referring now to fig1 the implantable cardiac stimulation device in accordance with this invention is shown as a dual sensor rate - responsive pacemaker 10 . it is well within the scope of this invention to operate this stimulation device in a demand mode as is well known within the art . while the preferred embodiment is directed towards a stimulation device which uses an activity sensor for determining the pacing rate , it is well within the scope of this invention to apply the principles of this invention for use with other physiologic sensors that measure metabolic demand . fig1 sets forth a simplified block diagram of the stimulation device 10 . the stimulation device 10 is coupled to a heart 5 by way of two leads 12 , 14 . the first lead 12 has at least one electrode 18 in contact with the atrium of the heart 5 , and the second lead 14 has at least one electrode 20 in contact with the ventricles of the heart 5 . the leads 12 , 14 are electrically and physically connected to the stimulation device 10 through a connector 16 which forms an integral part of the housing ( not shown ) in which the circuits of the stimulation device 10 are housed . the connector 16 electrically protects circuits within the stimulation device 10 via a protection network 17 from excessive shocks or voltages that could appear on electrodes 18 , 20 in the event with contact with a high voltage signal , e . g ., from a defibrillator shock . the leads 12 , 14 carry the stimulating pulses to the electrodes 18 , 20 from an atrial pulse generator 22 and a ventricular pulse generator 24 , respectively . further , the electrical signals from the atrium are carried from electrode 18 through the lead 12 to the input terminal of an atrial channel sense amplifier 26 . the electrical signals from the ventricle are carried from the electrode 20 through the lead 14 to the input terminal of the ventricular channel sense amplifier 28 . similarly , electrical signals from both the atrium and ventricle are applied to the inputs of the iegm ( intracardiac electrogram ) amplifier 30 . the stimulation device 10 detects an evoked response from the heart in response to an applied stimulus , allowing the detection of capture with a suitable broad bandpass filter . the iegm amplifier 30 is also used during transmission to the external programmer &# 39 ; s 60 state machine or other control logic . the stimulation device 10 is controlled by a controller 32 that typically includes a microprocessor to carrying out the control and timing functions . the controller 32 receives output signals from the atrial amplifier 26 , the ventricular amplifier 28 , and the iegm amplifier 30 over the signal lines 34 , 36 , 38 , respectively . the controller 32 also generates trigger signals that are sent to the atrial pulse generator 22 and the ventricular pulse generator 24 over the signal lines 40 , 42 , respectively . the stimulation device 10 also includes a memory circuit 48 that is coupled to a control system 32 over a suitable data / address bus 50 . this memory circuit 48 allows certain control parameters , used by the controller 32 in controlling the operation of the stimulation device 10 , to be stored and modified , as required , in order to customize the stimulation device &# 39 ; s operation to suit the needs of a particular patient . further , the data sensed by the iegm amplifier 30 during the operation of the stimulation device 10 may be stored in the memory circuit 48 for later retrieval and analysis . a clock circuit 52 directs appropriate clock signal ( s ) to the controller 32 as well as any other circuits throughout the stimulation device 10 , e . g ., to the memory circuit 48 , by the clock bus 54 . the stimulation device 10 also includes a telemetry communications circuit 56 which is connected to the controller 32 by way of a suitable command / data bus 58 . in turn , the telemetry circuit 56 is selectively coupled to an external programming device 60 by an appropriate communication link 62 such as any suitable electromagnetic link . advantageously , through the external programmer 60 and the communication link 62 , desired commands may be sent to the control system 32 . other data measured within or by the stimulation device 10 such as iegm data , etc . may be stored and uploaded to the programmer 60 . the stimulation device 10 additionally includes a battery 64 which provides operating power to all the circuits of the stimulation device 10 via a power signal line 66 . the stimulation device 10 also includes a sensor 68 that is connected to the controller 32 over a suitable connection line 72 . in the preferred embodiment , this sensor detects patient activity via an ac accelerometer , but could be any appropriate sensor which can indicate patient activity . attention is directed to &# 39 ; 483 for further examples of other suitable activity sensors . in addition , any sensor which indicates metabolic need over time could be used in place of the activity sensor . such sensors could be an oxygen saturation sensor , temperature sensor , etc . in the case of these alternative sensors , the sensor would be placed on the lead 14 as shown by alternative sensor 69 . the operation of the above described stimulation device 10 is similar to the conventional manner to provide pacing pulses at a rate that comfortably meets the patient &# 39 ; s metabolic demands . in this case , the controller 32 uses signals generated by the sensor 68 to determine the activity level of the patient . the measured level of activity is indicative of metabolic need . many methods of determining the activity level are well known in the art . attention is drawn to &# 39 ; 483 , which is hereby incorporated by reference . to regulate the pacing rate , the controller 32 provides a trigger signal to the a - pulse generator 22 and / or the v - pulse generator 24 . the timing of this signal ( to a large extent ) is determined by the activity level . in fig2 the activity indicated rate and the circadian base rate methods are illustrated together via a single transfer function . the transfer function is used by the control system to correlate the activity level measurements shown along the horizontal axis to the activity indicated pacing rates shown along the vertical axis . the controller 32 then triggers the appropriate pulse generator 22 , 24 at the activity indicated rate . it should be noted that an appropriate transfer function can be used based upon individual patient need . in addition , different modes of pacing ( i . e . ddd , vvi , etc .) can be accommodated by this method . two activity levels are noted on the horizontal axis of the transfer function : a low activity threshold 202 and a high activity threshold 204 . for activity level measurements above &# 39 ; the high activity threshold 204 , the pacing rate is maintained at a maximum pacing rate 200 . for activity level measurements between the low activity threshold 202 and the high activity threshold 204 , the activity indicated pacing rate varies according to the programmed transfer function 208 . in this case , the activity indicated pacing rate varies linearly between a circadian base rate 210 and a maximum pacing rate 200 . however , this transition can be programmed to meet patient &# 39 ; s needs by the physician or adjusted by the processor periodically as set forth in u . s . pat . no . 5 , 514 , 162 to bomzin et al , entitled “ system and method for automatically determining the slope of a transfer function for a rate - responsive cardiac pacemaker ”, issued may 7 , 1996 , hereby incorporated by reference . for activity level measurements below the low activity threshold 202 , the processor sets the pacing rate to a rate defined by the circadian base rate 210 . the circadian base rate 210 is defined through monitoring the activity variance measurements as described more fully in &# 39 ; 483 . a patients activity levels are monitored and activity variance measurements are calculated and monitored to determine when and how long a patient typically sleeps . these two terms are used to define a stimulation rate which is below the programmed base rate of the stimulation device 10 such that the patient receives a lower pacing rate during sleep . this lower pacing rate more closely mimics the natural cardiac rhythm . as discussed above , the patient group which suffers from long term diabetes tends to develop neuropathy from the long term exposure of their nerves to excessive blood sugar levels . this condition erodes the ability to adequately control the heart rate . in particular , this condition renders the patient unable to compensate for the dramatic drop in blood pressure upon standing after sitting or lying down due to an inability to increase the heart rate and constrict the system resistance and capacitance vessels . to overcome this condition , the controller 32 compensates for the change in patient position by triggering at an orthostatic compensation pacing rate . fig3 sets forth the normal heart response to provide the orthostatic compensation . upon standing after a prolonged period of sitting or lying down , the normal autonomic nervous system abruptly increases the natural heart rate to approximately 80 - 100 bpm in 3 - 8 seconds at 302 . then , the natural heart rate then slowly decreases to a rest rate in 2 seconds to one minute , typically approximately 60 - 70 bpm at 304 . fig4 sets forth the orthostatic compensation pacing method that provides the orthostatic compensation to a patient that does not naturally have it . the controller 32 abruptly increases the stimulation rate to approximately 85 - 100 bpm in 8 seconds at 402 . the upper orthostatic compensation pacing rate is determined by the clinician for each individual patient . then , the stimulation rate is slowly decreased to a high base rate in 20 - 60 seconds , typically approximately 70 bpm at 404 . the controller can override the orthostatic compensation pacing method if the patient activity level indicates an immediate stimulation rate higher than that of the immediate orthostatic compensation pacing rate . in other words , if the activity indicated pacing rate or the circadian base pacing rate should exceed the orthostatic compensation pacing rate at a particular time , then the controller 32 would follow the maximum of the three indicated stimulation rates . once the orthostatic compensation pacing rate has finished , the controller 32 uses the transfer function 208 as set forth in fig2 to determine the immediate stimulation rate . to determine when a patient is in need of orthostatic compensation , the controller 32 uses the activity level signals and the activity variance measurements to determine when the patient has stood after prolonged time of sitting or lying down . to this end , the controller 32 monitors two main variables in relation to two preset thresholds : the immediate activity level and the long term variance in activity ( also known as the activity variance measurement ). the clinician programs the activity threshold for a patient appropriate activity level . the activity variance threshold is predetermined based upon the patients activity . to determine the activity variance threshold , the activity variance measurements are stored in a histogram for a week . further information regarding histograms can be found in &# 39 ; 483 . to determine when a patient is standing after an extended period of inactivity , a night time activity variance threshold and a day time activity variance threshold are determined . the night time activity variance threshold is predetermined to be the bins of the histogram which contain counts of less than 17 . 5 % of the total histogram counts . the day time activity variance is predetermined to be the bins in the histogram which contains counts of less than 67 . 5 % of the total bin count . these two activity variance thresholds are then averaged to determine an activity variance threshold that indicates a patient is resting . in addition to monitoring the patient activity and the activity variance measurements , the controller 32 monitors how long the activity variance measurement is below the activity variance threshold . this time duration ( t rest ( expired ) ) is the necessary time for a patient to be resting and then in need of orthostatic compensation once the patient stands . it has been found that a t rest ( expired ) time duration of 1 minute to 3 hours as programmed by the clinician is the time duration that adequately indicates when a patient will require orthostatic compensation pacing upon standing . fig5 sets forth the flow chart describing how the controller 32 determines the immediate pacing rate and if patient has changed body positions and has previously been sitting or lying down for an extended period of time . following flow 1 , the controller 32 determines if the activity level signal is less than an activity threshold ( block 502 ), and if the activity variance measurement is greater than an activity variance threshold ( block 504 ). if these conditions are met , then the patient must be inactive , and the controller 32 adjusts the pacing rate to follow the circadian base rate ( block 506 ) as set forth in fig2 . following flow 2 , the controller 32 determines if the activity level signal is less than the activity threshold ( block 502 ), and the activity variance is also less than the activity variance threshold ( block 504 ). if these conditions are met , then the patient must be in a reclined or in a supine / prone position and is resting . at this point , the controller 32 starts a duration timer . this duration timer monitors the time the patient is at an extended period of inactivity ( i . e . t rest ) ( block 508 ). the controller 32 adjusts the stimulation rate to follow the circadian base pacing rate ( block 506 ) as set forth in fig2 . following flow 3 , the controller 32 determines if the activity level signal is greater than an activity threshold ( block 502 ) and if the t rest duration timer has not been started ( i . e . t rest = 0 )( block 520 ). if these conditions are met , then the patient must be active and must have been active . in this case , the controller 32 adjusts the stimulation rate to be the maximum of the activity indicated pacing rate and the circadian base pacing rate ( block 522 ) as set forth by the transfer function 208 in fig2 . following flow 4 , the controller 32 determines if the activity level signal is greater than an activity threshold ( block 502 ) and if the t rest duration timer has been started ( block 520 ) but has not exceeded t rest ( expired ) ( block 524 ). if these conditions are meet , then the patient has been resting a short period of time and has stood . in this case , the controller resets the t rest duration timer ( block 526 ) and adjusts the pacing rate to the maximum of the activity indicated pacing and the circadian base pacing rate as set forth by the transfer function 208 ( block 522 ). following flow 5 , the controller 32 determines if the activity level signal is greater than an activity threshold ( block 502 ), and the trest duration timer is greater than the t rest ( expired ) duration ( blocks 520 , 524 ). if these conditions are met , then the patient must have just stood and is in need of orthostatic compensation pacing . the orthostatic compensation pacing method has a total regimen time ( n ) 406 , and the controller 32 starts a regimen duration timer to monitor how far into the orthostatic compensation pacing method the patient is ( k ) 408 . if the regimen duration timer indicates that the pacing method is not complete ( k & lt ; n ) ( block 528 ), then the controller 32 adjusts the stimulation rate to be the maximum of the activity indicated pacing rate , circadian base pacing rate , and the orthostatic compensation pacing rate ( block 530 ), and increments the regimen duration timer ( block 532 ) ( i . e . k = k + 1 ). following flow 6 , the controller determines if the activity level signal is greater than an activity threshold ( block 502 ), the t rest duration timer exceeds t rest ( expired ) time period ( blocks 520 , 524 ), and the regimen duration timer exceeds the regimen time ( k & gt ; n ) ( block 528 ). if these conditions are met , then the patient must have just stood and has finished orthostatic compensation pacing . at this point , the controller 32 resets the t rest duration timer and the regimen duration timer ( block 540 ) and adjusts the stimulation rate to be the maximum of the activity indicated pacing rate and the circadian base rate ( block 522 ) as set forth in fig2 . although the invention has been described with reference to particular embodiments , it is to be understood that these embodiments are merely illustrative of the application of the principles of the invention . for instance , this method can be used to detect instantaneous changes and long term variations in any signal indicative of metabolic need to vary the pacing rate and pacing method as described . such sensors could be an oxygen saturation sensor , impedance sensors that measures the change in blood volume ; and sensors that detect the change in iegm or evoked response , etc . accordingly , the embodiments described in particular should be considered exemplary , not limiting , with respect to the following claims .
a system and method are provided for compensating for the drop in blood pressure upon standing . upon transition from prolonged sitting , lying down , or standing position , the pacemaker abruptly increasing its pacing rate upon postural transition . the pacing rate is abruptly increased to about 80 - 100 bpm in 20 seconds - one minute . the pacing rate then decreases slowly to another high rate in two or three minutes and then follows the metabolically indicated rate . this pacing rate is triggered whenever a patient stands after a prolonged reclined or supine / prone position as indicated by activity variance measurements .