Laser Doppler flowmetry (LDF) has been applied widely in tissue microcirculation research. Annually, more than 100 studies using the method are published in the Russian literature and more than 500 studies, worldwide. The method is based on the optical probing of tissue and analysis of the signal scattered by moving blood cells, mainly erythrocytes, in a studied volume (1-2 mm 3 ). The LDF results are expressed in perfusion units (PU). The depth of probing in the skin is limited by the subpapillary plexus, in particular, small (terminal) arterioles and collecting venules. Tissue microcirculation is characterized by the microcirculation index (MI; in PU), which reflects the mean perfusion value in the given area. The MI depends on the average velocity of blood and erythrocyte concentration in a volume of tissue [1,2]. It has been estimated in in vitro experiments using polymer tubes with different diameters that the MI depends mainly on the blood cell velocity and less on the cell count [3].The main limitation of MI application in tissue perfusion research is an unstable linear correlation and differences from blood flow values assayed by other methods, in particular, with labeled microspheres. It has been demonstrated in experiments with rat skeletal muscles that the formula for vascular resistance R (mm Hg/PU)where P m is the mean arterial pressure, may fail to reflect true alterations of R [2]. Consequently, the skin vascular conduction parameter (SVCP, mm Hg/PU) estimated as SVCP = MI/ P m is not physiologically valid [4].Another limitation is that the MI characterizes the total microvascular perfusion rather than just the transcapillary nutritive flow. This restricts the application of LDF and makes interpretation of its results difficult in clinical physiological studies in humans.Microvascular blood flow is unstable and variable. LDF-accessible changes of erythrocyte flow are termed flux motions, flow motions, or oscillations. The contributions of particular regulatory mechanisms to the LDF pattern can be evaluated by computer spectral amplitude-frequency analysis. Each rhythm is characterized by frequency ( F , in Hz or oscillations per minute) and amplitude ( A , in PU) [1,5]. The frequency is more inert than the amplitude under external modulation. The genesis of very low frequency rhythms (0.095-0.02 Hz) is still unclear, but they are presumably related with endothelium secretion of nitric oxide [6]. Neurogenic rhythms (0.02-0.06 Hz) are caused by sympathetic adrenergic influences on myocytes of arterioles and arteriovenous anastomoses [5,7,8]; myogenic rhythms (0.06-0.15 Hz) are determined by the activity of myocytes of precapillary sphincters and precapillary metarterioles [5]. I previously suggested a method for separate evaluation of the neurogenic and myogenic tones, which are inversely proportional to the amplitudes of the neurogenic and myogenic rhythms in microvessels [8,9]. Respiratory and cardiac rhythms are synchroAbstract -Examination of 28 healthy subjects and 66 patients was performed usin...