to gain a clearer understanding of the lms process , it is believed expedient to illustrate its operation in a typical noise canceller application and , in this regard , reference is made to the block diagram of fig1 . an antenna 2 is illustrated as receiving simultaneously an information signal 4 and an additive noise component 6 which is typically altered in an unknown fashion between the noise source 8 and the output of receiver no . 2 which is identified by numeral 10 . at this point , it is not known which portion of the received signal is due to the superimposed noise . if an independent source of the noise is available as at the output of receiver no . 1 , identified by numeral 12 , that source may be used as the &# 34 ; input &# 34 ; to the lms adaptive filter 14 . the transfer function of the lms filter continuously adapts to furnish an &# 34 ; estimate &# 34 ; of the noise as registered at receiver 2 . the wave 16 is intended to illustrate the adaptation as time progresses . the noise - laden signal emanating from receiver no . 2 is represented by the waveform 18 and is applied as an input to a subtracter 20 . the second input to this subtracter is the &# 34 ; estimate &# 34 ; wave 16 and the resultant signal 22 appears on the &# 34 ; error &# 34 ; output line 24 . this &# 34 ; error &# 34 ; signal is fed back to the lms adaptive filter 14 and is used to adjust the weight parameters thereof until the &# 34 ; error &# 34 ; and the &# 34 ; input &# 34 ; signals are mutually uncorrelated and incoherent . at this point , the &# 34 ; error &# 34 ; signal then approximates the noise - free signal segments of the wave 22 . in applying the lms algorithm to the detection of p - waves in surface electrocardiograms , it is necessary that there be two distinct surface ecg channels such that one channel can be considered as the source of the signal observed on the other . the atria and the ventricles , acting as independent generators , transmit their respective signals to the chest wall . as shown in fig2 leads v 1 and v 5 are selected to provide the &# 34 ; input &# 34 ; and the &# 34 ; desired &# 34 ; operands to the lms filter . as mentioned above , both channels , v 1 and v 5 are driven by the cardiac atrial and ventricle equivalent dipoles which comprise linear summations of cellular action potential sequences , and , therefore , each contains both p and qrs energy . ideally , one would like to have an independent source of the interfering qrs signal , such as might be obtained using a ventricular catheter , but in practice , any two non - invasive surface ecg leads will suffice , providing there is a significant algebraic or vector difference in the p - wave versus the qrs wave between the two leads . thus , for example , if a / v disassociation exists or if there are significant differences in the p / qrs amplitude ratios or if significant differences in the p and the qrs phase properties prevail , then two surface contacting electrodes , containing the pqrst complex in contrasting form , can be used . as is set out in my aforereferenced co - pending application , the lms algorithm operates to cancel any energy which is coherent between the &# 34 ; input &# 34 ; signal and the &# 34 ; desired &# 34 ; signal , i . e ., the signals picked up by surface electrodes v 5 and v 1 , respectively . thus , any energy that is related by a linear transform between the two leads in question tends to be cancelled . when it is considered that the qrs complex represents a significantly greater amount of energy than does the p - wave , the adjustment of the tap weights of the lms adaptive filter is dominated by the qrs complex in just the ratio of qrs energy to p and t wave energy . the qrs complex is thus accommodated ( cancelled ). with the qrs energy substantially eliminated , the p - wave achieves greater prominence in the residue and , is therefore , more detectable . due to artifacts attributable to movement of the heart beneath the ribcage or motion of the electrodes on the surface of the body , a residual level of noise remains in the &# 34 ; error &# 34 ; output from the summing device 20 . this residual noise adds to the background noise against which the p - wave must be disconnected . however , by applying bandpass filtering to the error channel , further enhancement of the p - wave energy results . referring to fig2 and 3 , the method of the present invention comprises the steps of attaching suitable stabilized electrodes to two separate locoations on the patient &# 39 ; s chest wall which have been selected for certain p and qrs vector properties , i . e ., contrasting phase properties , contrasting amplitude properties or both . next , the electrical signals arising from the electrode pair are preprocessed by amplification and filtering . this filtering acts to eliminate aliasing in the a / d conversion by maintaining the signal bandwidth equal to or less than one - half the sampling rate chosen for the a / d conversion process . the amplifier gains are adjusted so that the analog signal is appropriately matched to the a / d converter employed . next , a subsequent and related filtering stage is imposed , whereby that portion of the qrs energy which is least uniform between channels is filtered out . this filtering may be implemented as an analog filter , and combined with the standard anti - aliasing filter which precede a / d conversion , or may be implemented as digital filters following a / d conversion . next , the amplified and filtered &# 34 ; input &# 34 ; and &# 34 ; desired &# 34 ; signals are applied as inputs to an analog - to - digital converter , as illustrated in fig3 and the thus digitized signals are supplied to a computer which has been preprogrammed with the lms algorithm . the memory of the microprocessor also holds certain control parameters appropriate to processing the digitized surface electrocardiogram signals . for example , the memory of the microprocessor store the number of tap weights assigned to the lms filter when it is functioning as a finite impulse response or &# 34 ; fir &# 34 ; filter . for the present application of detecting p - waves in surface ecg traces , the number of tap weights are chosen so that at the particular a / d sampling rate and for the particular bandwidth chosen for the prefiltering , the tap weights will just span the length or duration of the qrs portion of the overall cardiac pqrst complex . as an illustration , if the qrs complex is on the order of 50 milliseconds duration and the a / d converter is sampling the arriving &# 34 ; input &# 34 ; and &# 34 ; desired &# 34 ; signal channels at a 250 hz rate , there will be approximately 12 to 15 samples taken across the qrs segment . thus , anywhere from eight to thirty - two tap weights have been found sufficient for the assumed conditions . the other control parameter which primarily acts to control convergence is the factor , μ . as was explained in my aforereferenced co - pending and co - filed patent application , in the adaptive lms filter , the weight vector is updated in accordance with the formula , w k + 1 = w k + 2ρε k x k . thus , for appropriate update of the tap weight , the factor , μ , must be judiciously chosen . the appropriate value of mu relates to the magnitudes of the eigenvalues of the correlative matrix of the input signal in a way described by widrow and stearns . in general , values which are large on a scale from zero to one cause instability , while values close to zero lead to long convergence times . in that the software for implementing the lms algorithm has been explained in detail in the aforereferenced pending patent application , which has been incorporated herein by reference , nothing further need be said relative to it except to say that computer programmers or ordinary skill would be in a position to encode a list of instructions for carrying out the sum of the products computations called for by the lms algorithm . hence , it is deemed unnecessary to set out the lines machine code listings herein . under some circumstances , a high - frequency oscillation , or ringing , may appear in the &# 34 ; error &# 34 ; channel as part of the qrs residue . this is caused by a combination of the parameter mu , the eigenvalues of the input correlation matrix , and unequalized differences in the frequency distributions of the qrs in the &# 34 ; input &# 34 ; and &# 34 ; desired &# 34 ; leads . this oscillation , if not compensated at the lms input , may be filtered out of the &# 34 ; error &# 34 ; channel by traditional low pass filtering , leaving the p - wave detachable . once the qrs noise residue has been reduced , standard thresholding techniques can be used to identify the p - wave artifact and its time of occurrence in the ecg waveform . that is to say , a threshold may be set and if that threshold is exceeded , it is presumed that the signal involved is a p - wave and identification is completed . rather than merely employing linear thresholding , those skilled in the art of signal processing will recognize that more complex thresholding techniques incorporating a running average and standard deviation techniques can be used as well . referring to fig4 there are shown a series of vertically aligned signal traces showing signal amplitude versus time . the top waveform is a surface ecg signal obtained from electrode v 1 in fig2 and the one below it is the ecg signal picked up by surface electrode v 5 . the next waveform is a trace of the signal developed on the &# 34 ; estimate &# 34 ; channel and the bottommost wave shows the &# 34 ; error &# 34 ; output from the lms filter operation only amplified by a factor of 4 . comparing waves on channels 1 or 2 with the &# 34 ; error &# 34 ; wave on channel 4 reflects the substantial enhancement of the p - wave and corresponding suppression of the qrs complex . also , the fact that the qrs component is of a significantly higher frequency component allows subsequent filtering to further enhance the discrimination . this invention has been described herein in considerable detail in order to comply with the patent statutes and to provide those skilled in the art with the information needed to apply the novel principles and to construct and use such specialized components as are required . however , it is to be understood that the invention can be carried out by specifically different equipment and devices , and that various modifications , both as to equipment details and operating procedures , can be accomplished without departing from the scope of the invention itself . in particular , those skilled in the art will realize that the invention can not only be practiced using a programmed digital computer , but also can be implemented using special purpose digital logic devices ( hardware ).
a method and apparatus for reliably detecting the p - wave component in a surface electrocardiograph . an adaptive least means square filter is implemented in a programmed computer and the computer receives as its inputs a digitized version of the ecg waves picked up from two discrete locations on a subject &# 39 ; s chest wall . the lms adaptive filter functions to accommodate the energy component of the qrs complex thereby leaving the p - wave as the paramount signal component in the filter &# 39 ; s &# 34 ; error &# 34 ; output .