Abstract:
A non-invasive device for determining the hemodynamic state of a subject. The device comprises: (a) at least two electrodes ( 20 ); (b) an electrical total body integral bioimpedance measuring unit (26) coupled to the electrodes; and (c) a data processing and analyzing unit ( 30 ) coupled to the electrical integral bioimpedance measuring unit and optionally to a display means ( 34 ) for calculating the cardiac output of the subject from the active component of the-integral bioimpedance. Also disclosed are methods for determining the hemodynamic state of a subject and for diagnosing a tendency of a subject to a cardiac disease.

Description:
FIELD OF THE INVENTION  
       [0001]     This invention relates to a non-invasive medical device for the determination of the hemodynamic state of a subject by use of parameters of cardiac and peripheral vascular performance.  
       BACKGROUND OF THE INVENTION  
       [0002]     The following references may be relevant to the understanding of the invention, and are referred to in the specification by number:  
         [0003]     1. Roul G, Moulichon M. E, Bareiss P, Gries P, Koegler A, Sacrez J, Germain P, Mossard J. M., Sacrez A,  Prognostic factors of chronic heart failure in NYHA class II or III: value of invasive exercise haemodynamic data . Eur Heart J (1995); 16:1387-98.  
         [0004]     2. Marmor A, Schneeweiss A.  Prognostic value of noninvasively obtained left ventricular contractile reserve in patients with severe heart failure . J Am Coll Cardiol (1997) February;29(2):422-8.  
         [0005]     3. Marmor A, Jain D, Cohen L S, Nevo E, Wackers F J, Zaret B L.  Left ventricular peak power during exercise: a noninvasive approach for assessment of contractile reserve . J Nucl Med (1993) November;34(11): 1877-85.  
         [0006]     4. Tan L B.  Cardiac pumping capability and prognosis in heart failure . Lancet (1986) 13(2):1360-63.  
         [0007]     5. Sharir T, Feldman M D, Haber H, Feldman A M, Marmor A, Becker L C, Kass D A.  Ventricular systolic assessment in patients with dilated cardiomyopathy by preload - adjusted maximal power—Validation and noninvasive application . Circulation (1994) May;89(5):2045-53.  
         [0008]     6. Tan L B.  Clinical and research implications of new concepts in the assessment of cardiac pumping performance in heart failure . Cardiovasc Res (1987) August;21(8):615-22.  
         [0009]     7. Cotter G, Metzkor E, Kaluski E, Faigenberg Z, Miller R, Simovitz A, Shaham O, Margithay D, Koren D, Blatt A, Moshkovitz Y, Zaidenstein R, Golik A.  Randomized trial of high - dose Isosorbide Dinitrate plus low - dose Furosamide versus high - dose Furosamide plus low - dose Isosorbide Dinitrate in severe pulmonary oedema . Lancet. (1998); 351: 389-93.  
         [0010]     8. Cotter G, Kaluski E, Blatt A, Milovanov O, Moshkovitz Y, Zaidenstein R, Salah A, Alon D, Mihovitz Y, Metzger M, Vered Z, Golik A.  L - NMMA  ( a Nitric Oxide Synthase Inhibitor )  is Effective in the Treatment of Cardiogenic Shock . Circulation. Mar. 28, 2000 ;101(12):1358-61.  
         [0011]     9. P. D. Sasieni,  Statistical Analysis of the performance of diagnostic tests  (Invited review), Cytopathology, 1999, 10,73-78.  
         [0012]     10. Jeroen G. Lijmer, Ben Willen Mol, Siem Heisterkamp, Gouke J. Bonsel, Martin H. Prins, Jan H. P., van der Meulen, Patrik M. M. Bossuyt.  Empirical Evidence of Design Related Bias in Studies of Diagnostic Tests , JAMA, 1999, 282,11,1061-1066.  
         [0013]     11. SAS/STAT User&#39;s Guide, Version 6, Fourth Edition. Volume 1, Cary, NC:SAS Institute Inc.,1989.  
         [0014]     12. Lange R A, Hillis L D.  Cardiac catheterization and hemodynamic assessment . In: Topol E J; Textbook of Cardiovacular Medicine.  
         [0015]     To date, no correlation has been found between invasive hemodynamic measurements and the clinical syndrome of patients with congestive heart failure (CHF) (1). In patients admitted with acute deterioration in cardiac function such as progressive dyspnea leading to pulmonary edema or cardiogenic shock, and even in patients with systolic chronic stable CHF, the measurement of cardiac index (CI) or systemic vascular resistance index (SVRi i ) has not provided any reliable diagnostic, therapeutic or prognostic value.  
         [0016]     SVR i  is a measure of the resistance of the vascular system to blood flow and is measured in Kg.*Me/sec 3  (=wood*M 2 ). In the cardiovascular system, SVR I =mean arterial blood pressure (MAP)−right arterial pressure)/CI. If not obtainable, right arterial pressure may be estimated as 10-15% of MAP.  
         [0017]     Cardiac power index (Cp i ) is a measure of the contractile state of the myocardium and is measured in watts/M 2 . The measurement of Cp i  is a newly introduced concept in cardiology (2-6). It is based on the physical law of fluids where 
 
Power=Flow×Pressure. 
 
         [0018]     In the cardiovascular system, Cp i  can be measured by replacing flow with cardiac index (CI) and pressure by the MAP.  
         [0019]     Therefore: 
 
 Cp   i   =CI×MAP.  
 
         [0020]     This measurement was partially used in the past (2-6) to evaluate the cardiac contractility of patients with CHF. It may be assumed that in patients with CHF, as Cp i  progressively decreases a compensatory increase of SVR i  occurs, and this increase is predictable within normal ranges. In addition, in patients with acute decrease in Cp i  this SVR i  response could be either (1) adequate—leading to a compensated or near compensated response, (2) excessive—leading to a significantly higher than required MAP increase, thereby leading to pulmonary edema, or (3) insufficient—leading to low MAP, inadequate perfusion of vital organs (brain, heart, kidneys) and cardiogenic shock.  
         [0021]     Israel Patent Application No. 135032, filed Mar. 13, 2000, and International Application No. PCT/IL01/00234, filed Mar. 12, 2001, describe a method for determining the hemodynamic state of a subject. The method comprises (a) determining the cardiac power index (Cpi) and systemic vascular resistance index (SVRi) values of a plurality of subjects who have been diagnosed as having a specified hemodynamic state; (b) determining the range of Cpi and SVRi paired values corresponding to each of the hemodynamic states; (c) determining the Cpi and SVRi paired value of the subject; (d) comparing the Cpi and SVRi paired value of the subject to the ranges of Cpi and SVRi paired values determined in step (b); and (e) determining the range of Cpi and SVRi paired values which is most similar to the Cpi and SVRi paired value of the subject. The hemodynamic state which corresponds to the range indicates the hemodynamic state of the subject. No dedicated apparatus is disclosed in that application.  
         [0022]     Thermodilution is a well-known invasive procedure for enabling a physician to determine the main hemodynamic parameters of the human body. The patients investigated are admitted to the Intensive Care Unit and have pulmonary artery catheters inserted. Ice cold saline solution is then used for the thermodilution measurements. This method is quite accurate, but it suffers from obvious disadvantages of an invasive procedure.  
         [0023]     Several non-invasive methods intended to substitute the invasive thermodilution procedure have been disclosed in the prior art. Two such modern non-invasive methods are widely known: one being based on echocardiographic measurements, and the other being the bioimpedance measurement method.  
         [0024]     An obvious requirement of non-invasive techniques is the correlation of their results with the readings obtained by the basic invasive method, such as thermodilution. It has been found that the echocardiographic measurements are technically unsatisfactory in many cases.  
         [0025]     Against this, bioimpedance measurements, performed by modern impedance cardiographs, show reasonable correlation coefficients with thermodilution—C. Jewkes at al. ( British Journal of Anaesthesia  1991; 67:788-794). The validity of impedance cardiography is an important issue because of its potential usefulness in intensive care medicine. Impedance cardiography can be used in the intensive care unit to monitor changes in hemodynamic parameters (e.g. Cardiac Output, Systemic Vascular Resistance, etc.), particularly in post-operative cardiac patients, as well as to gauge responses in these parameters to pharmacologic therapy.  
         [0026]     The bioelectric impedance of a living tissue or the whole body is the measurement of its opposition to an electric current passing therethrough between electrodes applied to the body. The impedance readings through the whole body are affected by the following three major components: 
        1. The base impedance (Zo) arising from the electrical characteristics of the fundamental materials which make up the tissues (mainly, the extracellular fluids).     2. The impedance change (δZ), synchronized with the cyclic cardiac activity. This component can be represented by a continuous curve, called the “rheogram”, representing the information concerning the cardiac activity.     3. The impedance waveform (δV), accompanying the changes of the air volume and redistribution of the blood volume caused by respiration.        
 
         [0030]     The combination of these three components can be represented by a curve, which is called the “plethysmogram”.  
         [0031]     The three main groups of hemodynamic parameters are reflected in the plethysmogram and can thus be calculated therefrom.  
         [0032]     Although electrical bioimpedance measurements have been studied for more than 30 years, it is only in recent years that clinical studies have documented the applicability of the bioimpedance measurements in the clinical setting.  
         [0033]     Two main types of the Electrical Bioimpedance Measurements (EBM) are known for measuring cardiac outputs: 
        Local (segmentary) EBM of the variations in the blood volume, provided on specific parts of the body; the technique for thoracic EBM was suggested by Kubicek W. G., et al. ( Biomedical Engineering,  1974, 9:410-416), and then modified by Sramek B. B., ( Med Elect.,  1982, April: 93-97) and Bernstein, D. P. ( Crit. Care Med.,  1986; 14:904-9); and     Integral EBM (EBM of the whole body), enveloping practically the entire blood conducting system; the technique is described by Tischenko, M. I., ( Sechenov Physiol. J. of the USSR,  1973; 49:1216-24). The whole body EBM technique is a priori more informative than the segmentary EBM; however, no realization thereof appropriate for reliable clinical use has been documented.        
 
         [0036]     It has been shown that in Segmentary EBM of the thorax where a low level current is applied to the thorax, changes in the volume and velocity of blood flow in the thoracic aorta result in detectable changes in thoracic conductivity. Kubicek et al. (supra) demonstrated that the first derivative of the oscillating component of thoracic bioimpedance (dZ/dt) is linearly related to aortic blood flow. Using this relationship, empirical formulas were developed to estimate Stroke Volume (SV), and then Cardiac Output (CO). (Francis G. Spinale at al:  Critical Care Medicine,  1990, Vol 18 No. 4, USA).  
         [0037]     A cardiograph, known as the Minnesota Impedance Cardiograph, was developed based on the Kubicek method but as reported by C. Jewkes at al. (supra) this device produced different correlation coefficients with the thermodilution technique, varying from good (r=0.97) to poor (r=0.41).  
         [0038]     U.S. Pat. No. Re: 30,101 (William Kubicek et al.) describes an Impedance Plethysmograph. Cardiac output is measured by connecting excitation electrodes at the upper and lower ends of the thorax of a patient, and connecting measuring electrodes to the thorax between the excitation electrodes. A constant fluctuating excitation current is applied to the excitation electrodes, and any changes in impedance within the thorax are measured, whilst simultaneously measuring the beginning and the end of a systole. Cardiac output is determined by measuring the maximum decreasing impedance slope during the systole.  
         [0039]     U.S. Pat. No. 4,450,527 (Bohumir Sramek), assigned to one of the leading companies in the field, BoMED® Medical Manufacturing Ltd., describes a non-invasive cardiac output monitor. The system disclosed there, where measurement of cardiac output is made by means of thoracic EBM, eliminates the effect of respiration from the thoracic impedance as a function of time, so as to provide continuously a signal of pulsatile thoracic impedance changes. The pulsatile thoracic impedance signal is processed to produce signals indicative of the ventricular ejection time and the maximum rate of change of the pulsatile thoracic impedance, is fed to a microprocessor in order to calculate the volume of blood pumped per stroke according to an improved systolic upstroke equation.  
         [0040]     BoMED® (Irvine, Calif.) continued its activity in the described field and offers several products. One of them is the BoMED® NCCOM3 where the band electrodes of the original Minnesota Impedance Cardiograph was replaced with pairs of standard ECG electrodes, which improved patients&#39; acceptance. It also has an integrated computer using a new algorithm based on the Bernstein-Sramek formula, which allows on-line calculation of Stroke Volume (SV) and Cardiac Output (CO) (C. Jewkes et al., Supra).  
         [0041]     The device is used to measure cardiac output (CO), stroke volume (SV), heart rate (HR), and basal impedance (Zo) or thoracic fluid index (TFI). Two “sensing” electrode pairs are placed on the thorax at the level of the mid-axillary line and on the lateral aspect of the neck. The other two pairs of the “current injecting” electrodes which deliver a 2.5 mA, 70 KHz current, are located 5 cm above the cervical, and below the thoracic sensing electrodes.  
         [0042]     The comparison of the EBM results, supplied by the BoMED® NCCOM3™, with the Thermodilution readings, have shown reasonable correlation coefficients.  
         [0043]     However, with respect to the BoMED® NCCOM3™ apparatus, it has been shown in several studies (C. Jewkes et al., supra; Francis G. Spinale, et al., supra; Kou Chu Huang et al.,  Critical Care Medicine,  1990, Vol 18, No.1 1), that: 
        the apparatus overestimates at low and underestimates at high values of cardiac output. In other words, there is no linearity in the measuring characteristics; and     the results seriously depend on the form, type and positioning of the electrodes.        
 
         [0046]     U.S. Pat. No. 4,807,638 (B. Sramek, assigned to BoMED®) discloses an improvement of the thoracic EBM of the U.S. Pat. No. 4,450,527. This monitor measures the electrical impedance across two segments of body tissue (thorax and legs) to provide a signal for each segment that indicates the increase in blood flow in the segment at the beginning of each cardiac cycle. The cardiac output of the patient is also measured and the cardiac index of the patient is calculated from the cardiac output.  
         [0047]     The electrodes, used in this monitor, are arranged on the two segments in the way described in the &#39;527 patent. It means that an unpredictable error will appear due to the positioning of each pair of the excitation and measuring electrodes and due to the distance between these pairs.  
         [0048]     An analysis of systems which implement Kubicek&#39;s and Sramek&#39;s method, reveals that they are not accurate for the following reasons: 
        1. Calculation of all the main “volume” hemodynamic parameters (Stroke volume, Cardiac output, etc.) is accomplished by using the derivative of the Impedance (dZ/dt), but not the measured change of the active bioimpedance component (δr), being the direct characteristics of the fluid volume.     2. Dispersion of the measuring current out of the measured segment into other parts of the body, causes errors in the measurement of stroke volume.     3. Geometry of the measured segment affects the results.     4. Errors occurring owing to the initial non-accurate electrodes&#39; placement on is the thorax, and their displacement caused by respiration.     5. Substantial calculation errors as a result of the fact, that dZ/dt is determined relative to the partial thoracic impedance, but not relatively to the whole body impedance.        
 
         [0054]     Moreover, these systems do not obtain and calculate parameters, characterizing the respiratory system.  
         [0055]     One of the more recent local EBM techniques which have been developed is described in U.S. Pat. No. 5,178,154 assigned to Sorba Medical Systems, Inc. There is disclosed an impedance cardiograph and method of operation thereof, utilizing peak aligned ensemble averaging which has a relatively high measurement accuracy.  
         [0056]     However, the Sorba system still suffers from several drawbacks. For one, the measurements are provided by a tetrapolar system of electrodes which is complex, inconvenient to the patient and results in artifacts.  
         [0057]     Second, the main parameter to be measured (Cardiac Stroke Volume) is computed by the Sorba system from a limited area section under a line of the mathematical derivative of the bioimpedance curve of a cardiac cycle. More particularly, this area reflects only the phase of the fast ejection of blood by the heart, and thus cannot reflect all specific processes of blood distribution taking place during a complete cardiocycle (and having an influence on the cardiac parameters). Furthermore, owing to the fact that the Sorba system involves the thoracic impedance measurements, signals characterizing cardiac activity are much weaker (10%) than carrier signals of respiratory cycles; however, the small cardiac activity signals in Sorba&#39;s system are thoroughly sorted out, averaged and processed, while the respiratory oscillations are considered as artifacts and are not analyzed. It is understood, that when using such an approach the respiratory parameters cannot be defined, and the accuracy of calculations of cardiac parameters may be difficult to achieve.  
         [0058]     Integral EBM is a priori more informative than the segmentary EBM; however, no realization thereof appropriate for broad clinical use has been achieved till date.  
         [0059]     The Integral EBM of the whole body was originally suggested by M. I. Tishcenko supra. This method includes applying electrodes in a manner so that the measuring current passes not through a segment, but rather through the whole body; injecting a low amplitude alternating current having a frequency of 30 KHz; measuring the whole body&#39;s impedance with an impedance plethysmograph having a measuring bridge; separation of the active component of the impedance by manual tuning, and using it for the subsequent calculations.  
         [0060]     The above integral EBM method enables the operator to obtain information, concerning the whole cardiovascular system of the body; the main hemodynamic parameters are obtained using different empiric equations derived by M. Tishcenko for the integral measurements. Owing to the larger length of the body, embraced by the electrodes, calculation errors can be minimized. The method uses a bipolar electrode system, which is simpler and less prone to error than the tetrapolar Kubicek&#39;s system used in the segmentary type EBM method.  
         [0061]     However, the system used by M. Tishcenko, needs to be calibrated before every measurement; it also requires tuning in order to exclude the reactive component of the impedance. The other problem is the error, caused by the reactive component, appearing between the electrodes and the skin at the place of their contact. This error is almost impossible to remove by tuning. The accuracy of the calculations completely depends on the manual adjustment, thus rendering the Tishcenko system unreliable.  
         [0062]     The formulae of Tishcenko for calculating cardiovascular parameters are corrected only by sex parameters. However, it has been documented that the whole body impedance and, in particular, its resistive component are influenced by many other parameters, such as Hematocrit, body composition, etc.  
         [0063]     U.S. Pat. Nos. 5,469,859 and 5,735,284, whose entire contents are incorporated herein by reference, disclose a method and a system for non-invasively determining at least one main cardiorespiratory parameter of an individual, such as the Stroke Volume, at least one parameter characterizing balance of the extracellular fluid in the body (such as the Index Balance), and for diagnostics of blood circulatory problems and/or failures of cardiac functions. The method for determining the main cardiorespiratory parameter comprises the steps of attaching at least two electrodes to the individual&#39;s body in a manner enabling to obtain electrical bioimpedance measurements of the whole individual&#39;s body, passing an alternating current with a stable and constant amplitude through the electrodes, measuring the integral bioimpedance as the result of the current flow; simultaneously separating an active component from the integral bioimpedance; calculating the cardiorespiratory parameter of the individual from the obtained active component, using an empiric formula applicable to integral bioimpedance measurements. The calculation is based on obtaining a number of values of the parameter for a number of cardiac cycles during a respiratory cycle, and computing an average of the cardiorespiratory parameter during a single respiratory cycle.  
         [0064]     Stress tests are known for diagnosing various cardiac diseases. Among the known types of stress tests are pharmacological, exercise and mental stress tests.  
       SUMMARY OF THE INVENTION  
       [0065]     It is an object of the present invention to provide a device which is capable of determining the hemodynamic state of a patient on the basis of bioimpedance measurements together with other data.  
         [0066]     It is a further object of the invention to provide a method based on a stress test for diagnosing a tendency towards a cardiac disease.  
         [0067]     In a first aspect of the invention, there is provided non-invasive device for determining the hemodynamic state of a subject comprising: 
        (a) at least two electrodes;     (b) electrical total body integral bioimpedance measuring unit coupled to the electrodes and including a high stability amplitude alternating current source and an electronic circuit for automatic derivation of an active component of said integral bioimpedance; and     (c) a data processing and analyzing unit coupled to the electrical integral bioimpedance measuring unit and optionally to a display means for calculating the cardiac output of said subject from the active component of the integral bioimpedance; and     (d) optionally, display means;     wherein said data processing and analyzing unit has a predetermined analyzer utility operable to calculate the cardiac index (CI) of said subject from the cardiac output (CO);     and wherein the mean arterial blood pressure (MAP) of said subject has been entered into said data processing and analyzing unit;     and wherein said data processing and analyzing unit has a predetermined analyzer utility operable to calculate the cardiac power index (Cp i ) of said subject according to the formula Cp i =CI*MAP, and to calculate the systemic vascular resistance index (SVR i ) of said subject according to the formula SVR i =n*MAP/CI, where n=0.85 to 0.95, thereby obtaining a Cp i  and SVR i  paired value for said subject;     and wherein said data processing and analyzing unit has a predetermined analyzer utility including a memory for storing a plurality of sets of Cp i  and SVR i  paired values, each set corresponding to a hemodynamic state selected from the group consisting of systolic congestive heart failure (sCHF), pulmonary edema (PE), cardiogenic shock (CS), vasodilative shock (VS) and normal state, said sets of Cp i  and SVR i  paired values originating from a plurality of subjects who have been previously diagnosed as having said hemodynamic states;     and wherein said data processing and analyzing unit has a predetermined analyzer utility operable to compare the Cpi and SVRi paired value of said subject to the sets of Cp i  and SVR i  paired values; and     wherein said data processing and analyzing unit has a predetermined analyzer utility operable to determine the set of Cpi and SVRi paired values which is most similar to the Cpi and SVRi paired value of said subject, the hemodynamic state corresponding to said set indicating the hemodynamic state of said subject.        
 
         [0078]     Preferably, n=0.9.  
         [0079]     In a preferred embodiment, the CO is calculated from the stroke volume (SV), which is calculated substantially according to the following equation:  
       SV   =         Hct     corr   .         K   ⁡     (     shape   *   sex   *   age     )         *   δ   ⁢           ⁢   r   ⁢           ⁢       H     corr   .     2     R     *       α   +   β     β     *   Ke1   *   Kw   *   IB         
 
 where: 
        Hct corr. is a correcting factor depending from hematocrit, being 145+0.35(Hct−40);     Hct is the hematocrit, obtained from analysis of the individual&#39;s blood;     K(shape*sex*age) is a coefficient of the individual&#39;s body, being: 
            527.3−(3.1*(Actual Age −20)), for men younger than 20 years old;     527.3, for men from 20 to 40 years old;     527.3+(3.1*(Actual Age −40)), for men older than 40 years old;     587.6−(2.9*(Actual Age −18)), for women younger than 18 years old;     587.6, for women from 18 to 50 years old;     587.6+(2.9*(Actual Age −50)), for women older than 50 years old;    
            δr is the amplitude value of the change of the individual&#39;s basic body resistance R at the anacrotic (systolic) portion of a cardiac cycle;     R is the individual average basic body resistance during one cardiac cycle;     H corr.  is a corrected height of the individual, given by:  
               H   corr     =         (       H   real     +   2     )     ⁢           ⁢   if   ⁢           ⁢       legs   ⁢           ⁢   length       body   ⁢           ⁢   length         =     0.66   ±   0.04                 or               H   corr     =         (       H   real     -   2     )     ⁢           ⁢   if   ⁢           ⁢       legs   ⁢           ⁢   length       body   ⁢           ⁢   length         =     0.54   ±   0.04                 or               H   corr     =         (     H   real     )     ⁢           ⁢   if   ⁢           ⁢   0.62     ≥       legs   ⁢           ⁢   length       body   ⁢           ⁢   length       ≥   0.58               
    α+β is duration of a cardiac cycle, being a sum of its anacrotic and catacrotic portion;     β is duration of the catacrotic portion of a cardiac cycle;     Kel is a coefficient depending on ion concentration in the individual&#39;s blood plasma, calculated based on the blood analysis and being given by: 
            a) for an individual exposed to a hemodialysis  
             Kel   =     sum   ⁢           ⁢   of   ⁢           ⁢   the   ⁢           ⁢   blood   ⁢           ⁢   concentrations   ⁢           ⁢   at                         ⁢           Na   +     +     K   +     +     Mg   +     +     Ca   +         142   +   13       ⁢   3               
    b) for other individuals  
         Kel   =     blood   ⁢           ⁢   concentration   ⁢           ⁢   of   ⁢           ⁢       Na   +     142         ;       
   
            K w  is a weight coefficient, being a ratio  
           Actual   ⁢           ⁢   weight       Ideal   ⁢           ⁢   weight       ,       
 
 where Ideal weight being obtained from International Tables of ideal weights; and 
    IB is an Index Balance, reflecting ratio between the measured volume of extracellular fluids and the individual&#39;s proper volume of extracellular fluids wherein the Index Balance is calculated based on the following formula:  
         R     ind   .           ⁢   prop         R   measured         
 
 where R measured is the measured resistive component of the individual&#39;s bioimpedance, not including the individual&#39;s skin resistance; R ind. prop.  is a proper value of the resistive component of the indivudual&#39;s bioimpedance being calculated according to the two following formulae:  
               0.42   ⁢           ⁢     H   2           0.47   ⁢           ⁢   W     -   8.30             for   ⁢           ⁢   men                 0.42   ⁢           ⁢     H   2           0.37   ⁢           ⁢   W     -   4.96             for   ⁢           ⁢   women             
 
 where H is the individual&#39;s height, and W is the individual&#39;s actual weight. 
       
 
         [0099]     It has now been surprisingly found that for a given patient, the values of the pair of parameters Cp i  and SVR i  are indicative of the hemodynamic state of the patient. In this specification, the term “paired values” will be used to indicate the Cp i  and SVR i  values of a given patient measured at essentially the same time.  
         [0100]     The device of the present invention enables the direct determination of the hemodynamic state of a patient by determining only two parameters, Cp i  and SVR i . These parameters are determined non-invasively by bioimpedance measurements, as described below. The obtained values are then compared by the data processing and analyzing unit of the device to a set of values previously compiled from patients with known hemodynamic states and stored in the device memory. The range of Cp i  and SVR i  paired values which is most similar to the Cp i  and SVR i  paired value of said subject will indicate in which group the subject should be classified. Similarity may be determined by the data processing and analyzing unit of the device by known statistical methods.  
         [0101]     The known hemodynamic states determined by the device of the invention are: (1) systolic or compensated CHF (sCHF). This group also includes hypertensive patients (HTN), due to their similar hemodynamic profile and small number in the study; (2) PE; (3) CS; (4) vasodilative or septic shock (VS); and (5) a group termed “normal” which represents patients who do not suffer from CHF. The last group consists of normal patients, i.e. with an SVR i  of approximately 15-35 wood*M 2  and a Cp i  above 190 watt/M 2 .  
         [0102]     The position of the patient&#39;s paired Cp i  and SVR i  values provides an indication as to how to treat the patient. For example, if the paired values are located in the range of values typical of cardiogenic shock, it would be advisable to administer to the patient a treatment which will boost vascular resistance (8). On the other hand, if the paired values are located in the range of values typical for pulmonary edema, it would be advisable to administer to the patient a treatment which will decrease vascular resistance (7).  
         [0103]     Changes in the condition of the patient, due either to the natural progression of the disease or to therapeutic treatment, may be easily monitored using the device of the invention by following the change in position of the paired Cp 1  and SVR i  values of the patient with respect to the predetermined set of values. In this way, the effectivity of a treatment may be assessed. Thus, the device of the invention may have significant therapeutic implications through pharmaceutical manipulation of SVRi by vasodilators (nitrates, endothelin antagonists) or vasoconstrictors (L-NMMA, vasopresin).  
         [0104]     A graph prepared by the device of the invention, also termed a “nomogram”, may appear, for example, on the display of a monitor, so that the measured Cp i  and SVR i  values of a patient can be automatically plotted by the device on the graph in order to determine the patient&#39;s “real time” condition.  
         [0105]     The device of the invention is based on the method, system and device disclosed in U.S. Pat. Nos. 5,469,859 and 5,735,284, whose entire contents are incorporated herein by reference. Briefly, the previously disclosed device is a measuring and analyzing unit that is applied to the patient by non-invasive electrodes for providing a continuous display of the amount of blood pumped into the circulation by the heart. This is measured in liters per minute, which is one of the most basic cardiovascular measures used.  
         [0106]     The previously disclosed method is based on measuring changes of the body&#39;s impedance to electrical current, this being termed bio-impedance. This method is particularly suitable for measuring changes in cardiac output, because the electrical impedance of the blood is lower than that of other constituents of the body.  
         [0107]     For example, to monitor cardiac output, a low-grade alternating electrical current (1.4 mA at 31 KHz) is continuously transmitted via two electrodes, one applied to the arm and one to the ankle. The same electrodes serve for transmission of the electricity and for sensing the body&#39;s impedance. The previously disclosed method provides the basic hemodynamic parameter—stroke volume (SV). With a knowledge of the heart rate (HR), the cardiac output may be computed using the known formula CO=SV*HR.  
         [0108]     In one embodiment of the invention, the device consists of a hardware set-up, configured either as a smart box attached to existing physiological monitors or as a stand-alone device with an optional liquid crystal display screen and user interface. The device uses algorithms to calculate a number of hemodynamic parameters, as disclosed in the aforementioned patents. The system can provide the following patient data on a continuous basis: 
        1. Stroke volume (including waveform tracing).     2. Stroke index (SV/body surface area).     3. Cardiac output (CO).     4. Cardiac index (CO/body surface area).     5. Heart rate.     6. Respiration rate (including waveform tracing).     7. Total peripheral resistance (mean Blood pressure/CO).        
 
         [0116]     To collect patient signals, the device uses electrodes that meet the specialized needs of the system, as disclosed in the aforementioned patents. In one embodiment, these electrodes are placed on the patient, arranged either wrist to wrist or wrist to ankle. In addition, a standard three lead ECG connection is made. The precise positioning of the electrodes is not critical and an untrained operator can make the attachments. The system automatically gives feedback to the user, to ensure that the electrodes are property attached.  
         [0117]     In order to obtain the SV and cardiac index (CI), the device requires the input of a number of patient parameters including height, weight, age, and sex. The device uses this data to calculate the body surface area (BSA). The device can then calculate the CI using the known formula CI=CO/BSA.  
         [0118]     Once this embodiment of the device is set-up, it may take one minute to make an initial reading, and then may automatically update all parameters every 20 seconds. In addition, a trend of Stroke Volume and CO may be displayed and updated every 20 seconds, to allow a user to clearly track changes over time.  
         [0119]     MAP may be measured independently and the data fed into the data is processing and analyzing unit of the device, or a blood pressure measuring unit may be integrated into the device.  
         [0120]     The display means or monitor is optional, and may be configured to display the hemodynamic state of the subject. Additionally, various hemodynamic parameters such as the Cp i  and SVR i  paired value of the subject and the HR, SV, CO and CI values may also be displayed.  
         [0121]     In a second aspect of the invention, there is provided a method for determining the hemodynamic state of a subject, comprising the steps of: 
        (a) attaching at least two electrodes to the subject&#39;s body in a manner ensuring a low impedance contact between the electrodes and the individual&#39;s skin, and positioning the electrodes so that current which passes between the at least two electrodes flows between at least one arm or at least one leg to at least another arm or at least another leg of the individual;     (b) passing an alternating current with a stable and constant amplitude through said at least two electrodes and at the same time, measuring the potential change as the result of the current flow, whereby an electrical bioimpedance measurement of the individual&#39;s body from the measured potential between the said at least two electrodes is obtained;     (c) simultaneously separating an active component from said integral bioimpedance;     (d) calculating the stroke volume (SV) of said subject from the active component of said integral bioimpedance, using a semi-empiric formula applicable to integral bioimpedance measurements, in such a manner so as to obtain a number of values of the SV for a number of cardiac cycles during a respiratory cycle, and calculating an average of the SV during a single respiratory cycle;     (e) calculating the cardiac output (CO) of said subject from the SV;     (f) calculating the cardiac index (CI) of said subject from the CO;     (g) calculating the cardiac power index (Cp i ) of said subject according to the formula Cp i =CI*mean arterial blood pressure (MAP), and to calculate the systemic vascular resistance index (SVR i ) of said subject according to the formula SVR i =n*MAP/CI, where n=0.85 to 0.95, thereby obtaining a Cp i  and SVR i  paired value for said subject;     (h) comparing the Cp i  and SVR i  paired value of said subject to a plurality of sets of Cp i  and SVR i  paired values, each set corresponding to a hemodynamic state selected from the group consisting of systolic congestive heart failure (sCHF), pulmonary edema (PE), cardiogenic shock (CS), vasodilative shock (VS) and normal state, said sets of Cp i  and SVR i  paired values originating from a plurality of subjects who have been previously diagnosed as having said hemodynamic states; and     (i) determining the set of Cp i  and SVR i  paired values which is most similar to the Cp i  and SVR i  paired value of said subject, the hemodynamic state corresponding to said set indicating the hemodynamic state of said subject.        
 
         [0131]     In a third aspect of the invention, there is provided a method for diagnosing a tendency of a subject to a cardiac disease comprising: 
        (a) measuring a first Cp i  and SVR i  paired value of said subject;     (b) performing a step of a stress test on said subject;     (c)measuring a second Cp i  and SVR i  paired value of said subject;     (d) optionally repeating steps (b) and (c) one or more times;     (e)comparing said first Cp i  and SVR i  paired value with said second and optional subsequent Cp i  and SVR i  paired values, wherein a decrease in Cp i  of &gt;15%, an increase in SVR i  of &gt;15% or an increase in Cp i  to &lt;400 wattiM 2  during stages 3 or 4 of said stress test indicates that said subject is prone to myocardial ischemia,     (f) and wherein if said first Cp i  is &lt;2.7 L./min/M 2  and said first SVR i  is &gt;35 wood/M 2  and said Cp i  increases to &lt;400 watt/M 2  without a subsequent decrease in Cp i  or an increase in SVR i  during stages 3 or 4 of is said stress test indicates that said subject is prone to systolic congestive heart failure (sCHF).        
 
         [0138]     Types of stress tests with which the method of the invention may be applied include pharmacological, exercise and mental stress tests. Drugs used in the pharmacological stress test include dobutamine, dipyridamole and adenosine. 
     
    
     BRIEF DESCRIPTION OF THE DRAWINGS  
       [0139]     In order to understand the invention and to see how it may be carried out in practice, a preferred embodiment will now be described, by way of non-limiting example only, with reference to the accompanying drawings, in which:  
         [0140]      FIG. 1  shows CI (litter/minute/M 2 ) in the six following diagnosed groups: CS, PE, HTN, sCHF, normal and VS;  
         [0141]      FIG. 2  shows Pulmonary Capillary wedge pressure (mmHg) in the 6 groups;  
         [0142]      FIG. 3  shows Cp i  (watt/M 2 ) in the 6 groups;  
         [0143]      FIG. 4  shows SVR i  (wood*M 2 ) in the 6 groups;  
         [0144]      FIG. 5  is a graph in which the Y-axis indicates Cp i  units (in watts/N 2 ) and the X-axis indicates SVR i  units (Wood*M 2  units). The graph (also termed in this specification a “nomogram”) is used for classification of the hemodynamic status of patients and may be constructed by a method of statistical analysis according to one embodiment of the invention. Normal patients are indicated by (Δ), PE patients are indicated by (?), CS patients are indicated by (ο), VS patients are indicated by (*) and sCHF and HTN patients are indicated by (●);  
         [0145]      FIG. 6  is a block diagram showing one embodiment of a device according to the invention; and  
         [0146]      FIG. 7  shows changes in Cp i  and SVR i  paired value of various subjects undergoing a stress test, displayed on the nomogram of  FIG. 5 . 
     
    
     DETAILED DESCRIPTION OF THE INVENTION  
     EXAMPLE 1  
     Determination of Hemodynamic State by Graphic Means  
       [0000]     Patients and Methods.  
         [0147]     Hemodynamic data was obtained in patients undergoing right heart catheterization.  
         [0000]     Inclusion Criteria:  
         [0148]     All patients who were diagnosed by conventional clinical criteria (see below) as having systolic CHF (sCHF), hypertensive crisis, acute pulmonary edema (PE), vasodilative shock (VS) or cardiogenic shock (CS) were included.  
         [0000]     Exclusion Criteria:  
         [0149]     Significant valvular disease, significant brady- or tachy-arrhythmias or renal failure (creatinine &gt;2.5 mg/dl).  
         [0000]     Clinical Diagnosis Criteria:  
         [0150]     1) Systolic CHF: Patients admitted for invasive hemodynamic assesment due to CHF exacerbation, defined as clinical symptoms and signs of CHF, NYHA class III-IV, accompanied by EF &lt;35% on echocardiography and not treated with any oral drugs for 6 hours or intravenous drugs for the last 2 hours; not fulfilling the criteria for cardiogenic shock or pulmonary edema.  
         [0151]     2) Pulmonary edema: patients admitted due to clinical symptoms and signs of acute pulmonary congestion accompanied by findings of lung edema on chest X-Ray and O 2  saturation &lt;90% on room air by pulse oxymetery during invasive measurements.  
         [0152]     3) Cardiogenic shock: Systolic blood pressure &lt;100 mmHg for at least one hour after percutaneous revascularization due to an acute major coronary syndrome not responsive to revascularization, mechanical ventilation, Intra-Aortic Balloon-Pump (IABP), IV fluids administration and dopamine of at least 10 μg/kg/min and accompanied by signs of end organ hypoperfusion but not accompanied by fever &gt;380 or a systemic inflammatory syndrome.  
         [0153]     4) Vasodilative shock: Systolic blood pressure &lt;100 mmHg accompanied by fever &gt;380, systemic inflammatory syndrome and signs of end organ hypoperfusion for at least 3 hours not responsive to IV fluids and IV dopamine of at least 10 μg/kg/min.  
         [0154]     5) Hypertension: MAP&gt;135 mmHg without signs of end-organ hypoperfusion, ischemia or pulmonary edema. These patients were included in the sCHF group.  
         [0000]     Hemodynamic Variables assesment:  
         [0155]     In all patients the hemodynamic variables were obtained during right heart catheterization using a Swan-Ganz cathteter placed under fluroscopic guidence. All measurments were obtained while patients were at least 30 seconds without LABP while on the same treatment used at the time the clinical diagnosis was made.  
         [0156]     CI was measured by thermodilution using the mean of at least 3 consecutive measurments within a range of &lt;15%. In Normal subjects, right heart catheterization was not performed due to ethical concerns. The values used in this cohort were obtained by standard non-invasive cuff blood pressure measurment and evaluation of CI by the FDA-approved NICaS 2001, a device according to the aforementioned U.S. patents (Cohen J A, Arnaudov D, Zabeeda D, Schlthes L, Lashinger J, Schachner A.  Non - invasive measurment of cardiac output during coronary artery bypass grafting . Eur. J. Card. Thoracic Surg. 1998; 14: 64-9). Therefore, wedge pressure was not assessed in normal subjects. Instead, we used standard values documented in the litterature (12).  
         [0000]     Hemodynamic Variables Calculation:  
         [0157]     Cp i  was determined as MAP×CI and SVR i  was determined as (MAP−right atrial pressure)/CI. As right atrial pressure was not measured in normal subjects, it was estimated to be 10% of MAP.  
         [0000]     Results:  
         [0158]     One hundred consecutive patients (56 patients with systolic CHF, 5 patients with HTN crisis, 11 patients with pulmonary edema, 17 patients with cardiogenic shock and 11 patients with vasodilative shock) and twenty healthy volunteers were enrolled in the study. The mean CI, wedge pressure, MAP, SVR i  and Cp i  according to clinical diagnosis are presented in Table 1 and as box-plots in  FIGS. 1-4 . Since the number of patients with hypertensive crisis (HTN) was too small to yield a statisticaly meaningful analysis, they were incorporated into the systolic CHF group for all further analysis.  
                                                           TABLE 1                           The means and standard deviations of various parameters in       the 5 diagnosis groups            GROUP   No. Obs.   Variable   Mean   Std. Dev.                    CHF   61   SVRiI   44.8666667   8.0327015               CPI   210.6833333   60.1848823               WEDGE   25.5166667   7.1556347               MAP   101.1833333   17.9806786               CI   2.0611667   0.3313153       Pulmonary   11   CVRI   88.1818182   16.7380894       Edema       CPI   182.2727273   57.3673965               WEDGE   32.7272727   8.6033820               MAP   131.3636364   12.6828445               CI   1.3727273   0.3196589       Normal   20   SVRiI   25.1500000   4.0817308               CPI   280.0000000   35.7402913               WEDGE   —   —               MAP   87.9000000   8.8549718               CI   3.2000000   0.3568871       Septic Shock   11   SVRiI   11.8181818   1.1241158               CPI   358.1818182   56.4921555               WEDGE   11.3636364   7.6976974               MAP   68.1818182   5.4372453               CI   5.2181818   0.5344496       Cardiogenic   17   SVRiI   55.6375000   31.0761833       Shock       CPI   98.9375000   34.9866046               WEDGE   23.3125000   6.5086481               MAP   72.1875000   11.2973079               CI   1.4218750   0.6426427                  
 
 Hemodynamic Variables: 
 
         [0159]     1) Cardiac Index (CI) ( FIG. 1 ): The mean values of CI were significantly lower in patients with systolic CHF, pulmonary edema and cardiogenic shock compared to normals and higher in patients with vasodilative shock. ROC analysis found the cut-off point of CI&lt;2.7 Lit./min./M 2  useful for the determination that a patient has any kind of heart failure (either systolic CHF, pulmonary edema or cardiogenic shock)(sensitivity=1, specificity0.99). However, values between 1.2-2.7 Lit./min./M 2  could be found in all patients with systolic CHF, 73% of patients with pulmonary edema and 47% of patients with cardiogenic shock. Moreover, the mean CI of patients in pulmonary edema and cardiogenic shock was found to be almost identical (1.4±0.4 vs 1.35±0.7 L/min/M 2 , p=ns).  
         [0160]     2) Mean Arterial Blood Pressure (MAP): As compared to normals, the mean values of MAP were significantly higher in patients with pulmonary edema and by definition, higher in patients with HTN crisis and lower in vasodilative and cardiogenic shock. Despite this, large areas of overlap were found regarding MAP measurments between pulmonary edema, systolic CHF and HTN crisis (MAP&gt;100 mmHg) and between systolic CHF, cardiogenic shock and vasodilative shock (MAP&lt;100 mmHg).  
         [0161]     3) Pulmonary capillary wedge pressure ( FIG. 2 ): As compared to normals, the mean wedge pressure was significantly higher in patients with systolic CHF and pulmonary edema and lower in patients with vasodilative shock. The analysis was based on the normal values for wedge pressure reported in the literature (&lt;12 mmHg (12)(p=0.001). However, the overlap of wedge pressure values among the groups was very extensive. Values between 12-38 mmHg were found in 82% of patients with systolic CHF, 64% of patients with pulmonary edema, 76% of patients with cardiogenic shock, and 18% of patients with vasodilative shock.  
         [0162]     4) Cardiac Power index ( FIG. 3 ): As compared to normals, the mean values of Cp i  were low in patients with systolic CHF and pulmonary edema, extremely low in patients with cardiogenic shock and high in patients with HTN crisis and vasodilative shock. However, some overlap was encountered among the 5 groups. Values of 200 to 300 Watt/M 2  were measured in 75% of normal people, 39% of patients with systolic CHF, 27% of patients with pulmonary edema, 18% of patients with vasodilative shock but none of the patients with cardiogenic shock (in whom Cpi was consistently below 170 Wat/M 2 .  
         [0163]     5) Systemic Vascular Resistence Index ( FIG. 4 ): As compared to normals, the mean values of SVR i  were significantly higher in patients with systolic CHF and HTN crisis, extremely high in patients with pulmonary edema and lower in patients with vasodilative shock. ROC analysis found the cut-off point of SVR i &lt;35 wood*M 2  to be useful in discriminating normal subjects from patients with any CHF syndrome (specificity=1, sensitivity=0.95). Also, SVR i  was found instrumental in the diagnosis of pulmonary edema: all patients with this clinical syndrome had SVR i &gt;67 wood*M 2  while SVR i  values in all other patients as well as normal subjects were significantly lower than this value.  
         [0000]     Cpi/SVRi graph ( FIG. 5 ):  
         [0164]     Distributions of SVR i  and Cp i  were highly skewed, whereas log(SVR i ) and Log(CP i ) were less skewed. Therefore, for further analysis only Log of the indices was used. However, the graph was constructed using values translated back from the Log values.  
         [0165]     The distributions of the two log-parameters were different between groups. However, neither of the individual parameters enabled separation among the five groups, as shown in Table 2.  
                                                                                                                               TABLE 2                           Number of Observations Classified into the Correct       Clinical Group Using Log(Cpi) or Log(SVRi) only.                By Clinical diagnosis                Cardio-                           By   genic   Systolic       Pulmonary   Septic       Parameters   Shock   CHF   Normal   Edema   Shock   Total                    (1) Classification using Log(CPi) only.            Cardiogenic   13   4   0   0   0   17       Shock       Systolic CHF   1   44   14   0   2   61       Normal   0   9   8   0   3   20       Pulmonary   1   9   1   0   0   11       Edema       Septic Shock   0   0   3   0   8   11            (2) Classification using Log(SVRi) only.            Cardiogenic   2   12   1   2   0   17       Shock       Systolic CHF   0   58   3   0   0   61       Normal   0   3   17   0   0   20       Pulmonary   2   0   0   9   0   11       Edema       Septic Shock   0   0   0   0   11   11                  
 
         [0166]     These data suggested that the separation may be obtained using two dimensional discriminant analysis. We used classical discriminant analysis for Normal distributions with unequal covariance matrices because the small numbers of observations in two groups prevented from using more flexible kernel functions.  
         [0167]     Due to large variability of variances of the parameters in the five groups, we could not suppose equal covariance matrices in the groups. (The test of homogeneity of within covariance matrices gives P&lt;0.0001).  
         [0000]     Classification using the Nomogram.  
         [0168]     In order to determine the state of a patient, his Cp i  and SVR i  are determined, and the paired values are plotted by the data processing and analyzing unit of the device on a graph, e.g.  FIG. 5 . The location of the measured paired values on the graph indicates which clinical condition may be assigned to the patient.  
         [0169]     The vascular response to decreased cardiac performance is crucial in determining the clinical syndrome of CHF. Insufficient SVRi increase may cause cardiogenic shock while excessive vasoconstriction will induce progressive pulmonary congestion resulting in frank pulmonary edema. The exact mechanism of deterioration of each patient can be determined using measurements of CI and MAP and a simple nomogram. This can have extensive therapeutic implication through pharmaceutical manipulation of SVRi. For example, ISDN can be used to move patients from PE to cCHF, and 1-NMMA can be used to move patients from cardiogenic shock.  
         [0170]      FIG. 6  illustrates the operation of one embodiment of the device of the invention. Electrodes  20  are applied to three of the extremities  22  of a subject  24 . The electrodes are connected to an electrical total body integral bioimpedance measurement unit  26 . Optionally, a blood pressure measuring unit  28  may be connected to one  29  of the extremities of the subject. The bioimpedance measurement unit and the blood pressure measuring unit generate signals representative of cardiorespiratory parameters and transmit them to a data processing and analyzing unit  30 , which processes the signals from these units and calculates the CI, and Cp i  and SVR i  paired value of the subject. The Cp i  and SVR i  paired values originating from a plurality of subjects who have been previously diagnosed as having the defined hemodynamic states may be stored in a memory  32  is which interacts with the data processing and analyzing unit  30 . The hemodynamic state of the subject may subsequently be displayed on a display monitor  34 , together with other hemodynamic values.  
       EXAMPLE II  
     Determination of Hemodynamic State using Statistical Analysis  
       [0171]     The manner in which the data processing and analyzing unit of the device may analyze and classify the paired value of the subject will be illustrated by means of the example given below. However, it will be clear to the skilled man of the art that other embodiments using other statistical methods of analysis are possible.  
         [0000]     1. Data  
         [0000]     Statistical Methods:  
         [0172]     The five clinical groups were compared with regard to all parameters using a one-way Analysis of Variance. The Ryan-Einot-Gabriel-Welsch Multiple Range Test was used for pair-wise comparisons between the groups, while Dunnett&#39;s T test was used to compare all groups to the healthy controls.  
         [0173]     A one-sample t-test was performed to compare mean Wedge pressure in each group to the wedge pressure of normal people (less than 12 mmHg).  
         [0174]     In order to determine the usefulness of the hemodynamic parameters to discriminate between the clinical syndromes, ROC curves, derived from a Logistic regression model were applied to the data to determine the best cutoff point of various parameters in terms of highest sensitivity and specificity.  
         [0000]     Cpi/SVRi Normogram:  
         [0175]     A classification rule was developed using second order discriminant analysis. Firstly both variables (CP i  and SVR i ) were transformed into Log scale for better approximation to normality. Since the number of patients with HTN was small, they were incorporated into the systolic CHF group. The classification used two steps. In the first step the rule separated three classes: Vasodilative shock, Cardiogenic shock and combined group, which includes Normal patients, systolic CHF and Pulmonary Edema (N-C-P). If after the first step the patient was defined as N-C-P, the second classification was used for separation among Normal, Systolic CHF and Pulmonary Edema subgroups.  
         [0176]     All calculations were performed by SAS 6.12 [SAS Institute Inc., Cary, N.C.] using procedures FREQ, MEANS, GLM, DISCRIM, GPLOT.  
         [0000]     2. Classification Rule.  
         [0000]     A. Classification using Calculations.  
         [0177]     Step 1. Calculate three values v 1 , v 2 , v 3  according to the formulas below. 
 
 v   1 = LCPi 2*21.54+2* LCPi*LSVRi* 10.61 +LSVRi 2*59.44- LCPi* 305.24- LS VRi* 417.70+1408.89 
 
 v   2 = LCPi   2 *10.12+2* LCPi*LSVRi* 5.67- LSVRi 2*4.99- LCPi* 135.81- LSVR i* 90.11+482.61 
 
 v   3 = LCPi 2*7.29 +LCPi*LSVRi* 2.57 +LSVRi 2*4.09- LCPi* 97.41- LSVRi* 58.22+368.16 
 
         [0178]     Classify the Patient 
        into the group ‘Vasodilative shock’, if v 1  is the smallest value     into the group ‘Cardiogenic Shock’, if v 2  is the smallest value     if v 3  is the smallest value go to step 2        
 
         [0182]     Step 2. Calculate three values v 4 , v 5 , v 6  according to the formula below. 
 
 v   4 = LCPi 2*6.45-2* LCPi*LSVRi* 0.45 +LSVRi 2*16.01- LCPi* 65.16- LSVRi* 116.53+391.67 
 
 v   5 = LCPi 2*17.75+2* LCPi*LSVRi* 26.56 +LSVRi 2*54.27- LCPi*  420.26- SVRi* 758.55+2775.78 
 
 v   6 = LCPi 2*32.95+2* LCPi*LSVRi* 3.09+ LSVRi 2*19.72- LCPi* 390.74- LS VRi* 161.49+1355.57 
 
         [0183]     Classify the Patient 
        into the group ‘Systolic CHF’, if v 4  is the smallest value among v 4 , v 5 , v 6  and LSVRi&lt;Log(67)     into the group ‘Pulmonary Edema’, if v 5  is the smallest value among v 4 , v 5 , v 6  and LSVRi&gt;Log(67)     into the group ‘Normal’, if v 6  is the smallest value among v 4 , v 5 , v 6         
 
         [0187]     The value of SVRi=67 was used to separate patients with systolic CHF from patients with pulmonary edema since the group of ‘pulmonary edema’ was rather small and by classifing these patients according to the usual rule we did not receive a separating line for Cpi measures &gt;250 Watt/M 2 . Therefore, the line of SVRi=67 wood*M 2  was used as an approximation of the classification results.  
         [0000]     3. Classification Results.  
         [0188]     The results of the application of the classification rule to the sample are presented in Table 3.  
                                                                                     TABLE 3                           Number of Observations Classified into the Correct       Clinical Group using both Log(SVR i ) and Log(CP i ).                By Clinical diagnosis                Cardio-                           By   genic   Systolic       Pulmonary   Septic       Parameters   Shock   CHF   Normal   Edema   Shock   Total                    Cardiogenic   15   2   0   0   0   17       Shock       Systolic CHF   0   60   1   0   0   61       Normal   0   0   20   0   0   20       Pulmonary   2   0   0   11   0   11       Edema       Septic Shock   0   0   0   0   11   11                  
 
 4. Performance of the Classification Rule. 
 
         [0189]     The performance of the diagnostic procedure with only two possible results and two classes of patients usually is expressed by using measures like positive (negative) predictive value (9) or diagnostic odds ratio(10). For more complex tests with many outcomes and many classes of patients the overall performance may be expressed through the difference between proportion of erroneously classified patients with and without using the test. This measure is usually called as Lambda assymmetric (R/C), where R (rows) is the true group and C (column) is a group where the patient was classified. For our data, Lambda (R/C)=0.95 (S.D.(Lambda)=0.03) which corresponds to the 3 errors of classification according to the classification rule, instead of 59 errors of classification according to the prior probabilities of the groups.  
       EXAMPLE III  
     Determination of Cardiac Power and Vascular Resistance for the Diagnosis of Heart Failure and Myocardial Ischemia  
       [0190]     The purpose of the present study was to determine the specificity and sensitivity of a Dobutamine stress test as a screening method for the diagnosis of congestive heart failure (CHF) or myocardial ischemia, using one embodiment of the device of the invention.  
         [0191]     Methods: The Dobutamine stress test was performed by the conventional protocol of the Dobutamine-Echocardiographic stress test. At baseline and at the end of each stage mean arterial blood pressure (MAP) and CI were non-invasively measured using the device of the invention. Cardiac contractility was estimated by the cardiac power index (Cp i ) which was calculated as CI*MAP. Systemic vascular resistence index (SVR i ) was calculated as MAP*0.9/CI.  
         [0192]     As illustrated in  FIG. 7 , the paired values of a normal subject would be expected to act as indicated by arrow 50. Criteria for the diagnosis of myocardial ischmia were: any decrease in Cp i  of&gt;15% or increase in SVR i  of &gt;15% or increase in Cp i  to &lt;400 watt/M 2  during stage 3 or 4 of dobutamine uptitration (arrow 54). Criteria for the diagnosis of CHF were CI&lt;2.7 L./min/M 2  and SVR i &gt;35 Wood/M 2  at baseline and a blunted increase in Cp i  (to &lt;400 watt/M 2 ) during stage 3 or 4 of dobutamine uptitration without a subsequent decrease in Cp i  or an increase in SVR i  (arrow 52).  
         [0193]     27 consecutive subjects were prospectively evaluated by both the Dobutanine-Echocardiographic and Dobutamine-stress test using the device of the invention. Clinical diagnoses by the Dobutanine-echocardiographic stress test evaluation were normal subjects (n=10), hypertension only (n=4), CHF without myocardial ischemia (n=7) and significant myocardial ischemia (n=6).  
         [0194]     Results: Dobutamine-stress test using the device of the invention showed 100% sensitivity and 80% specificity for determining that the subject suffers from either CHF or myocardial ischemia.  
         [0195]     Conclusion: Using the device of the invention in a stress test is a simple and accurate way of screening for CHF and myocardial ischemia.