there are a great many different implementations of the invention possible , too many to possibly describe herein . some possible implementations that are presently preferred are described below . it cannot be emphasized too strongly , however , that these are descriptions of implementations of the invention , and not descriptions of the invention , which is not limited to the detailed implementations described in this section but is described in broader terms in the claims . referring to fig2 , a rescuer uses an aed 10 to automatically monitor a victim during cardiac resuscitation . the aed 10 includes a speaker 16 , a display screen 18 , an analog to digital converter 20 , a processor 22 , and a defibrillator pulse generator 24 . the analog - to - digital converter 20 is connected to a set of ecg leads attached to the victim . the ecg leads monitor the electrical rhythms of the victim &# 39 ; s heart . the converter 20 sends the signals from the ecg leads to the processor 22 . the processor 22 monitors the victim &# 39 ; s heart for dangerous rhythms using the ecg signals while the victim is resuscitated using chest compressions techniques . if the aed 10 detects a dangerous heart rhythm , the aed 10 generates an alarm signal . the alarm signal is noticeable to the rescuer . the aed 10 can generate a defibrillating shock to the victim when the rescuer issues a command to the aed 10 . the defibrillating shock is intended to remedy the dangerous rhythm of the victim &# 39 ; s heart . the aed 10 uses a rhythm advisory method for a ) quantifying the frequency - domain features of the ecg signals ; b ) differentiating normal and abnormal ecg rhythms , such as vf ; c ) detecting the onset of abnormal ecg rhythms ; and d ) making decisions about the physiological states of the heart . this frequency - domain measure is reliable with or without the presence of the chest compression artifact in the ecg signals . the aed 10 , after identifying the current physiological state of the heart , can make a decision about appropriate therapeutic action for the rescuer to make and communicates the action to the rescuer using the speaker 16 and the display screen 18 . this rhythm advisory method can also be incorporated in an ecg rhythm classifier or a ventricular arrhythmia detector . the aed 10 may incorporate functionality for performing additional therapeutic actions such as chest compressions , ventilations , or delivery of intravenous solution containing metabolic or constitutive nutrients . based on the results of the analysis of the rhythm advisory method , the aed 10 may automatically deliver the appropriate therapy to the patient . the aed 10 may also be configured in “ advisory ” mode wherein the aed 10 will prompt the caregiver after the aed 10 has made a determination of the best therapy , and acknowledgement by the caregiver / device operator , in the form of a button press or voice - detected acknowledgement , is required before therapy is delivered to the patient . the aed 10 then analyzes the ecg signals to predict defibrillation success as well as to decide whether it is appropriate to defibrillate or to deliver an alternative therapy such as chest compressions , drugs such as epinephrine , constitutive nutrients such as glucose , or other electrical therapy such as pacing . in some examples , one or more therapeutic delivery devices 30 automatically deliver the appropriate therapy to the patient . the therapeutic delivery devices 30 are physically separate from the defibrillator aed 10 and control of the therapeutic delivery devices 30 may be accomplished by a communications link 32 . the communications link 32 may take the form of a cable connecting the devices 10 , 30 , but preferably the link 32 is via a wireless protocol such as bluetooth or a wireless network protocol such as institute of electrical and electronics engineers ( ieee ) 802 . 11 . bluetooth is a telecommunications industry specification that describes how mobile computing devices can be interconnected using a short - range wireless connection . the therapeutic delivery device 30 can be a portable chest compression device that is commercially available as the autopulse ™, provided by revivant of sunnyvale , calif . in other examples , the therapeutic delivery device 30 is a drug infusion device that is commercially available as the power infuser ™, provided by infusion dynamics of plymouth meeting , pa ., or the colleague cx ™, provided by baxter healthcare corp ., of round lake , ill . the therapeutic delivery device 30 can be a ventilator that is commercially available as the ivent ™, provided by versamed of pearl river , n . y . the therapeutic delivery device 30 can also include multiple therapies such as defibrillation , chest compression , ventilation and drug infusion . in other examples , control and coordination for the overall resuscitation event and the delivery of the various therapies may be accomplished by a device 34 or processing element external to the aed 10 , for instance the device 34 may download and process the ecg data from the aed 10 ; analyze the ecg signals , perform the determinations based on the analysis , and control the other therapeutic devices 30 , including the aed 10 . in other examples , the aed 10 may perform all the processing of the ecg , including analyzing the ecg signals , and transmit to the control device 34 only the final determination of the appropriate therapy , whereupon the control device 34 would perform the control actions on the other linked devices 30 . the control device 34 is commercially available as the autopulse ™, provided by revivant of sunnyvale calif . the chest compression artifact can be separated from the ecg signal components in the frequency domain . this makes it possible for the aed 10 to process the ecg signal without halting the processing during cpr chest compressions . the compression rate during cpr chest compressions recommended by american heart association ( 2000 ) is 100 per minute or 1 . 7 hz and the frequency range used for quantifying the frequency - domain features of the ecg signals can be set to be higher than that ( preferably but not limited to be 3 hz and up ) using a high pass frequency filter . the rhythm advisory method quantifies the energy distribution of the ecg signal in the frequency domain with a quantification method . the quantification result can be used to differentiate normal and dangerous ecg rhythms with or without the presence of the chest compression artifact . in one method , the aed 10 breaks up the frequency domain of the ecg signal into analysis frequency bands . the aed 10 then analyzes the different frequency bands for energy or variation over time to determine an appropriate treatment for the victim . in the preferred embodiment , the bands are 0 . 5 hz in width , though they may also be divided into unequal widths such that additional resolution is provided for frequency bands that are of greater importance in the analysis . for instance , frequencies less than 3 hz may be subdivided into only three equally spaced bands while the range from 3 - 5 hz may have 0 . 5 hz bands , and the range of 6 - 12 hz may have 0 . 25 hz bands . each band may be composed of an aggregation of multiple spectral measurements . for each band , characteristics of the distribution of spectral measurements within the band mayinclude such descriptors , e . g ., as mean spectral energy , spectral energy variance , median spectral energy , maximum spectral energy , minimum spectral energy . in one example of the analysis frequency bands , the aed 10 generates the frequency bands based on peaks in the frequency spectrum . thus , one frequency band corresponds to the frequency spread of a given peak in the frequency spectrum . there are common algorithms for identifying peaks in the frequency spectrum that include calculating slopes and energy at different points of the frequency spectrum . for each of these peaks , the aed 10 uses a non - linear parameter estimation algorithm or curve fitting algorithm to estimate the shape of the peak . from this spectral shape , the aed 10 calculates parameters about the peak . the quantification method differentiates various spectral patterns and shapes . the aed 10 makes a decision about the physiological state of the heart and suitable therapy based on the quantification results . the quantification method of the rhythm advisory method is a combination of measures from sub - methods . some of these sub - methods differentiate various spectral shapes , including but not limited to : ( 1 ) the number of peaks in the target frequency range , ( 2 ) the relative strength / peak value of various spectral peaks , ( 3 ) the relative bandwidth of various spectral peaks and ( 4 ) the variance of the energy distributed in a selected frequency range . one or more sub - methods can also measure change in the spectral information over time . these measures can be combined in a multi - dimension space to enhance both the sensitivity and specificity of the decision . one or more information processing techniques can be used to quantify the combination following the computation of these measures in order to make a decision based on the combination . the information processing techniques can include but are not limited to simple combining rules or math , neural networks , expert systems incorporating fuzzy or standard logic , or other artificial intelligence techniques . the additional measures can also include measurement of velocity or acceleration of chest compression during chest compressions according to the techniques taught by u . s . application ser . no . 10 / 704 , 366 , method and apparatus for enhancement of chest compressions during chest compressions , filed on nov . 6 , 2003 . the information processing techniques include simple combining rules or math , neural networks , expert systems incorporating fuzzy or standard logic , or other artificial intelligence techniques . these techniques make a decision based on the combination of measures about the physiological state of the heart and suitable therapy . the different measures are individual indications that have varying degrees of uncertainty about the physiological state of the heart and suitable therapy . in some examples , the information processing technique is trained automatically using software techniques known to those skilled in this art and a database of ecg rhythms that include outcome data . these examples include neural networks . in other examples , the information processing technique is generated manually based on observations of ecg patterns and outcomes . these examples include simple combining rules or math , and expert systems utilizing fuzzy or standard logic . in the example of expert systems utilizing standard logic , a programmer manually generates logical rules without uncertainty , the rules specifying preconditions such as “ if measure a recommends defibrillation ” and “ if measure b recommends defibrillation ”, and if these preconditions are met , the aed 10 automatically defibrillates the patient . in the example of expert systems utilizing fuzzy logic , the rules are more “ fuzzy ” and the states to be combined incorporate some degree of uncertainty based on human language . for instance , the fuzzy logic rules can incorporate such input as “ measure a detects a strong need for defibrillation ” versus “ measure a detects a weak need for defibrillation ”. the fuzzy logic framework combines the different measures and outputs results such as “ strong need for defibrillation ” or “ weak need for defibrillation ”. the method of making the decision about the physiological state is to choose from a group of possible states , each of which corresponds to a predetermined value range of the proposed measure . the possible states can include but are not limited to normal sinus rhythm , vf , shockable ( unstable ) vt , stable vt , supraventricular rhythm , and pulseless electrical activity . one possible sub - method for the quantification method is the variance of the energy distributed in a selected frequency range , or variance sub - method . two examples of energy - distribution patterns are shown in fig3 a and 3b . the frequency spectrum plots of fig3 a and 3b are calculated using a fast fourier transform ( fft ) of a signal over time . referring to fig3 a , the energy y 1 ( f ) of a frequency spectrum 50 is concentrated within a narrow frequency band and represents a pattern found in an arrhythmic state such as vf . referring to fig3 b , the energy y 2 ( f ) of a frequency spectrum 52 is distributed over a wide frequency range and represents a pattern found in a non - dangerous heart rhythm or normal sinus rhythm . the variance sub - method quantifies the features of the two frequency spectra 50 , 52 and thus the variance sub - method can differentiate between an arrhythmic state and normal sinus rhythm . one example of the variance sub - method calculates the variance of the energy from a reference frequency ( f ref ) of the spectrum . possible candidates of the reference frequency include but are not limited to the mean frequency , the median frequency , the center frequency , or the peak frequency of the spectrum . in this example , the variance sub - method computes the weighted distance of each frequency component from the reference frequency of the spectrum and thus quantifies the energy - distribution pattern . an example of this measure , the energy - frequency variance ( efv ) can be calculated with the following mathematical equation : however , the variance sub - method is not limited to this mathematical equation . measures that quantify the weighted or un - weighted distance of the frequency components from a reference frequency of the frequency spectrum can be used for this measure . referring to fig3 a , energy of the spectrum 50 is concentrated within a narrow frequency range and thus the spectrum has a relatively small efv value . referring to fig3 b , energy of the spectrum 52 is distributed over a relatively wider frequency range and the spectrum has a relatively larger efv value . thus , the efv value can be used to distinguish between a normal sinus rhythm and an arrhythmic sinus rhythm ( e . g ., vf ). referring to fig4 , a spectrum 100 of a piece of an ecg signal is a function of time . part 102 of the signal shows a vf rhythm during chest compressions . part 104 of the signal shows a vf rhythm without chest compressions . the vf is terminated by an electrical shock 106 , which is followed by a period of normal sinus rhythm ( nsr ). during this nsr period , part 108 has no chest compressions while part 110 has chest compressions . chest compression artifacts that are characterized by strong low - frequency ( below 3 hz ) components can be observed in the first 15 seconds ( part 102 ) and the last 10 seconds ( part 110 ) of this time - frequency plot 100 . during the time periods 102 and 104 that are associated with vf ( i . e . before the electrical shock 106 ), the energy distribution y ( f ) above 4 hz is clearly concentrated in a small frequency range , with or without the presence of the chest compression artifact . during the time periods 108 and 110 of nsr ( i . e . after the electrical shock 106 ), the energy distribution y ( f ) above 4 hz has a pattern that the energy is distributed over a wide frequency range , with or without the presence of the chest compression artifact . referring to fig5 , an efv score 152 is calculated from the signal 100 ( shown in fig4 ). a threshold 154 can be used to distinguish an arrhythmic rhythm from a normal sinus rhythm . thus , during the first 50 seconds ( parts 102 and 104 having vf rhythm ) of the signal 100 , the efv score 152 is below the threshold 154 . referring to fig6 , a variance sub - method 200 is implemented in the software and / or hardware of the aed 10 . the ecg data acquired by the front - end analog to digital converter 10 of the aed 10 is processed in a segment - by - segment manner . the number of segments to be processed before a decision is made is predetermined ( e . g ., 9 segments ). the length of a segment is preferably 2 seconds and each segment preferably has a 1 - second overlap with both the segment before and after itself , for the desired frequency and time - domain resolution . the segment - counter is set ( 202 ) to be zero when the processing starts and the first segment of the signal is acquired ( 204 ). a high - pass filter with a desired cutoff frequency ( preferably but not limited to be 0 . 5 hz ) is then applied ( 206 ) to remove the baseline drift . the frequency - domain representation of the filtered signal is acquired via a fast fourier transform ( fft ) ( 208 ). the spectral shape is quantified ( 210 ) using a preferred method . in an example , the efv score is calculated based on this frequency - domain representation and the frequency range for the efv calculation is selected such that the low - frequency part where the chest compression artifact dominates is excluded . the segment counter is increased ( 212 ) by one after the quantification of the spectral shape . if ( 214 ) all of the predetermined number of segments have been processed , the quantification results are processed ( 216 ) to get a final score ( including but not limited to the mean value of the efv scores ), otherwise the next segment of ecg signal is processed . in some implementations , the final score is an average of the scores from the segments . an estimate of the physiological state of the heart can be made based on the final efv score . if ( 218 ) the final score is below a predetermined threshold , an arrhythmic rhythm is estimated ( 220 ). using the variance sub - method , the aed 10 compares a threshold to the final efv score to determine if the victim is in an arrhythmic state . otherwise the processed signal is estimated to be normal . in one example , a preset threshold of 6 is used . in other examples , other preset thresholds can be used . an arrhythmic sinus rhythm can be detected using the variance sub - method . these arrhythmic sinus rhythms can be different types of rhythms with different appropriate therapies . it may be difficult to distinguish between arrhythmic rhythms that are shockable rhythms and unshockable rhythms using only the variance sub - method . for example , vts that are shockable ( rates exceeding 120 - 150 beats per minute [ bpm ]) may not be distinguishable from non - shockable vts (& lt ; 120 bpm ) solely with the measure from the variance sub - method . thus , the quantification method preferably enhances the variance sub - method with at least one other spectral measurement in determining the appropriate therapy for detected sinus rhythms . the quantification method may also make decisions based on changes in the spectral parameters over time . multiple measures may be thought of as forming a matrix , but actual implementations need not employ matrices . in some implementations , the aed 10 may combine the frequency of the largest amplitude spectral peak ( lasp ) in the frequency spectrum with the measure from the variance sub - method to create a 1 × 2 matrix . in some implementations , aed 10 may additionally calculate the number of spectral peaks in the frequency representation of the ecg signal with amplitudes of at least 25 % of the lasp using conventional methods known to those skilled in the art of signal processing and spectral analysis and include this measurement in the vector . a frequency of the lasp ( flasp ) of less than 2 hz and the number of peaks ( nop ) less than 3 indicates that it is a shockable vt or vf , while a flasp of greater than 2 hz and an nop of less than 3 indicates a non - shockable vt . non - shockable supraventricular rhythms can have a nop greater than 3 . in other implementations , the aed 10 can combine information from the variance sub - method and the flasp and nop measure , using information processing techniques described previously , to estimate the physiological state of the heart and suitable therapy . a combination of the efv under a threshold and flasp & lt ; 2 hz and nop & lt ; 3 can indicate a shockable vt or vf for which appropriate therapy can be defibrillation . a combination of the efv under a threshold and flasp & gt ; 2 hz and nop & lt ; 3 can indicate a non - shockable vt for which appropriate therapy can be normal cpr . a combination of the efv under a threshold and nop & gt ; 3 can indicate a supraventricular rhythm for which appropriate therapy can be simply monitoring the patient or drug therapy . a descriptor matrix may take the form of a [ n × m ] dimensional matrix , where n = the number of peaks and m = the number of parameters used to describe the spectral shape . in one implementation with m = 6 , the six parameters are the following : 1 ) the frequency of the particular peak ( fp ); 2 ) the amplitude of that peak ( ap ); 3 ) the width of the peak ( pw ); 4 ) the depth of the peak ( dp ); 5 ) the variance of that peak ( vp ); and 6 ) the first moment of that peak ( fm ). peak number ( pn ) is a digit providing an identifier for each individual peak . for instance , initially the aed 10 detects 5 peaks , each pn numbered sequentially with frequencies at 1 , 2 , 3 , 4 , and 5 hz . four seconds later in time , however , the aed 10 detects a peak at a new frequency of 4 . 5 hz and the peak is assigned a pn of 6 . the description matrix , which may be termed a spectral shape matrix ( ssm ), may include two header values , nop and a boolean value , gaussian peak ( gp ), which indicates that for spectral shapes that have a single peak ( nop = 1 ) and gp = true , that the spectral shape may be described by a parameter subset of only fp , ap , and vp . the ssm may preferably take the form : since fibrillation is a chaotic rhythm , the fp frequencies may vary at a rate faster than the time window of the short - time fourier transform . for instance , if the time window for computing the fourier transform to generate a frequency spectrum is set for 4 seconds , the fps for adjacent time windows ( and corresponding frequency spectrums ) will appear to jump from one frequency to the next . if , however , the aed 10 applies a standard short time fourier transform to the signal while at the same time increasing the rate at which a fourier transform is performed on the incoming data , the time window will be reduced and thus there will be a loss in the spectral resolution of the fourier transform . thus , in one example , the aed 10 simultaneously performs multiple fourier transforms on the ecg data with each subsequent transform initiated 400 milliseconds after initiation of the previous transform and a time window of 4 seconds , resulting in the aed performing 10 simultaneous transforms of data in a time window of 4 seconds . thus , the data for each transform has some overlap with data for adjacent transforms . in such a manner , the aed 10 maintains both spectral and time resolution . the aed 10 may calculate additional header values that describe generic aspects of the ecg spectrum . these additional header values may include , for instance , the amplitude spectrum area ( amsa ) as described in u . s . pat . no . 5 , 957 , 856 or the variance measure , as described previously . these values , along with nop and gp , can be thought of as forming a vector on which matrix operations and transformations may be performed independently of , or combined with , the matrix formed by the parameters for the individual peaks . the aed 10 can then perform matrix operations and transformations known to those skilled in the art on the ssm . the aed 10 can also calculate the ssm at regular intervals in time , to generate a [ n × m × p ] dimensional matrix , where p is the number of samples in the time interval of interest . each ssm may be thought of as a point in [ n , m ]- space that then forms a trajectory in the [ n , m , p ]- space . the aed 10 then analyzes this trajectory to predict defibrillation success as well as to decide whether it is appropriate to defibrillate or deliver an alternative therapy such as chest compressions , drugs such as epinephrine , constitutive nutrients such as glucose , or other electrical therapy such as pacing . the aed 10 may identify one or more peaks in the frequency spectrum . for each of these identified peaks , the aed 10 identifies a frequency band corresponding to the peak . the aed 10 may determine the peak model parameters , e . g . fp , ap , and pw , iteratively by a nonlinear parameter estimation or curve fitting routine for each peak &# 39 ; s frequency band . for example , the aed 10 may use the marquardt - levenberg algorithm to minimize the error in the nonlinear parameter estimation or chi - square , χ 2 , where χ 2 is expressed as follows . χ 2 ⁡ ( p ) = 1 n - p ⁢ ∑ i ⁢ [ m ⁡ ( i ) - s ⁡ ( i ; p ) m ⁡ ( i ) ] 2 . for this expression , there are n recorded energy values , m ( i ) are the recorded energy values , and s ( i ; p ) is the synthesized model curve energy values , sampled at points i in dependence on p varying parameter values . the term enclosed in brackets corresponds to the normalized residuals r ( i ), which provide a weighted measure of the difference between the fit curve and the data at each measured frequency value m ( i ). the aed 10 uses either the height - normalized lorentzian function , l ( e ), or the gaussian function , g ( e ) to model an energy function for each of the spectral peaks where e is a frequency . in the case of l ( e ): l ⁡ ( e ) = { 1 + [ e - e 0 β ] 2 } - 1 . g ⁡ ( e ) = exp ⁢ { - ln ⁢ ⁢ 2 · [ ( e - e 0 ) β ] 2 } . both functions l ( e ), g ( e ) are completely characterized by the peak parameters β , corresponding to ½ the peak width at half - maximum peak amplitude and e 0 , the peak position or fp . the aed 10 can model skew of the peak by combining the gaussian g ( e ) and lorentzian l ( e ), with β replaced by the term β + α ( e − e 0 ). the aed 10 can also add in a factor h to allow for varying peak heights . the result is function ƒ ( e ). the aed 10 calculates ƒ ( e ) as follows . some of the advantages of this product - type peak shape model ƒ ( e ) are the availability of analytical presentations of the partial derivatives of ƒ ( e ) with respect to the parameters , which are needed in the marquardt - levenberg algorithm to establish the jacobi matrix , the analytical value of β , and a faster convergence of the iterative estimation process . the depth of each peak is estimated either by incorporating a baseline curve into the marquardt - levenberg algorithm , or by simply determining the two minimum points of the spectrum for a region around the estimated peak . thus , using techniques known to one skilled in this art , the aed 10 can compute the spectral shape parameters of the peak : fp , ap , pw , dp , vp , and fm from the function ƒ ( e ). if the aed 10 finds a peak in the immediately subsequent time interval for which the ap and fp value does not vary by more than preferably 10 %, then that second peak is considered to have the same peak number , pn , indicating that it is the same peak with a shift in frequency and amplitude . in such a fashion , the aed 10 can develop trajectories for the parameters for each particular peak as well as for the overall descriptor matrix . the aed 10 can add a new peak at any time during the event , in which case the aed 10 gives the new peak a new pn value . if the aed 10 determines that a peak is extinguished , the pn number is maintained in memory of the aed 10 . in the processing of candidates for new peaks , the sub - method reviews all extinguished peaks to first determine if the new peak is actually an extinguished peak , in which case the candidate is not given a new pn , and instead is given the pn number of the extinguished peak . prior to a successful shock of a heart in a dangerous rhythm , one or more parameters ap , dp , vp , fp , pw of peaks in the 6 - 12 hz range of the frequency spectrum can oscillate with a cycle rate in the range of 0 . 1 - 1 hz . thus , detection of this oscillation through multiple time windows and frequency spectrums can be incorporated into the information processing technique as an additional sub - method that can recommend defibrillating the heart . furthermore , the sub - method can recommend timing the defibrillating shock when the peaks are at a maximum energy in the 0 . 1 - 1 hz cycle . for example , the sub - method can recommend timing the delivery of the defibrillation shock to occur during the 100 millisecond fourier transform cycle when the aps in the 6 - 12 hz region are at a maximum . when the particular ap - maximum cycle has be found , the aed 10 waits to deliver the defibrillation shock until the aed 10 detects the peak of the waveform after it has been band pass - filtered with a center frequency of 7 hz . this sub - method synchronizes the shock with the elements of the ecg waveform that are most related to the normal sinus qrs . the parameters fp , ap , and pw of peaks in the 6 - 12 hz region may also undergo oscillations indicating a change in the state of the heart as shown in fig7 a and 7b , which depict the spectrum as measured at two points in time , separated by an interval of 4 seconds . for a heart that has been in fibrillation for a period of time , the ecg undergoes a gradual degradation in the values of the parameters fp , ap , and pw of peaks in the 6 - 12 hz region of the frequency spectrum . as described previously , suitable therapy for a heart that has been in fibrillation for a period time is to do chest compressions and then defibrillate . this degradation is measured over at least a 8 - 10 second interval . this is an additional sub - method for the information processing technique . for example , if the aed 10 detects the aps of at least two peaks in the 6 - 12 hz region of the frequency spectrum decreasing by at least 15 % over a 10 second interval , the sub - method recommends chest compressions and then defibrillation . if the circulation and metabolic substrate of the heart improve to the point that the heart is more likely to be able to recover from a defibrillation shock , changes in the parameters fp , ap , and pw of peaks in the 6 - 12 hz region of the frequency spectrum will provide precursors to changes in the ecg that might be seen in the time domain of the ecg signal , such as an increase in the amplitude of the ventricular fibrillation ecg ( often termed “ coarsening ” by medical practitioners ). if the aed 10 detects an increase in the parameters fp , ap , dp , vp or pw of peaks in the 6 - 12 hz region of the frequency spectrum , for instance as shown in fig7 b , a sub - method will recommend ceasing chest compressions or other current therapy and then defibrillation . the peak frequencies , fp , for the peaks in the 6 - 12 hz region of the frequency spectrum can vary over time less when the condition of the heart is improving and thus the heart can handle the shock of defibrillation . this may be due to the presence in the myocardial activations of more normal activity at low levels manifesting in harmonics of the sinus rhythm fundamental frequency . this variation in the peak frequencies may be measured as the ratio of the average change in frequency in the region of 6 - 12 hz with that of the fps in the frequency range of 3 - 6 hz or measured as an absolute change for fps in the range of 6 - 12 hz . this sub - method , upon detecting the variation in the peak frequencies , recommends defibrillation to the information processing technique . it is also possible for a sub - method to project the [ n × m × p ] trajectory of the ssm matrix onto a plane within the [ n × m ]- space and then analyze the form taken by the projection of the trajectory in the plane to determine the appropriate time to shock or the optimal treatment . the projection may include up to ( n + m ) variables of different weightings , though it preferably is a projection that is primarily along the vp axis of the [ n × m ]- space . in the plane projection , image mensuration algorithms are employed to evaluate the features of the two dimensional projection of the trajectory . the following are some of the preferred mensuration classes for which measurements are made by means known to those skilled in the art : area , centroid , circularity , clustering , compactness , maximum axis , minimum axis , and perimeter . for instance , the minimum axis may be determined as follows . the minimum axis of an object is formally defined as the axis of maximum inertia ( dispersion ) passing through the centroid . one method to calculate the minimum axis is to compute the eigenvalues and eigenvectors of the scatter matrix comprised of the coordinate points of the object . the eigenvector corresponding to the smallest eigenvalue is the minimum axis . another method is to fit an ellipse to the object perimeter . the projection may be calculated for a specific duration of time , for instance 10 seconds , resulting in a series of 2 - dimensional objects that are representations of the trajectory in time — so - called projection “ snap - shots ”. it then becomes possible to analyze trends in the time series of values in the mensuration classes for changes indicative of improving physiological conditions . for instance , an increased amplitude in vp oscillation during vf is indicative of an improving physiological state . in this case , the aed 10 would then provide feedback to the caregiver to continue performing the rescue operation as they have with an audible prompt such as , “ keep up the good work . the patient &# 39 ; s condition is improving .” other such mensuration classes that are of value to track over time are the maximum axis angle , the perimeter and compactness . methods such as the kalman filter may be used for the estimation and prediction of the trajectory . the kalman filter estimates a process by using a form of feedback control : the filter estimates the process state at some time and then obtains feedback in the form of ( noisy ) measurements . as such , the equations for the kalman filter fall into two groups : time update equations and measurement update equations . the time update equations are responsible for projecting forward ( in time ) the current state and error covariance estimates to obtain the a priori estimates for the next time step . the measurement update equations are responsible for the feedback — i . e . for incorporating a new measurement into the a priori estimate to obtain an improved a posteriori estimate . the time update equations can also be thought of as predictor equations , while the measurement update equations can be thought of as corrector equations . indeed the final estimation algorithm resembles that of a predictor - corrector algorithm for solving numerical problems . k k = p k − h t ( hp k − h t + r ) − 1 { circumflex over ( x )} k ={ circumflex over ( x )} k − + k k ( z k − h { circumflex over ( x )} k − ) the first task during the measurement update is to compute the kalman gain , k k , the next step is to actually measure the process to obtain , and then to generate an a posteriori state estimate by incorporating the measurement , z k . the final step is to obtain an a posteriori error covariance estimate , p k . after each time and measurement update pair , the process is repeated with the previous a posteriori estimates used to project or predict the new a priori estimates . this recursive nature is one of the very appealing features of the kalman filter — it makes practical implementations much more feasible than ( for example ) an implementation of a wiener filter which is designed to operate on all of the data directly for each estimate . the kalman filter instead recursively conditions the current estimate on all of the past measurements . the equation , { circumflex over ( x )} k ={ circumflex over ( x )} k − + k k ( z k − h { circumflex over ( x )} k − ) one of the primary limitations of the kalman filter is that it only models a linear system with gaussian distribution , not often encountered in the physiological setting . the best known algorithm to solve the problem of non - gaussian , nonlinear filtering is the extended kalman filter ( ekf ). this filter is based upon the principle of linearizing the measurements and evolution models using taylor series expansions . the series approximations in the ekf algorithm can , however , lead to poor representations of the nonlinear functions and probability distributions of interest . as a result , this filter can diverge . based on the hypothesis that it is easier to approximate a gaussian distribution than it is to approximate arbitrary nonlinear functions other researchers have developed a filter termed the unscented kalman filter ( ukf ). it has been shown that the ukf leads to more accurate results than the ekf and that in particular it generates much better estimates of the covariance of the states ( the ekf often seems to underestimate this quantity ). the ukf has , however , the limitation that it does not apply to general non - gaussian distributions as is often the case with the ecg spectral distributions . sequential monte carlo methods , also known as particle filters overcome this limitation and allow for a complete representation of the posterior distribution of the states , so that any statistical estimates , such as the mean , modes , kurtosis and variance , can be easily computed . particle filters can therefore , deal with any nonlinearities or distributions . particle filters rely on importance sampling and , as a result , require the design of proposal distributions that can approximate the posterior distribution reasonably well . in general , it is hard to design such proposals . the most common strategy is to sample from the probabilistic model of the states evolution ( transition prior ). this strategy can , however , fail if the new measurements appear in the tail of the prior or if the likelihood is too peaked in comparison to the prior . in the preferred implementation , a estimator / predictor trajectory tracking technique known as the unscented particle filter ( upf ) as developed by merwe , doucet , freitasz and wan . pseudocode for the upf is as follows : for i = 1 , . . . n , draw states ( particles ) x 0 ( i ) from the prior p ( x 0 ) and set , for i = 1 , . . . n : update particles with the ukf : calculate sigma points : for i = 1 , . . . n , evaluate the importance weights up to a normalizing constant : c ) output : the output of the algorithm is a set of samples that can be used to approximate the posterior distribution as follows : e ⁡ ( g i ⁡ ( x 0 : i ) ) = ∫ g i ⁡ ( x 0 : i ) ⁢ p ⁡ ( x 0 : i | y 1 : i ) ⁢ ⅆ x 0 : i ≈ 1 n ⁢ ∑ i = 1 n ⁢ g i ⁡ ( x 0 : i ( i ) ) for some function of interest , g t , for instance the marginal conditional mean or the marginal conditional covariance or other moment . in one implementation the prediction matrix may be used to anticipate the optimal therapeutic intervention . rather than wait for the characteristics of the parameters or trajectory to achieve a certain condition , the algorithm will base its output on the predicted future state of the patient using the tracking and prediction algorithms mentioned above . transform methods other than the fourier method may be employed , for instance the laplace , hilbert , radon , and hankel transforms , as well as time frequency transforms such as the gabor short time fourier transform and the wavelet transform . other data besides ecg data may be included as part of the description matrix and incorporated into the analysis algorithm , for instance pulse oximetry , capnography , respiration , impedance cardiography and blood pressure measurements . at least some of the data may remain in the time domain without any fourier or other transform method being performed on it . pulse oximetry , impedance cardiography , and blood pressure measurements may be used to augment the ecg to determine if a pulse is present . capnography may be used to determine the overall effectiveness of cardiopulmonary resuscitation . large (˜ 5 ″ in diameter ), self - adhesive electrode pads are typically used to deliver defibrillation therapy to patients . the pads also provide ecg monitoring through the same conductive surfaces . in one implementation , additional small (˜ 0 . 5 ″ diameter ) ecg electrodes are integrated into the large pads that provide simultaneous monitoring of at least one additional electrical vector that is approximately orthogonal to the monitoring vector produced by the large defib / monitoring electrodes . a second matrix is then formed , identical in structure to the original ssm , but based on the orthogonal leads . the aed 10 can then perform techniques such as cross correlation on the two matrices to verify state changes . in one embodiment , the two small ecg electrodes and large pads are configured such that there at least two mutually orthogonal ecg leads are generated . the vector sum of these leads generates a trajectory over time . the same methods for trajectory analysis described above may be used to analyze this trajectory as well . as described previously , the aed 10 combines these sub - methods to determine appropriate therapy for the rescuer to perform on the victim . if uncertainty is included in the combination , the probability of defibrillation success is shown on the display of the device as a number between zero and one hundred , allowing the trained medical person such as a paramedic to make his own decision as to whether to shock the patient . in an implementation where the variance sub - method is used , the aed 10 may be configured such that the vf detection algorithm employing spectral variance may provide notification in the form of an audible or visual alarm indication that the paramedic should stop doing compressions for a more accurate analysis of the ecg waveform . in a more automated implementation , if the aed 10 determines that defibrillation has a low probability of success , the aed 10 may prompt the rescuer to perform cpr . during the course of cpr , the aed 10 may analyze the ecg continuously and prompt the rescuer to cease doing cpr when the aed 10 determines that the myocardium will be receptive to defibrillation . following the defibrillation , the aed 10 may prompt the rescuer to deliver uninterrupted chest compressions , and the aed 10 may again monitor the underlying ecg waveform during compressions for the appropriate time to deliver the defibrillation therapy . as a result of the spectral analysis , the aed 10 may also determine that neither defibrillation nor cpr is appropriate , but rather drug and metabolic therapy such as epinephrine and glucose is appropriate , in which case the aed 10 will prompt the rescuer to deliver the appropriate therapy . many other implementations of the invention other than those described above are within the invention , which is defined by the following claims .
a method of automatically determining which type of treatment is most appropriate for a cardiac arrest victim , the method comprising transforming one or more time domain electrocardiogram signals into a frequency domain representation comprising a plurality of discrete frequency bands , combining the discrete frequency bands into a plurality of analysis bands , wherein there are fewer analysis bands than discrete frequency bands , determining the content of the analysis bands , and determining the type of treatment based on the content of the analysis bands .