the present invention is similar to that disclosed in parant u . s . pat . no . 5 , 655 , 540 , ( from which priority derives ), with the exception that a single subject ecg cycle is utilized in analysis rather than a composite subject ecg cycle . in the following a specific embodiment of the present invention is presented much as it was in the earlier parent patent , and previous examples are provided . said specific embodiment assumes the use of an ( ecg ) system which utilizes frank ( ecg ) orthogonal x - y - z leads . it is to be understood , however , that the present invention is not limited to such and can be practiced with ( ecg ) systems in which any number of leads , ( eg . standard twelve ( 12 ), sixteen ( 16 ), or mapping arrays of twenty - four ( 24 ) or more etc . ), are present , and in which only some of the present leads are utilized . the following specific embodiment is presented as it is well documented and is presently the preferred embodiment . turning now to the drawings , there is shown in fig1 ( a ) a frontal view of a torso of a human , with ( ecg ) frank x and y leads properly affixed thereto . fig1 ( b ) shows a cross section taken at a — a in fig1 ( a ) with ( ecg ) frank z leads properly attached thereto . in use said ( ecg ) frank x - y - z leads are attached to an ( ecg ) system and serve to effect orthogonal monitoring of ( ecg ) full cardiac cycle pqrst signals which are essentially shaped as shown in fig2 . the present invention requires as a starting point that a significant data base be available , which significant data base contains representative composite ( ecg ) data for all , or some portion of full ( ecg ) pqrst cycles for each ( ecg ) lead , for a normal population . ( note , a normal population is defined as one in which the subjects have no detectable coronary artery disease ( cad ) by history and multiple conventional diagnostic tests , and are not at risk therefore based upon age , family history etc .) such a significant data base for normals was acquired by obtaining a number of full ( ecg ) pqrst cycles from each of the frank x - y - z ( ecg ) leads present in the presently discussed embodiment of the invention , from each of two - hundred - fifty ( 250 ) normals . ( it is noted that the present invention is not limited to cases in which all leads present in an ( ecg ) system are monitored but that a preferred embodiment does utilize all available information ). next , a random sample of one - hundred - forty - six ( 146 ) of said two - hundred - fifty ( 250 ) normals was selected and a representative number of the full ( ecg ) pqrst cycles from each , ( typically one - hundred ( 100 )), for each frank x - y - z ( ecg ) lead , were then selected and each subjected to a sampling procedure which provided some number of data points for each , ( six - hundred ( 600 ) was chosen in the presently discussed embodiment ). next , the sampled data points corresponding to the qrs depolarization complexes in each selected full ( ecg ) pqrst cycle were selected and a representative composite qrs complex for each frank ( ecg ) x - y and z leads formed therefrom by mathematical averaging thereof . said representative composite was then subjected to filtering and windowing techniques to provide a number of data sets for each of the frank ( ecg ) x - y - z leads . said data sets in the presently preferred embodiment of the present invention provide information present in said representative composite in the frequency bands : for each of the frank ( ecg ) x - y - z leads then , five ( 5 ) sets of data were derived as described , and from each of said sets of data a root - mean - square ( rms ) mean and ( rms ) standard deviation were calculated . this , it will be appreciated , resulted in fifteen ( 15 ) rms representative composite means and standard deviations being available , ( five for each frank ( ecg ) x - y - z lead ). in view of the described rms mean and rms standard deviations ( sd &# 39 ; s ) available clinical application of the present invention can be practiced . in prior practice data were obtained from a subject in a manner essentially the same as described infra for normals , but the present embodiment provides that a single ecg cycle be obtained and utilized . that is , a number of full ( ecg ) pqrst full cardiac cycles from each frank ( ecg ) x - y - z lead are obtained and a representative one selected and subjected to a sampling procedure . some portion of a selected full pqrst waveform is selected , ( eg . the qrs depolarization complex is utilized in the presently preferred embodiment of the present invention ), for each frank ( ecg ) system x - y - z lead . for said representative ( ecg ) cycle a rms mean is then calculated so that a table equivalent to that shown in fig3 but containing subject rms mean data , is formed . with the described normal rms mean and rms standard deviation data , and subject rms mean data then available , the algorithm of the method of the present invention can be applied to arrive at a diagnostic mathematical “ score ”. a . normal and subject rms means in view of normal rms standard deviation ; b . ratios of normal and subject rms frequency range and means to the summation of rms means for all frequency range bands for each frank ( ecg ) x - y - z lead in view of normal standard deviation for the numerator frequency band . c . ratios of normal and subject frank ( ecg ) x - y - z lead rms means in view of normal standard deviations of said ratios . briefly , application of each of the identified steps provides a numerical result ( pi ), which in general is typically not a whole integer . the next step is to process said numerical result ( pi ) by comparison to an assumed gaussian distribution derived from the normal population data to arrive at a whole number integer which represents how many rms standard deviations the subject rms mean is away from the normal rms mean , and assign a whole integer “ score ” component number ( si ) based thereupon . the algorithm then requires that a ninety - five ( 95 %) confidence interval , based upon normal rms standard deviation data be applied to determine if a “ score ” component should be accepted and included in calculation of a final “ score ”, said final “ score ” being arrived at by an addition of accepted “ score ” components . said algorithm will now be described in detail . the first step in applying the algorithm of the presently described presently preferred embodiment of the present invention is perform up to fifteen ( 15 ) calculations comprising subtracting the subject rms mean from a corresponding normal rms mean and dividing the result by a corresponding normal rms standard deviation for each frank ( ecg ) x - y - z lead in each frequency range identified infra , to provide numbers ( pi ). for all frequencies : (  subject   rms   mean  -  normal   rms   mean  ) normal   rms   standard   deviation = px1 = p1 for the frequency range band zero ( 0 ) to ten ( 10 hz ): (  subject   rms   mean  -  normal   rms   mean  ) normal   rms   standard   deviation = px2 = p2 for the frequency range band ten ( 10 ) to sixty ( 60 hz ): (  subject   rms   mean  -  normal   rms   mean  ) normal   rms   standard   deviation = px3 = p3 for the frequency range band sixty ( 60 ) to one - hundred - fifty ( 150 hz ): (  subject   rms   mean  -  normal   rms   mean  ) normal   rms   standard   deviation = px4 = p4 for the frequency range band one - hundred - fifty ( 150 hz ) to two - hundred - fifty ( 250 hz ): (  subject   rms   mean  -  normal   rms   mean  ) normal   rms   standard   deviation = px5 = p5 for all frequencies : (  subject   rms   mean  -  normal   rms   mean  ) normal   rms   standard   deviation = py1 = p6 for the frequency range band zero ( 0 ) to ten ( 10 hz ): (  subject   rms   mean  -  normal   rms   mean  ) normal   rms   standard   deviation = py2 = p7 for the frequency range band ten ( 10 ) to sixty ( 60 hz ): (  subject   rms   mean  -  normal   rms   mean  ) normal   rms   standard   deviation = py3 = p8 for the frequency range band sixty ( 60 ) to one - hundred - fifty ( 150 hz ): (  subject   rms   mean  -  normal   rms   mean  ) normal   rms   standard   deviation = py4 = p9 for the frequency range band one - hundred - fifty ( 150 hz ) to two - hundred - fifty ( 250 hz ): (  subject   rms   mean  -  normal   rms   mean  ) normal   rms   standard   deviation = py5 = p10 for the frank ( ecg ) z lead , ( ie . front to back axis ): ps for all frequencies : ( subject   rms   mean - normal   rms   mean ) normal   rms   standard   deviation = pz1 = p11 for the frequency range band zero ( 0 ) to ten ( 10 hz ): ( subject   rms   mean - normal   rms   mean ) normal   rms   standard   deviation = pz2 = p12 for the frequency range band ten ( 10 ) to sixty ( 60 hz ): ( subject   rms   mean - normal   rms   mean ) normal   rms   standard   deviation = pz3 = p13 for the frequency range band sixty ( 60 ) to one - hundred - fifty ( 150 hz ): ( subject   rms   mean - normal   rms   mean ) normal   rms   standard   deviation = pz4 = p14 for the frequency range band one - hundred - fifty ( 150 hz ) to two - hundred - fifty ( 250 hz ): ( subject   rms   mean - normal   rms   mean ) normal   rms   standard   deviation = pz5 = p15 twelve ( 12 ) additional groups of calculations are then performed in which the relative rms mean content of each frequency range band identified infra is determined as a percentage of the rms mean of the sum of the filter derived frequency range bands for each frank ( ecg ) system x - y - z system lead , for both subject and normal data , the differences therebetween being divided by the corresponding normal rms standard deviation to provide additional numbers ( pi ): define : ( 100 × subject   rms   ( 0  – 10   hz )   mean ) ( subject   rms   mean   ( 0  – 10   hz ) + ( 10  – 60   hz ) + ( 60  – 150   hz ) + ( 150  – 250   hz ) ) = sx0 ( 100 × normal   rms   ( 0  – 10   hz )   mean ) ( normal   rms   mean   ( 0  – 10   hz ) + ( 10  – 60   hz ) + ( 60  – 150   hz ) + ( 150  – 250   hz ) ) = nx0 define : ( 100 × subject   rms   ( 10  – 60   hz )   mean ) ( subject   rms   mean   ( 0  – 10   hz ) + ( 10  – 60   hz ) + ( 60  – 150   hz ) + ( 150  – 250   hz ) ) = sx1 ( 100 × normal   rms   ( 10  – 60   hz )   mean ) ( normal   rms   mean   ( 0  – 10   hz ) + ( 10  – 60   hz ) + ( 60  – 150   hz ) + ( 150  – 250   hz ) ) = nx1 define : ( 100 × subject   rms   ( 60  – 150   hz )   mean ) ( subject   rms   mean   ( 0  – 10   hz ) + ( 10  – 60   hz ) + ( 60  – 150   hz ) + ( 150  – 250   hz ) ) = sx2 ( 100 × normal   rms   ( 60  – 150   hz )   mean ) ( normal   rms   mean   ( 0  – 10   hz ) + ( 10  – 60   hz ) + ( 60  – 150   hz ) + ( 150  – 250   hz ) ) = nx2 define : ( 100 × subject   rms   ( 150  – 250   hz )   mean ) ( subject   rms   mean   ( 0  – 10   hz ) + ( 10  – 60   hz ) + ( 60  – 150   hz ) + ( 150  – 250   hz ) ) = sx3 ( 100 × normal   rms   ( 150  – 250   hz )   mean ) ( normal   rms   mean   ( 0  – 10   hz ) + ( 10  – 60   hz ) + ( 60  – 150   hz ) + ( 150  – 250   hz ) ) = nx3 define : ( 100 × subject   rms   ( 0  – 10   hz )   mean ) ( subject   rms   mean   ( 0  – 10   hz ) + ( 10  – 60   hz ) + ( 60  – 150   hz )  ( 150  – 250   hz ) ) = sy0 = sy0 ( 100 × normal   rms   ( 0  – 10   hz )   mean ) ( normal   rms   mean   ( 0  – 10   hz ) + ( 10  – 60   hz ) + ( 60  – 150   hz ) + ( 150  – 250   hz ) ) = ny0 define : ( 100 × subject   rms   ( 10  – 60   hz )   mean ) ( subject   rms   mean   ( 0  – 10   hz ) + ( 10  – 60   hz ) + ( 60  – 150   hz ) + ( 150  – 250   hz ) ) = sy1 ( 100 × normal   rms   ( 10  – 60   hz )   mean ) ( normal   rms   mean   ( 0  – 10   hz ) + ( 10  – 60   hz ) + ( 60  – 150   hz ) + ( 150  – 250   hz ) ) = ny1 define : ( 100 × subject   rms   ( 60  – 150   hz )   mean ) ( subject   rms   mean   ( 0  – 10   hz ) + ( 10  – 60   hz ) + ( 60  – 150   hz ) + ( 150  – 250   hz ) ) = sy2 ( 100 × normal   rms   ( 60  – 150   hz )   mean ) ( normal   rms   mean   ( 0  – 10   hz ) + ( 10  – 60   hz ) + ( 60  – 150   hz ) + ( 150  – 250   hz ) ) = ny2 define : ( 100 × subject   rms   ( 150  – 250   hz )   mean ) ( subject   rms   mean   ( 0  – 10   hz ) + ( 10  – 60   hz ) + ( 60  – 150   hz ) + ( 150  – 250   hz ) ) = sy3 ( 100 × normal   rms   ( 150  – 250   hz )   mean ) ( normal   rms   mean   ( 0  – 10   hz ) + ( 10  – 60   hz ) + ( 60  – 150   hz ) + ( 150  – 250   hz ) ) = ny3 define : ( 100 × subject   rms   ( 0  – 10   hz )   mean ) ( subject   rms   mean   ( 0  – 10   hz ) + ( 10  – 60   hz ) + ( 60  – 150   hz ) + ( 150  – 250   hz ) ) = sz0 ( 100 × normal   rms   ( 0  – 10   hz )   mean ) ( normal   rms   mean   ( 0  – 10   hz ) + ( 10  – 60   hz ) + ( 60  – 150   hz ) + ( 150  – 250   hz ) ) = nz0 define : ( 100 × subject   rms   ( 10  – 60   hz )   mean ) ( subject   rms   mean   ( 0  – 10   hz ) + ( 10  – 60   hz ) + ( 60  – 150   hz ) + ( 150  – 250   hz ) ) = sz1 ( 100 × normal   rms   ( 10  – 60   hz )   mean ) ( normal   rms   mean   ( 0  – 10   hz ) + ( 10  – 60   hz ) + ( 60  – 150   hz ) + ( 150  – 250   hz ) ) = nz1 define : ( 100 × subject   rms   ( 60  – 150   hz )   mean ) ( subject   rms   mean   ( 0  – 10   hz ) + ( 10  – 60   hz ) + ( 60  – 150   hz ) + ( 150  – 250   hz ) ) = sz2 ( 100 × normal   rms   ( 60  – 150   hz )   mean ) ( normal   rms   mean   ( 0  – 10   hz ) + ( 10  – 60   hz ) + ( 60  – 150   hz ) + ( 150  – 250   hz ) ) = nz2 define : ( 100 × subject   rms   ( 150  – 250   hz )   mean ) ( subject   rms   mean   ( 0  – 10   hz ) + ( 10  – 60   hz ) + ( 60  – 150   hz ) + ( 150  – 250   hz ) ) = sz3 ( 100 × normal   rms   ( 150  – 250   hz )   mean ) ( normal   rms   mean   ( 0  – 10   hz ) + ( 10  – 60   hz ) + ( 60  – 150   hz ) + ( 150  – 250   hz ) ) = nz3 three ( 3 ) additional calculations are then performed in which subject rms means of ratios of rms means obtained from the frank ( ecg ) x - y - z leads , are subtracted from corresponding rms means of ratios obtained similarly from normals , the results of which subtraction are then divided by rms standard deviations of normal corresponding rms ratios to provide additional numbers ( pi ): for the frank ( ecg ) x - y - z leads : subject   rms   ( x / y )   mean - normal   rms   ( x / y )   mean normal   standard   deviation   ( x / y ) = p  ( x / y ) = p28 subject   rms   ( y / z )   mean - normal   rms   ( z / y )   mean normal   standard   deviation   ( y / z ) = p  ( y / z ) = p29 subject   rms   ( x / z )   mean - normal   rms   ( x / z )   mean normal   standard   deviation   ( x / z ) = p  ( x / z ) = p30 continuing , each of the above up to thirty ( 30 ) calculated numbers : ( px 1 - p 1 , px 2 - p 2 , px 3 - p 3 , px 4 - p 4 , px 5 - p 5 , px 6 - p 6 px 7 - p 7 , px 8 - p 8 , px 9 - p 9 ), ( py 1 - p 10 , py 2 - p 11 , py 2 - p 11 , py 3 - p 12 , py 4 - p 14 , py 6 - p 15 , py 7 - p 16 , py 8 - p 17 , py 9 - p 18 ), ( pz 1 - p 19 , pz 2 - p 20 , pz 3 - p 21 , pz 4 - p 22 , pz 5 - p 23 , pz 6 - p 24 , pz 7 - p 25 , pz 8 - p 26 , pz 9 - p 27 ), p ( x / y - p 28 ), p ( y / z )- p 29 and p ( x / z )- p 30 ), ( generally identified as ( pi )), can optionally be compared to a corresponding assumed gaussian distribution of normal data to arrive at a “ score ” component number . if a number ( pi ) is within some +/− “ x ” rms standard deviation range of the rms mean as shown below , a “ score ” component number ( si ) is taken to be : if  - 1  x & lt ; ( pi ) & lt ; 1  x then si = 0 ; if  - 2  x & lt ; ( pi ) & lt ; - 1  x or if   1  x & lt ; ( pi ) & lt ; 2  x then si = 1 ; if  - 3  x & lt ; ( pi ) & lt ; - 2  x or if   2  x & lt ; ( pi ) & lt ; 3  x then si = 2 ; if  - 4  x & lt ; ( pi ) & lt ; - 3  x or if   3  x & lt ; ( pi ) & lt ; 4  x then si = 3   etc . continuing , each of this resulting “ score ” component ( pi ) or ( si ) calculated as just described is then subjected to a final test to determine if it should be accepted or rejected . said final test involves comparing the subject rms mean to the data from which the normal rms mean was calculated . if less than or equal to ninety - five ( 95 %) percent of the data points from which the normal rms mean was calculated are more than the subject &# 39 ; s rms mean the associated “ score ” component ( si ) is accepted , otherwise it is rejected . accepted “ score ” component numbers are then added to provide a final numerical “ score ”. it has been found that if said final numerical “ score ” is “ low ”, ( eg . approximately 0 to 7 ), then the subject involved is more likely to be normal . if the final numerical “ score ” is “ high ”, ( eg . greater than about 8 ), then the subject is more likely to be abnormal . a particularly relevant approach to presenting the results of applying the disclosed method of the present invention is demonstrated by fig5 . fig5 shows a plot in which the abscissa is ( 100 - specificity ) and the ordinate is ( sensitivity ). these terms are well known and mean : specificity = normals   with   negative   test all   normals   tested sensitivity = abnormal   with   positive   test all   abnormals   tested . the curve in fig5 is demonstrative of those which populations of subjects provide in an ( roc ) format . the present invention method provides that ( roc ) curves be prepared by associating a “ score ” value with the abscissa , in a nonlinear manner , and the percentage of a group having said “ score ” value with the ordinate of such a plot . the success of the present invention in identifying and distinguishing abnormal subjects has been demonstrated to be quite striking . fig8 and 9 , discussed supra , better serve to demonstrate this with actual empirically derived data . fig6 x 1 through 6 z 4 show twelve ( 12 ) diagrams , 6 x 1 , 6 x 2 , 6 x 3 , 6 x 4 , 6 y 1 , 6 y 2 , 6 y 3 , 6 y 4 , 6 z 1 , 6 z 2 , 6 z 3 and 6 z 4 , of subject time domain sample data recorded from frank x , y and z leads . higher frequency band data are presented as one progresses from fig6 x 1 to 6 x 4 , and from fig6 y 1 to 6 y 4 , and from fig6 z 1 to 6 z 4 . more particularly , fig6 x 1 , 6 y 1 and 6 z 1 show filtered composite subject ( ecg ) data set time domain waveforms obtained from x , y and z leads , respectively , of a frank ecg system in frequency band range of 0 . 0 - 10 hz . fig6 x 2 , 6 y 2 and 6 z 2 show filtered composite subject ( ecg ) data set time domain waveforms obtained from x , y and z leads , respectively , of a frank ecg system for the frequency band of 10 - 60 hz . fig6 x 3 , 6 y 3 and 6 z 3 show filtered composite subject ( ecg ) data set time domain waveforms obtained from x , y and z leads , respectively , of a frank ecg system for the frequency band of 60 - 150 hz . fig6 x 4 , 6 y 4 and 6 z 4 show filtered composite subject ( ecg ) data set time domain waveforms obtained from x , y and z leads , respectively , of a frank ecg system for the frequency band of 150 - 250 hz . it is noted that the plots for the 60 - 150 and 150 - 250 hz bands present as “ envelopes ” as signals go positive to negative and vice versa in very short time periods , ( ie . over a few “ sample numbers ”). all plots in fig6 x 1 - 6 z 4 have the ordinate marked in micro - volts , and the abscissa is marked in digital filter data points 0 to 600 , taken at progressive times during an ( ecg ) cycle . it is noted that fig6 y 2 and 6 y 4 show “ rhomboids ” present in the segment past the qrs complex region , ( ie . in channels 375 - 600 ). the rhomboids are shown as dashed - line to indicate that they were added to the actual patient data graph . this was done in preference to cluttering the disclosure with an additional page of drawings , however , the point to be made is that the presence of said “ rhomboids ” in at least one time domain , frequency band plot , and especially said presence in more than one such frequency band plot , is very indicative of a patient in danger of sudden death . fig7 a x 1 - 7 a z 5 show fifteen ( 15 ) diagrams of typical subject data in frequency domain power spectral density form , ( with magnitude on ordinate ), plotted as a function of frequency , ( on abscissa ). fig7 b x 1 - 7 b z 5 show fifteen ( 15 ) diagrams of typical subject data in time domain form , ( magnitude on ordinate ), plotted as a function of time , ( on abscissa ). all said identified plots provide magnitude , on the ordinate , in microvolts . more particularly , it is noted that fig7 a x 1 , 7 a y 1 and 7 a z 1 show subject composite ( ecg ) data set frequency domain power spectral density plots derived from x , y and z leads , respectively , of a frank ecg system , over a frequency band of 0 . 0 to 100 hz . fig7 a x 2 , 7 a y 2 and 7 a z 2 show subject composite ( ecg ) data set frequency domain power spectral density plots derived from x , y and z leads , respectively , of a frank ecg system , over a frequency band of 0 . 0 to 15 hz . fig7 a x 3 , 7 a y 3 and 7 a z 3 show subject composite ( ecg ) data set frequency domain power spectral density plots derived from x , y and z leads , respectively , of a frank ecg system , over a frequency band of 0 . 0 to 80 hz . fig7 a x 4 , 7 a y 4 and 7 a z 4 show subject composite ( ecg ) data set frequency domain power spectral density plots derived from x , y and z leads , respectively , of a frank ecg system , over a frequency band of 50 to 200 hz . fig7 a x 5 , 7 a y 5 and 7 a z 5 show subject composite ( ecg ) data set frequency domain power spectral density plots derived from x , y and z leads , respectively , of a frank ecg system , over a frequency band of 100 to 300 hz . all plots in fig7 a x 1 - 7 a z 4 have the ordinate marked in micro - volts , and the abscissa is marked in hz , ( ie . cycles per second ). as well , fig7 b x 1 , 7 b y 1 and 7 b z 1 show subject composite ( ecg ) data set time domain waveforms obtained from x , y and z leads , respectively , of a frank ecg system in an unfiltered full requisite frequency band . fig7 b x 2 , 7 b y 2 and 7 b z 2 show subject composite ( ecg ) data set time domain waveforms obtained from x , y and z leads , respectively , of a frank ecg system in a filtered frequency band range of 0 . 0 - 10 hz . fig7 b x 3 , 7 b y 3 and 7 b z 3 show subject composite ( ecg ) data set time domain waveforms obtained from x , y and z leads , respectively , of a frank ecg system in a filtered frequency band range of 10 - 60 hz . fig7 b x 4 , 7 b y 4 and 7 b z 4 show subject composite ( ecg ) data set time domain waveforms obtained from x , y and z leads , respectively , of a frank ecg system in a filtered frequency band range of 60 - 150 hz . fig7 b x 5 , 7 b y 5 and 7 b z 5 show subject composite ( ecg ) data set time domain waveforms obtained from x , y and z leads , respectively , of a frank ecg system in a filtered frequency band range of 150 - 250 hz . it is noted that the plots for the 60 - 150 and 150 - 250 hz bands present as “ envelopes ” as signals go positive to negative and vice versa in very short time periods , ( ie . over a few “ sample numbers ”). all plots in fig7 b x 1 - 7 b z 5 have the ordinate marked in micro - volts , and the abscissa is marked in digital filter sample number data points , taken at progressive times during a ( ecg ) cycle . the present invention the makes use of such visual aids as an added feature . the three curves in each plot represent normal mean and plus / minus one standard deviations , and subject data . it is also to be understood that the above described approach to diagnosis can be applied to tracking patients over time and can be applied before and after various stress tests which attempt to provoke otherwise indolent or silent coronary artery abnormalities . stress tests can , for example , involve treadmill exertion or a cold pressor test in which a subject simply places an arm into cold water for a few minutes . changes in “ score ” results combined with changes in the appearance of power spectral density ( psd ) and amplitude plots over time or before and after stress tests can provide insight as to a subject &# 39 ; s coronary health not made available by less vigerous testing . multiple mean curves can be simultaneously presented on a single plot to allow easy visual comparison of changes in power spectral density as a function of time or stress . observation of changes in ( psd ) plots in the various frequency bands is a correlated part of the method of the present invention . of particular interest , the inventor has noted that plots of ( psd ) in the frequency ranges of sixty ( 60 ) to one - hundred - fifty ( 150 ) hz and one - hundred - fifty ( 150 ) hz to two - hundred - fifty ( 250 ) hz show the greatest change in visually observable shape when a cold pressor test is administered . this is considered a significant observation . note also that as shown in fig7 a x 1 , it is common to include numerical representation in frequency as well as the time domain plots . four numbers can be present . using the power spectral density plot as an example , when present said numbers are representations of : upper left — the number of standard deviations a subject power spectral density value is away from a corresponding normal power spectral density value for the frequency band in the plot . lower left — the percentage of normals which are below the subject power spectral density value for the frequency band in the plot . upper right — the number of normalized , ( ie . subject power spectral density value in the frequency band of the plot divided by the sum of power spectral density values for all frequency bands ), standard deviations of subject power spectral value is away from a corresponding normalized subject power spectral density value for normals for the frequency band in the plot . lower right — the percentage of normals which are below the normalized subject power spectral density value for the frequency band in the plot . ( note that ( rms ) values can be substituted for power spectral density ). said numbers and visual plots aid in interpretation of a subject &# 39 ; s “ score ”. fig8 and 9 show ( roc ) plots for actual data arrived at using the present invention method . again , ( roc ) curves typically plot sensitivity vs . ( 100 - specificity ) on ordinate and abscissa respectively , presented as percentages . said plots in fig8 and 9 were generated by associating the present invention “ score ” with the abscissa ( 100 - specificity ), but with the zero ( 0 ) thereof being at the right side so that the “ score ” increases to the left . as the “ score ” increases the percentage of each group of subjects associated therewith is plotted on the ordinate . by observation of fig8 and 9 it will be appreciated that as the “ score ” increases the percentage of normals in a group of known normals having said “ score ” value drops off rapidly , but the percentage of known abnormals in a group of known abnormals drops off much more slowly . for instance , at a “ score ” of zero ( 0 ) all members of all groups are present . at a “ score ” of five ( 5 ) approximately eighty ( 80 %) percent of all members of an abnormal group will be present , but only approximately eleven ( 11 %) percent of normals are present . it is noted that a “ score ” scale along the abscissa will be nonlinear , when compared to the ( 100 - specificity ) scale . fig8 shows data presented in ( roc ) format for abnormals in various categories : for subjects known to have had a myocardial infarction ( mi ) shown by twelve ( 12 ) lead ( ecg ), identified as ( bemi ); for subjects with non - specific st - t wave abnormality on twelve ( 12 ) lead ( ecg ), identified as ( best ); for a subjects with normal twelve ( 12 ) lead ( ecg ) but awaiting surgery , identified as ( bnob ). for a test set of patients who have ( cad ), identified as ( btest ) and ( bgensia ). fig9 shows data plotted in fig8 plotted in a different format in which the abcissa is scaled in terms of the “ score ” developed by the present invention method . present is also a curve for normals data , identified as ( norm ). also included are curves for two groups additional groups of volunteer subjects which contain patients who have known risk factors for ( cad ) identified as ( bmaq ) and ( btnr ). these constitute a “ real - world ” population of what are considered normals , in that both normals and abnormals are present . as would be expected , the data for the ( bmaq ) and ( btnr ) groups is generally positioned between the data for the known abnormal ( btest ) and normal groups . the important thing to note is that the method of the present invention very definitely separates the various groups whether presented in the format of fig8 or fig9 . fig1 provides a flow chart representation of the primary focus of the preferred embodiment of the method of the present invention , said method comprising a noninvasive approach to investigating cardiac status of a subject , and enabling classification of a subject into normal and abnormal cardiac categories utilizing electrocardiography ( ecg ) data obtained therefrom . it has further been found by investigation of cami / 11 data base data for subjects known to be at risk for sudden death , that if dividing a present invention “ score ” for a patient , ( as provided by the described practice of the present invention ), by the ejection fraction , ( in percent ), of the patient , provides a result greater than one ( 1 . 0 ), then the patient involved is at high risk of sudden death . a visual presentation of the just described phenomona is quite striking , as is shown by in fig1 a and 11 b which show scatter - graphs demonstrating the relationship between said present invention : plotted against the present invention “ score ”, ( termed “ seecad ”™ score . (“ seecad ” is a trademark owned by r & amp ; s incorporated , a canadian corporation ). note , as shown in fig1 b , that a population of subjects not at risk for sudden death present with results wherein subject data “ scatter ” is closely confined about the line which begins at ( 0 . 0 , 0 . 0 ) and ends at ( 50 , 1 . 5 ); whereas a population which demonstrated sudden death presents with data which demonstrate a much larger range of scatter . in addition , and most importantly on an individual patient basis , note that no subject data in fig1 b exceed that value of 1 . 0 on the abscissa , whereas a large number of subjects shown in fig1 a provide data points above 1 . 0 . the bottom line conclusion to be appreciated is that should a subject present with a : value greater than 1 . 0 , said subject should be considered to definitely be a risk for sudden death . if said ratio is coupled with the presence of previously described “ rhomboids ” present following a qrs complex in time domain plots , ( see for instance demonstration in fig6 y 3 and 6 y 4 ), then the patient involved should be considered to be at very high risk for sudden death . this combination of present invention “ seecad ” score with other typically obtained cardiac data provides insight to the potential scope of application of the present invention . the definition of and availability of the described “ seecad ” score provided by practice of the present invention , has opened a whole new and very promising avenue in the area of subject evaluation . fig1 shows a three - dimensional presentation of data components utilized in computing a “ seecad ”™ score . fig1 is included to show that such a presentation indicates that patterns of : which data components were derived utilizing present invention methodology , can identify specific subject abnormality data patterns . it is emphasized that known efforts of previous researchers have had as a focus the diagnosis of subject abnormality by the comparison of : subject data to abnormal subject population data , and looking for a match . the present invention then has a new focus , emphasis added . again , the present invention focus is on comparing subject data to normal subject population data , and patterns of data components which naturally arise thereform are found to be indicative of specific categories of abnormality . the fact that the present invention approach , based in comparing subject data to normal subject population data , results in data patterns which serve to idicate a specific subject abnormality is a distinguishing factor of the present invention , and provides an extremely exciting area of continued development . it is projected that further work utilizing present invention non - invasively obtained “ seecad ” score data and methodology will provide the ability to not only separate abnormal from normal subjects , ( already possible ), but to further identify the most likely anatomical location of the source of identified abnormality , ( eg . specific myocardium , specific coronary - arteries etc ). fig1 shows a diagram of the basic components of a system which can be utilized to practice the present invention method . a partial human torso is shown with a chest mounted bioelectric interface ( bi ) thereon . ( note that equivalent limb electrodes ( ra ), ( la ) ( ll ) are present therein ). conventional individual limb and precordial ( ie . ( v 1 ), ( v 2 ), ( v 3 ), ( v 4 ), ( v 5 ) and ( v 6 )) leads can , of course , be utilized as well . it has been found , however , that use of a chest mountable bioelectric interface ( bi ), as shown , provides better ( ecg ) signals by maintaining relatively better electrode contact to a subject and relatively constant electrode spacing , in use . a cable ( c ) provides electrical signals from said electrodes ( ra ), ( la ), ( ll ), ( v 1 ), ( v 2 ), ( v 3 ), ( v 4 ), ( v 5 ) and ( v 6 ) to an ( ecg ) monitor ( ecg ), which feeds to a computational means ( computer ), which in turn provides seecad ™ data to a ( visual display ) and to a ( printer / plotter ). of course fig1 is only demonstrative and the present invention system is not limited to the configuration shown . it is to be understood that throughout this disclosure the rms mean values are cited . it is possible to utilize other calculated values , such as averages , in the method of the present invention . the term “ mean ” should be interpreted broadly to include such alternatives . the terms “ assumed gaussian ” have also been used throughtout this disclosure when refering to data distribution rms means and rms standard deviations . it is noted that in fact , analysis of empirically obtained data has proven the assumption to be valid . it is also to be understood that the term “ rhomboid ” is used herein only to generally identify the presence of ( ecg ) activity beyond the qrs complex as shown by dashed lines in fig6 y 3 and 6 y 4 , and does not impose any plot locus shape limitations . a print - out of major portions of the computer program utilized in the practice of the present invention was included in u . s . pat . no . 5 , 655 , 540 , said patent being incorporated herein by reference . the present invention practice is similar but does not require the combining of numerous subject ecg waveforms , in that it operates on a single ecg cycle . it is also disclosed that tracking of a subject can be continuous , and can utilize data obtained before and after , for instance : a suitable stress test ; intervention ( angioplasty etc . ); and / or medical therapy . of interest is the fact that signal magnitude in frequency domain plots , ( eg . 7 a x 1 - 7 a z 5 ), particularly in 60 - 150 and 150 - 250 hz ranges has routinely been noted to drop by thirty ( 30 %) percent or more upon subjecting patients who are prone to ischemia , to a cold - pressor test . it is also to be understood that the terminology “ coronary artery disease ” is used throughout this disclosure , the present invention serves to identify coronary disfunction generally , which can include myocardial poblems separate from coronary artery disease per se . finally , it is generally described herein that , for instance , as differences between normal subject population , and subject representative parameters increase , the “ score ” of the present invention increases . it would be a simple matter indeed to place a negative sign on the “ score ” and declare that it “ decreases ” when differences between normal subject population and subject representative parameters increase . it would further be a simple matter to utilize slightly different but substantially the same normal subject population , and subject data frequency bands , or select slightly different but substantially the same normal subject population , and subject data ( ecg ) cycle portions . as to attempt to draft definite claim language to overcome all such possibilities would be an impossible task in view of the complexity of the present invention subject matter , it is therefore to be understood that the doctrine of equivalent applies to , and the claims are to be interpreted to include all such contrived and substantially indifferent functional equivalents in the practice of the recited method of the present invention , emphasis added . having hereby disclosed the subject matter of the present invention , it should be obvious that many modifications , substitutions and variations of the present invention are possible in light of the teachings . it is therefore to be understood that the invention may be practiced other than as specifically described , and should be limited in breadth and scope only by the claims .
a method of analyzing experimentally derived electrocardiograph data , and system for practicing said method , which allow tracking of subject cardiac status change and which allow accurate catagorization of subjects into various abnormal and normal classifications is disclosed . the presently preferred embodiment applies an algorithm which compares representative parameter , mean ), values derived from analysis of a selected portion of a single cycle of an ecg pqrst waveform obtained from investigation of a subject , to similarly derived representative parameter , , values for a composite ecg waveform present in a compiled data bank derived from investigation of numerous subjects who were documented as normals , typically in each of a plurality of frequency range bands . a highly diagnostic numerical “ score ” is calculated by addition of “ score ” components found to be acceptable under certain mathematical criteria , and provided by the algorithm . visually interpretable time domain and power spectral density plots enhance the method . in addition , comparison of the calculated “ score ” to subject cardiac ejection fraction provides indication of risk for sudden death as does the presence of “ rhomboids ” following a qrs complex in frequency domain plots . the present method is directly adapted to tracking subject cardiac status change by substituting a baseline subject data set for the normal population data set . normal population data set .