeks.
But, based on the characteristic of the high electric current transmitted when the chemical constituent of battery eliminator and battery 118, for two weeks of depth of discharge estimation be averaged the short-term skew that may be sensitive to and be derived from high electric current and transmit.Therefore, in embodiments, can two weeks be greater than, the time period of surrounding such as, be averaged for depth of discharge measurement.In embodiments, at 12 weeks, moving window records depth of discharge to measure.In one embodiment, at 26 weeks, moving window records depth of discharge to measure.Therefore, the rolling average that depth of discharge can be used to estimate is made about until battery 118 needs replaced or recharges the judgement of front possible remaining time.
Fig. 4 is the flow chart of the method for the remaining battery capacity of the battery 118 of estimation implantable medical devices 10.Record battery parameter (400).As mentioned above, the battery parameter recorded can comprise the electric current that the terminal voltage of battery 118 and battery 118 transmit.At least in part based on measured battery parameter, calculate the estimation of (402) remaining battery capacity.In embodiments, calculating is based on above-mentioned formula 4, and remaining battery capacity is the initial charge Q based on battery 118 maxand the difference between the depth of discharge calculated in above-mentioned formula 4.Then, at least in part based on the frequency of relatively large pulse current (such as defibrillation pulse), reduce (404) electric charge residue.In one embodiment, the effect of step (402) and (404) realizes above-mentioned formula 5 to determine DOD estDefib, it can be converted into the electric charge residue of battery 118.
The estimation of equalization (406) remaining battery capacity on moving window, thus the estimation of the equalization of remaining battery capacity is provided.As mentioned above, can on the window at least two weeks equalization remaining battery capacity.In each embodiment, this window can at least surrounding, 12 weeks or 26 weeks.
Implantable medical devices, comprises generation current and has the battery of remaining battery capacity, described implantable medical devices be configured to use relatively low quantities described electric current and, in particular case, use the relatively large pulse of described electric current;
Described system has processor, described processor is operatively coupled to described battery and is configured to, at least in part based on the generation of measured battery parameter with the particular case of the relatively large pulse of the described electric current of transmission, calculate the estimation of described remaining battery capacity.
2. medical system as claimed in claim 1, it is characterized in that, described processor is configured to, further at least in part based on the frequency of described measured battery parameter with the described particular case of the relatively large pulse of the described electric current of transmission, calculate the estimation of described remaining battery capacity.
3. medical system as claimed in claim 2, it is characterized in that, described processor is configured to the estimation calculating described remaining battery capacity further at least in part based on described measured battery parameter, and then reduces the estimation of described remaining battery capacity at least in part based on the frequency of particular case of the relatively large pulse of transmitting described electric current.
4. medical system as claimed in claim 2, it is characterized in that, described processor is configured to, further at least in part based on the function of the initial charge of the number of times of the generation of the described particular case of the relatively large pulse of the described electric current of transmission, the quantity of electric charge used in the described relatively large pulse of electric current and described battery, calculate the estimation of described remaining battery capacity.
5. medical system as claimed in claim 4, it is characterized in that, described processor is configured to the initial charge being multiplied by charge ratio and the described battery used in the described relatively large pulse of electric current at least in part based on the number of times of generation of described particular case of the relatively large pulse of transmitting described electric current, calculates the estimation of described remaining battery capacity.
6. medical system as claimed in claim 2, is characterized in that, described processor is configured to the estimation regulating described remaining battery capacity at least in part based on the function of the described remaining battery capacity recorded in a period of time.
7. medical system as claimed in claim 6, it is characterized in that, described function is the average of the measurement of the multiple described remaining battery capacity obtained within described a period of time.
8. medical system as claimed in claim 2, is characterized in that, described measured battery parameter is cell output voltage.
9. estimate the method for the remaining battery capacity of the battery of implantable medical devices for one kind, described implantable medical devices be configured to use relatively low quantities electric current and in particular case, use the relatively large pulse of described electric current, described method employs processor, comprises the steps:
At least in part based on the generation of measured battery parameter with the described particular case of the relatively large pulse of the described electric current of transmission, calculate the estimation of described remaining battery capacity.
10. method as claimed in claim 9, it is characterized in that, described calculation procedure at least in part based on the frequency of described measured battery parameter with the described particular case of the described relatively large pulse of the described electric current of transmission, calculates the estimation of described remaining battery capacity further.
11. methods as claimed in claim 10, is characterized in that, described calculation procedure calculates the estimation of described remaining battery capacity at least in part based on described measured battery parameter, then described method comprises the steps: further
At least in part based on the frequency of the described particular case of the described relatively large pulse of the described electric current of transmission, reduce the described estimation of described remaining battery capacity.
12. methods as claimed in claim 10, it is characterized in that, the step of the described estimation of the described remaining battery capacity of described calculating is further at least in part based on the function of the initial charge of the number of times of the generation of the particular case of the described relatively large pulse of the described electric current of transmission, the quantity of electric charge used in the described relatively large pulse of electric current and described battery.
13. methods as claimed in claim 12, it is characterized in that, the step of the described estimation of the described remaining battery capacity of described calculating is multiplied by the described initial charge of charge ratio and the described battery used in the described relatively large pulse of electric current at least in part based on described frequency.
14. methods as claimed in claim 10, is characterized in that, comprise further, regulate the described estimation of described remaining battery capacity at least in part based on the function of the described remaining battery capacity recorded in a period of time.
15. methods as claimed in claim 14, is characterized in that, described function is the average of the measurement of the multiple described remaining battery capacity obtained within described a period of time.
CN201180033171.9A 2010-07-06 2011-06-13 Consider the cell durability estimation device of high current drain situation CN102971046B (en)
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PCT/US2011/040179 WO2012005880A1 (en) 2010-07-06 2011-06-13 Battery longevity estimator that accounts for episodes of high current drain
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2010-07-06 US US12/830,748 patent/US8452395B2/en active Active
2011-06-13 WO PCT/US2011/040179 patent/WO2012005880A1/en active Application Filing
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US20130226256A1 (en) 2013-08-29
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US8452395B2 (en) 2013-05-28
EP2590709A1 (en) 2013-05-15
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