fig1 and 2 illustrate the patient - to - patient differences that an external defibrillator design must take into account . these figures are schematic representations of truncated exponential biphasic waveforms delivered to two different patients from an external defibrillator according to the electrotherapy method of this invention for defibrillation or cardioversion . in these drawings , the vertical axis is voltage , and the horizontal axis is time . the principles discussed here are applicable to waveforms described in terms of current versus time as well , however . the waveform shown in fig1 is called a low - tilt waveform , and the waveform shown in fig2 is called a high - tilt waveform , where tilt h is defined as a percent as follows : ## equ1 ## as shown in fig1 and 2 , a is the initial first phase voltage and d is the second phase terminal voltage . the first phase terminal voltage b results from the exponential decay over time of the initial voltage a through the patient , and the second phase terminal voltage d results from the exponential decay of the second phase initial voltage c in the same manner . the starting voltages and first and second phase durations of the fig1 and fig2 waveforms are the same ; the differences in end voltages b and d reflect differences in patient impedance . prior art disclosures of the use of truncated exponential biphasic waveforms in implantable defibrillators have provided little guidance for the design of an external defibrillator that will achieve acceptable defibrillation or cardioversion rates across a wide population of patients . the defibrillator operating voltages and energy delivery requirements affect the size , cost , weight and availability of components . in particular , operating voltage requirements affect the choice of switch and capacitor technologies . total energy delivery requirements affect defibrillator battery and capacitor choices . we have determined that , for a given patient , externally - applied truncated exponential biphasic waveforms defibrillate at lower voltages and at lower total delivered energies than externally - applied monophasic waveforms . in addition , we have determined that there is a complex relationship between total pulse duration , first to second phase duration ratio , initial voltage , total energy and total tilt . up to a point , the more energy delivered to a patient in an electrotherapeutic pulse , the more likely the defibrillation attempt will succeed . low - tilt biphasic waveforms achieve effective defibrillation rates with less delivered energy than high - tilt waveforms . however , low - tilt waveforms are energy inefficient , since much of the stored energy is not delivered to the patient . on the other hand , defibrillators delivering high - tilt biphasic waveforms deliver more of the stored energy to the patient than defibrillators delivering low - tilt waveforms while maintaining high efficacy up to a certain critical tilt value . thus , for a given capacitor , a given initial voltage and fixed phase durations , high impedance patients receive a waveform with less total energy and lower peak currents but better conversion properties per unit of energy delivered , and low impedance patients receive a waveform with more delivered energy and higher peak currents . there appears to be an optimum tilt range in which high and low impedance patients will receive effective and efficient therapy . an optimum capacitor charged to a predetermined voltage can be chosen to deliver an effective and efficient waveform across a population of patients having a variety of physiological differences . this invention is a defibrillator and defibrillation method that takes advantage of this relationship between waveform tilt and total energy delivered in high and low impedance patients . in one aspect of the invention , the defibrillator operates in an open loop , i . e ., without any feedback regarding patient impedance parameters and with preset pulse phase durations . the preset parameters of the waveforms shown in fig1 and 2 are therefore the initial voltage a of the first phase of the pulse , the duration e of the first phase , the interphase duration g , and the duration f of the second phase . the terminal voltage b of the first phase , the initial voltage c of the second phase , and the terminal voltage d of the second phase are dependent upon the physiological parameters of the patient and the physical connection between the electrodes and the patient . for example , if the patient impedance ( i . e ., the total impedance between the two electrodes ) is high , the amount of voltage drop ( exponential decay ) from the initial voltage a to the terminal voltage b during time e will be lower ( fig1 ) than if the patient impedance is low ( fig2 ). the same is true for the initial and terminal voltages of the second phase during time f . the values of a , e , g and f are set to optimize defibrillation and / or cardioversion efficacy across a population of patients . thus , high impedance patients receive a low - tilt waveform that is more effective per unit of delivered energy , and low impedance patients receive a high - tilt waveform that delivers more of the stored energy and is therefore more energy efficient . another feature of biphasic waveforms is that waveforms with relatively longer first phases have better conversion properties than waveforms with equal or shorter first phases , provided the total duration exceeds a critical minimum . therefore , in the case of high impedance patients , it may be desirable to extend the first phase of the biphasic waveform ( while the second phase duration is kept constant ) to increase the overall efficacy of the electrotherapy by delivering a more efficacious waveform and to increase the total amount of energy delivered . fig3 - 5 demonstrate a defibrillation method according to this second aspect of the invention in which information related to patient impedance is fed back to the defibrillator to change the parameters of the delivered electrotherapeutic pulse . fig3 is a flow chart showing the method steps following the decision ( by an operator or by the defibrillator itself ) to apply an electrotherapeutic shock to the patient through electrodes attached to the patient and charging of the energy source , e . g ., the defibrillator &# 39 ; s capacitor or capacitor bank , to the initial first phase voltage a . block 10 represents initiation of the first phase of the pulse in a first polarity . discharge may be initiated manually by the user or automatically in response to patient heart activity measurements ( e . g ., ecg signals ) received by the defibrillator through the electrodes and analyzed by the defibrillator controller in a manner known in the art . discharge of the first phase continues for at least a threshold time t thresh , as shown by block 12 of fig3 . if , at the end of time t thresh , the voltage measured across the energy source has not dropped below the minimum first phase terminal voltage threshold v thresh , first phase discharge continues , as shown in block 14 of fig3 . for high impedance patients , this situation results in an extension of the first phase duration beyond t thresh , as shown in fig4 until the measured voltage drops below the threshold v thresh . discharge then ends to complete the first phase , as represented by block 16 of fig3 . if , on the other hand , the patient has low impedance , the voltage will have dropped below v thresh when the time threshold is reached , resulting in a waveform like the one shown in fig5 . at the end of the first phase , and after a predetermined interim period g , the polarity of the energy source connection to the electrodes is switched , as represented by blocks 18 and 20 of fig3 . discharge of the second phase of the biphasic pulse then commences and continues for a predetermined second phase duration f , as represented by block 26 of fig3 then ceases . this compensating electrotherapy method ensures that the energy is delivered by the defibrillator in the most efficacious manner by providing for a minimum waveform tilt and by extending the first phase duration to meet the requirements of a particular patient . because this method increases the waveform tilt for high impedance patients and delivers more of the energy from the energy source than a method without compensation , the defibrillator &# 39 ; s energy source can be smaller than in prior art external defibrillators , thereby minimizing defibrillator size , weight and expense . it should be noted that the waveforms shown in fig4 and 5 could be expressed in terms of current versus time using a predetermined current threshold value without departing from the scope of the invention . fig6 - 8 illustrate a third aspect of this invention that prevents the delivered waveform from exceeding a maximum tilt ( i . e ., maximum delivered energy ) in low impedance patients . as shown by blocks 52 and 54 in fig6 the first phase discharge stops either at the end of a predetermined time t thresh or when the first phase voltage drops below v &# 39 ; thresh . the second phase begins after an interim period g and continues for a preset period f as in the second aspect of the invention . thus , in high impedance patients , the first phase ends at time t thresh , even if the voltage has not yet fallen below v &# 39 ; thresh , as shown in fig7 . in low impedance patients , on the other hand , the first phase of the delivered waveform could be shorter in duration than the time t thresh , as shown in fig8 . once again , the waveforms shown in fig7 and 8 could be expressed in terms of current versus time using a predetermined current threshold value without departing from the scope of the invention . fig9 is a flow chart illustrating a combination of the defibrillation methods illustrated in fig3 and 6 . in this combination method , the first phase of the biphasic waveform will end if the voltage reaches a first voltage threshold v &# 39 ; thresh prior to the first phase duration threshold t thresh , as shown by blocks 91 and 92 . this defibrillator decision path delivers a waveform like that shown in fig8 for low impedance patients . for high impedance patients , on the other hand , if at the expiration of t thresh the voltage has not fallen below v &# 39 ; thresh , the duration of the first phase is extended beyond t thresh until the voltage measured across the electrodes reaches a second voltage threshold v thresh , as shown in decision blocks 91 and 93 . this defibrillator method path will deliver a waveform like that shown in fig4 . in alternative embodiments of this invention , the second phase pulse could be a function of the first phase voltage , current or time instead of having a fixed time duration . in addition , any of the above embodiments could provide for alternating initial polarities in successive monophasic or biphasic pulses . in other words , if in the first biphasic waveform delivered by the system the first phase is a positive voltage or current pulse followed by a second phase negative voltage or current pulse , the second biphasic waveform delivered by the system would be a negative first phase voltage or current pulse followed by a positive second phase voltage or current pulse . this arrangement would minimize electrode polarization , i . e ., build - up of charge on the electrodes . for each defibrillator method discussed above , the initial first phase voltage a may be the same for all patients or it may be selected automatically or by the defibrillator user . for example , the defibrillator may have a selection of initial voltage settings , one for an infant , a second for an adult , and a third for use in open heart surgery . fig1 is a schematic block diagram of a defibrillator system according to a preferred embodiment of this invention . the defibrillator system 30 comprises an energy source 32 to provide the voltage or current pulses described above . in one preferred embodiment , energy source 32 is a single capacitor or a capacitor bank arranged to act as a single capacitor . a connecting mechanism 34 selectively connects and disconnects energy source 32 to and from a pair of electrodes 36 electrically attached to a patient , represented here as a resistive load 37 . the connections between the electrodes and the energy source may be in either of two polarities with respect to positive and negative terminals on the energy source . the defibrillator system is controlled by a controller 38 . specifically , controller 38 operates the connecting mechanism 34 to connect energy source 32 with electrodes 36 in one of the two polarities or to disconnect energy source 32 from electrodes 36 . controller 38 receives timing information from a timer 40 , and timer 40 receives electrical information from electrical sensor 42 connected across energy source 32 . in some preferred embodiments , sensor 42 is a voltage sensor ; in other preferred embodiments , sensor 42 is a current sensor . fig1 is a schematic circuit diagram illustrating a device according to the preferred embodiments discussed above . defibrillator controller 70 activates a high voltage power supply 72 to charge storage capacitor 74 via diode 76 to a predetermined voltage . during this period , switches sw1 , sw2 , sw3 and sw4 are turned off so that no voltage is applied to the patient ( represented here as resistor 78 ) connected between electrodes 80 and 82 . sw5 is turned on during this time . after charging the capacitor , controller 70 deactivates supply 72 and activates biphase switch timer 84 . timer 84 initiates discharge of the first phase of the biphasic waveform through the patient in a first polarity by simultaneously turning on switches sw1 and sw4 via control signals t1 and t4 , while switch sw5 remains on to deliver the initial voltage a through electrodes 80 and 82 to the patient 78 . depending on the operating mode , delivery of the first phase of the biphasic pulse may be terminated by the timer 84 after the end of a predetermined period or when the voltage across the electrodes has dropped below a predetermined value as measured by comparator 86 . timer 84 terminates pulse delivery by turning off switch sw5 via control signal t5 , followed by turning off switches sw1 and sw4 . the voltage across electrodes 80 and 82 then returns to zero . during the interim period g , sw5 is turned on to prepare for the second phase . after the end of interim period g , timer 84 initiates delivery of the second phase by simultaneously turning on switches sw2 and sw3 via control signals t2 and t3 while switch sw5 remains on . this configuration applies voltage from the capacitor to the electrodes at an initial second phase voltage c and in a polarity opposite to the first polarity . timer 84 terminates delivery of the second phase by turning off switch sw5 via control signal t5 , followed by turning off switches sw2 and sw3 . the second phase may be terminated at the end of a predetermined period or when the voltage measured by comparator 86 drops below a second phase termination voltage threshold . in a preferred embodiment , switch sw5 is an insulated gate bipolar transistor ( igbt ) and switches sw1 - sw4 are silicon - controlled rectifiers ( scrs ). the scrs are avalanche - type switches which can be turned on to a conductive state by the application of a control signal , but cannot be turned off until the current through the switch falls to zero or near zero . thus , the five switches can be configured so that any of the switches sw1 - sw4 will close when sw5 is closed and will reopen only upon application of a specific control signal to sw5 . this design has the further advantage that switch sw5 does not need to withstand the maximum capacitor voltage . the maximum voltage that will be applied across switch sw5 will occur when the first phase is terminated by turning sw5 off , at which time the capacitor voltage has decayed to some fraction of its initial value . other switches and switch configurations may be used , of course without departing from the scope of the invention . in addition , the defibrillator configurations of fig1 and 11 may be used to deliver electric pulses of any polarity , amplitude , and duration singly and in any combination . while the invention has been discussed with reference to external defibrillators , one or more aspects of the invention would be applicable to implantable defibrillators as well . other modifications will be apparent to those skilled in the art .
this invention provides an external defibrillator and defibrillation method that automatically compensates for patient - to - patient impedance differences in the delivery of electrotherapeutic pulses for defibrillation and cardioversion . in a preferred embodiment , the defibrillator has an energy source that may be discharged through electrodes on the patient to provide a biphasic voltage or current pulse . in one aspect of the invention , the first and second phase duration and initial first phase amplitude are predetermined values . in a second aspect of the invention , the duration of the first phase of the pulse may be extended if the amplitude of the first phase of the pulse fails to fall to a threshold value by the end of the predetermined first phase duration , as might occur with a high impedance patient . in a third aspect of the invention , the first phase ends when the first phase amplitude drops below a threshold value or when the first phase duration reaches a threshold time value , whichever comes first , as might occur with a low to average impedance patient . this method and apparatus of altering the delivered biphasic pulse thereby compensates for patient impedance differences by changing the nature of the delivered electrotherapeutic pulse , resulting in a smaller , more efficient and less expensive defibrillator .