referring initially to fig1 and 2 , one preferred embodiment of the present invention is shown as comprising defibrillator 10 having body 12 , cover plate 14 , and carrying handle 16 . to use the defibrillator , an operator breaks seal 18 and removes cover plate 14 . the cover plate includes a pin 20 which is positioned in opening 22 of body 12 before the cover plate is removed . removal of the cover plate withdraws pin 20 and activates the defibrillator , as described below . the underside of cover plate 14 includes printed instructions 24 for facilitating correct usage of the device . prior to removal of the cover plate , a pair of electrodes 30 , 36 and associated cable 42 are held in the space between cover plate 14 and body 12 . when the cover plate is removed , the electrodes and cable may be withdrawn for use , as indicated in fig2 . electrodes 30 and 36 include adhesively surfaced outer portions 32 and 38 respectively , and respective inner portions 34 and 40 that are coated with a conductive gel for making electrical contact with a patient &# 39 ; s body . cable 42 includes separate cables 44 and 46 connected to electrodes 30 and 36 , respectively . cable 42 includes plug 48 which permits the electrodes to be quickly disconnected from the defibrillator , so that emergency medical personnel arriving on the scene can avoid delay by plugging electrodes 30 and 36 directly into their own equipment . electrode 36 includes diagram 37 illustrating the correct placement of the electrodes on the patient . the body 12 of the defibrillator includes an lcd display 50 , and pushbutton switches 52 , 54 and 56 . display 50 is used for prompting the operator of the defibrillator , as described in greater detail below . switches 52 and 54 are labeled with the words yes and no , respectively , and are used by the operator to respond to questions presented via display 50 . switch 56 is labeled &# 34 ; shock ,&# 34 ; and is used by the operator at the appropriate time to initiate application of a defibrillation shock . a pair of scissors 60 may also be carried in the space between body 12 and cover plate 14 . the scissors are used to remove the patient &# 39 ; s clothing , to facilitate placement of electrodes 30 and 36 . prior to use , the defibrillator of the present invention is completely contained within the portable , compact unit illustrated in fig1 . this design makes it both practical and convenient to continuously keep the defibrillator in the immediate vicinity of a patient known to be at risk with respect to heart attacks . seal 18 , in combination with other features described below , helps assure the integrity of the unit during prolonged periods of storage . the general operation of the defibrillator will now be described with reference to fig3 a - h . when a heart attack occurs , the operator removes the cover plate , and the defibrillator is activated electronically . the operator is immediately directed to connect the electrodes to the patient , as indicated in fig3 a . diagram 37 ( fig1 ) on one of the electrodes is available to guide proper placement . when the instrument detects that the electrodes have been connected , the message indicated in fig3 b is displayed . this message directs the operator to perform standard cpr operations on the patient . the operator indicates that this step has been completed by pushing the yes switch . when the yes switch is pushed , or when 25 seconds has elapsed , the message shown in fig3 c is displayed . if the subject is not unconscious , then the operator pushes the no switch , and the message shown in fig3 d will be displayed for a few seconds , after which the message in fig3 c will reappear . this feature allows the operator to respond appropriately if the patient later loses consciousness . if the patient is unconscious , or becomes unconscious , then the operator pushes the yes switch ( fig3 c ), and the instrument enters a detection mode in which the message shown in fig3 e is displayed . in this mode , electrocardiogram ( ecg ) and transthoracic impedance data is obtained directly from the patient via electrodes 30 and 36 ( fig2 ). the resulting data is used , together with information supplied by the operator ( e . g ., subject unconscious ), to determine whether a defibrillation shock is medically appropriate . during collection of data , the instrument looks for transthoracic impedance data that would indicate motion of the patient . if motion is detected , then the message shown in fig3 f is displayed , and the data collection is restarted . if the ecg data indicates that a defibrillation shock is not appropriate , then the message of fig3 d is briefly displayed , and the defibrillator then returns to the state corresponding to fig3 b . if the instrument determines that a shock is medically appropriate , then the message of fig3 g is displayed , advising the operator to proceed by pushing the shock switch . if the shock switch is then pushed , the instrument displays the message shown in fig3 h and then delivers a defibrillation shock to the patient . after the shock has been delivered , the instrument returns to the state corresponding to fig3 b . the cycle beginning at fig3 b and ending at fig3 h may be repeated for a maximum of two additional times , if the patient remains unconscious . the body 12 of the defibrillator houses the electronic components illustrated in fig4 a and 4b . these components include data processor 100 , analog - to - digital converter ( adc ) 102 , processor controller 110 , defibrillation circuit 120 , analog preprocessor 140 , data recorder 160 , battery circuit 170 , and various other components described below . electrodes 30 and 36 are connected through electromagnetic interference filter 190 to defibrillation circuit 120 and to analog preprocessor 140 . during the collection of ecg and transthoracic impedance data from the patient , relay 122 is in the position shown in fig4 a . the analog preprocessor separates the electrode signal into ecg and transthoracic impedance components , and delivers the component signals to adc 102 and to data recorder 160 . when a shock is to be delivered , the defibrillation circuit charges capacitor 126 up to a specified value , and then switches relay 122 such that capacitor 126 discharges through the patient via electrodes 30 and 36 . after the shock has been delivered , relay 122 returns to the position shown in fig4 a . the electronic circuit of the present invention is activated when cover plate 14 is removed from the unit . removal of the cover plate causes the withdrawal of pin 20 , which in turn causes switches 176 and 178 ( fig4 b ) to close , connecting recorder battery 172 to microcassette recorder 161 and system battery 174 to the other components of the circuit in fig4 a and 4b . the purpose of this feature is to prevent battery drain when the instrument is stored over extended periods of time . means are provided , however , for permitting a person to check the condition of system battery 174 without opening or unsealing the instrument . this means comprises magnetic reed switch 180 connected in parallel with switch 178 . the defibrillator of the present invention includes a separate battery test card having small magnets imbedded therein . to test the condition of system battery 174 , a person holds the battery test card at a designated position adjacent to the outer surface of body 12 . the magnet , indicated schematically by numeral 182 in fig4 b , closes reed switch 180 and provides power to all components of the defibrillator with the exception of microcassette recorder 161 . the closing of reed switch 180 also supplies a test signal to data processor 100 on line 184 . the test signal indicates to the data processor that a test is to be performed , and directs it to the appropriate procedure for carrying out the test . if the test is successful , the data processor causes tone generator 108 to emit a prescribed sequence of audible tones , to signal that the test has been successfully completed . diode 186 prevents a test signal from being applied to data processor 100 during normal operation of the defibrillator , i . e ., when switch 178 is closed . during operation of the defibrillator , battery level circuit 188 continuously monitors the voltage available from system battery 174 . if the voltage of system battery 174 falls below the level required for operation of data processor 100 , then battery level circuit 188 activates shutdown circuit 189 . shutdown circuit 189 responds by cutting off power to data processor 100 , thus preventing operation of the defibrillator at a voltage which might result in unreliable operation . a back - up system for preventing defibrillator operation when the battery level is too low is provided by adc 102 . adc 102 periodically samples the system battery voltage ( b2 ) and provides the digitized samples to data processor 100 over bus 104 . as described below , the data processor will not advise or initiate a shock if such samples indicate insufficient battery voltage . the function of the analog preprocessor is to supply a constant current signal to the electrodes and to analyze the return signal . if the return signal indicates that the electrodes are not connected to the patient , then the analog preprocessor sends a not connected signal to the data processor . if the electrodes are connected , then the analog preprocessor extracts ecg signals and transthoracic impedance ( tti ) signals from the return signal and sends the analog ecg and transthoracic impedance signals to data recorder 160 and analog - to - digital converter ( adc ) 102 . the analog preprocessor includes protection network 141 , constant current source 142 , synchronous demodulator 144 , amplifier / filters 146 and 148 , comparator 150 , low pass filter 152 , and amplifier / filter 154 . associated with the analog preprocessor is electromagnetic interference filter 190 consisting of inductor 192 and capacitor 194 . constant current source 142 supplies a constant ( rms ) current , 12 khz sine wave which is applied to the patient through protection network 141 and electrodes 30 and 36 . the resulting signal is synchronously demodulated by synchronous demodulator 144 . the synchronous demodulator provides an output signal whose amplitude is proportional to the amplitude of the 12 khz component of the return signal , i . e ., to the impedance between electrodes 30 and 36 . the output signal from synchronous demodulator 144 is passed to amplifier / filter 146 . amplifier / filter 146 removes unwanted high frequency components , including any residual 12 khz signal , and also provides a small amount of gain . the output of amplifier / filter 146 is fed to amplifier / filter 148 and to comparator 150 . amplifier / filter 148 includes a bandpass filter with a passband of approximately 1 - 20 hz . this filter thus removes the dc component from the return signal , and provides an output indicative of transthoracic impedance variations over time . comparator 150 compares the level of the output of amplifier / filter 146 with a fixed reference voltage . if the level exceeds the reference , then the comparator pulls line 158 low , signaling that the electrodes are not connected . the signal from electrodes 30 and 36 is also input to low pass filter 152 through protection network 141 . the filter removes the 12 khz signal and other high frequency components , and passes the resulting signal to amplifier / filter 154 . amplifier / filter 154 includes a bandpass filter adapted to extract the ecg signal returned from the patient through the electrodes . as further described below , amplifier / filter 154 also provides gain to the ecg signal , the amount of gain being determined by a digital gain select signal originating in data processor 100 and transmitted to amplifier / filter 154 over line 156 . protection network 141 is a conventional impedance matching network that protects the analog preprocessor from the high voltage applied to the electrodes by defibrillation circuit 120 during delivery of a shock to the patient . protection network 141 has an impedance that does not signficantly affect ecg or transthoracic impedance measurements , but that does cause the attenuation of the frequency components contained in a defibrillation pulse to a degree sufficient to prevent such a pulse from damaging any of the components of the analog preprocessor . data processor 100 is a conventional digital computer that includes a microprocessor , read only memory ( rom ) for storing a program , random access memory ( ram ) for data storage , a parallel port and a timer . a suitable microprocessor for use in data processor 100 is the nsc 800 microprocessor available from the national semiconductor corporation . associated with data processor 100 are processor controller 110 and associated shock pushbutton switch 56 , display system 106 , tone generator 108 , yes and no pushbutton switches 52 and 54 , and adc 102 . processor controller 110 coordinates the activities of data processor 100 and defibrillation circuit 120 , and is described in greater detail below . display system 106 comprises a conventional display driver and lcd display unit 50 ( fig2 ). tone generator 108 is a conventional audio transducer used for producing audible signals . pushbutton switches 52 , 54 and 56 correspond to the pushbuttons shown in fig2 and 3 , and are used by the operator to respond to prompts communicated through display system 106 , and to initiate a defibrillation shock . adc 102 is an analog - to - digital converter used for converting the analog tti and ecg signals from analog preprocessor 140 into digital signals usable by data processor 100 . adc 102 alternately samples the tti and ecg signals at 240 hz , thus providing a sampling rate of 120 hz for each signal . the digital samples are passed to the data processor over 8 - bit bus 104 . adc 102 provides an interrupt signal rstc to data processor 100 each time a digital sample is ready . in response to the rstc interrupt , data processor 100 jumps to an interrupt service routine for inputting the sample . through this arrangement , a uniform sampling rate is provided regardless of the timing of the program for operating data processor 100 . defibrillation circuit 120 is activated by a high enable signal on line 134 . in response to such a signal , the defibrillation circuit begins charging capacitor 126 from system battery 174 ( b2 ). when the charge reaches a predetermined threshold , the defibrillation circuit energizes relay 122 , discharging capacitor 126 through the patient through electrodes 30 and 36 . the defibrillation circuit is activated by a high enable signal momentarily appearing on line 134 . in response to this signal , bistable control circuit 124 latches line 134 into a high state , and causes charge transfer circuit 128 to begin charging capacitor 126 from system battery supply b2 . bistable control circuit 124 may , by way of example , consist of two amplifiers connected in series , with positive feedback means provided to enable the circuit to be stable in either one of two states . charge transfer circuit 128 may be any well known circuit for converting a low level dc voltage to a high voltage output by means of a flyback transformer or other conventional means . as capacitor 126 is charged through charge transfer circuit 128 , the voltage on capacitor 126 is continuously monitored by comparator / timer 130 . when the capacitor voltage exceeds a threshold level , comparator / timer 130 triggers relay driver 132 which in turn energizes the coil of relay 122 , switching the relay and connecting capacitor 126 to the electrodes . the capacitor then discharges through the patient via wave shaping inductor 138 . at the same time that comparator / timer 130 triggers relay driver 132 , it also pulls line 134 low bistable control circuit 124 then latches line 134 into a low state , completing the defibrillation cycle . should capacitor 126 fail to charge to the threshold level within a predetermined time interval , then a timeout circuit included within comparator / timer 130 triggers relay driver 132 and pulls line 134 low , thus delivering to the patient whatever energy is available and terminating the defibrillation cycle . as previously described , analog preprocessor 140 pulls line 158 low when it detects that electrodes 30 and 36 are not connected to the patient . one effect of line 158 going low is that line 134 is also pulled low through diode 136 . a low voltage on line 134 will cause bistable control circuit 124 to latch line 134 in its low state , terminating any defibrillation cycle that is in process . thus the defibrillator of the present invention will not attempt to deliver a defibrillation pulse should the electrodes become disconnected . line 134 is also connected to battery level circuit 188 through diode 137 . thus when battery level circuit 188 detects a low voltage on system battery b2 , line 134 will be held low , and the delivery of a defibrillation shock will also be prevented in this circumstance . processor controller 110 coordinates the activities of data processor 100 and defibrillation circuit 120 . when the data processor determines that a shock is advised ( see fig3 g ), it sends a high shock enable signal to processor controller 110 on line 200 . this signal activates shock pushbutton switch 56 , such that if switch 56 is now pushed , a high enable signal will be sent to defibrillation circuit 120 on line 134 , initiating a defibrillation cycle . at the same time that line 134 is driven high , processor controller 110 sends a low ready signal back to data processor 100 on line 202 . a short time after the ready signal is sent , processor controller sends a low shut down signal on line 204 . the shut down signal causes data processor 100 to go into a quiescent state in which only its timer continues to be active . the ready signal is used by data processor 100 to prepare for entering this quiescent state . the purpose of this feature is to prevent any electromagnetic interference that might accompany the delivery of a shock to interfere with the operations of the data processor . after a shock has been delivered , processor controller 110 pulls lines 202 and 204 high to restart the data processor , and then issues a high rsta interrupt signal on line 206 , causing the data processor to go back to the state corresponding to the display in fig3 b , starting another cycle . the detailed construction of processor controller 110 is illustrated in fig5 . a high shock enable signal appearing on line 200 causes inverter 210 to supply a low voltage to terminal 214 of shock switch 56 . when shock switch 56 is closed , terminal 216 is also driven low , enabling capacitor 218 to rapidly charge through switch 56 . the resulting low voltage is input to inverter 222 through input resistor 220 , driving line 134 high through resistor 224 and diode 226 . when switch 56 is released , capacitor 218 discharges through resistor 228 at a rate slow enough to enable bistable control circuit 124 ( fig4 a ) to latch line 134 into a high state . after capacitor 218 discharges , diode 226 provides isolation between line 134 and inverter 222 . diode 212 prevents capacitor 218 from discharging through switch 56 . the high voltage on line 134 is sensed by inverter 232 through input resistance 234 , causing inverter 232 to drive line 202 low . a low signal on line 202 causes data processor 100 to execute various housekeeping steps in preparation for line 204 going low . a low signal on line 202 also causes capacitor 236 to begin charging through resistor 238 and through resistor 240 and diode 242 . the decreasing voltage at node 243 is coupled to inverter 244 through input resistor 246 . when the voltage at node 243 has dropped below a certain level , a low signal appears on line 204 , halting the operations of data processor 100 . the delay between the shut down and ready signals is determined by the time constant for the charge of capacitor 236 . at the time that line 204 is pulled low , node 250 goes high , and capacitor 252 begins to charge through resistor 254 . the rising voltage at node 260 is coupled to inverter 256 through input resistor 258 . when the voltage of node 260 has risen to a sufficient level , inverter 256 causes a low rsta signal to appear on line 206 . since data processor 100 is shut down , the low rsta signal has no effect at this time . when a defibrillation cycle is completed , or when a low battery or a not connected signal is provided by analog preprocessor 140 , line 134 is pulled low . such a low signal initiates a sequence of events which is the reverse of that just described . in particular , a low signal on line 134 immediately drives line 202 high , and drives line 204 high a short time later , restarting the data processor . after another short time interval , processor controller 110 sends a high rsta interrupt signal on line 206 , vectoring data processor 100 to an appropriate restart point as described below . data recorder 160 comprises microcassette recorder 161 , multiplexer / modulator 162 , audio amplifier 163 , microphone 164 , and coupling capacitor 165 . microcassette recorder 161 is powered by separate recorder battery ( b1 ) 172 , which is connected to the microcassette recorder through a normal conductor line 166 and through fusible link 167 . fusible link 167 consists of a piece of thin wire that melts as soon as current begins to flow through it , i . e ., when cover plate 14 is removed and switch 176 closes . prior to melting , fusible link 167 holds spring loaded pinch roller 168 out of engagement with the tape and capstan of microcassette recorder 161 . this feature is provided so that the defibrillator of the present invention will be usable after an extended period of storage . during use , pinch roller 168 provides the pressure between the tape and capstan to enable the capstan to drive the tape . prior to use , however , the fusible link holds the pinch roller disengaged from the capstan and tape to prevent it from flattening and sticking to the tape . microcassette recorder 161 is a two track recorder , one track for transthoracic impedance and ecg data , and the second track for voice and status information . multiplexer / modulator 162 receives the analog transthoracic impedance and ecg signals from analog preprocessor 140 , converts these analog signals to pulse - width modulation format , and multiplexes the resulting pulse streams for recording on one track of microcassette recorder 161 . the other track of the microcassette recorder records voice and other audio signals picked up by microphone 164 and amplifier by audio amplifier 163 . the voice track also records system status information sent by data processor 100 through line 169 . the status information is coupled from line 169 to audio amplifier 163 through coupling capacitor 165 . the defibrillator of the present invention includes means by which data recorder 160 can record information confirming that a substantial amount of energy , i . e ., a defibrillation pulse , has actually been delivered to the patient through electrodes 30 and 36 . referring to fig6 a cross section of wave shaping inductor 138 is shown including bobbin 272 and inductor coils 270 . the central portion of bobbin 272 is indented to form recess 274 . elastic cord 276 is mounted to bobbin 272 over recess 274 , and mounts ferrous objects 278 thereon such that the ferrous objects are normally held over the recess spaced apart from the bobbin . when a defibrillation pulse is delivered through wave shaping inductor 138 , the current through inductor coils 270 creates a maximum magnetic field density in the direction indicated by arrow 280 that pulls ferrous objects 278 with considerable force into bobbin 272 at the base of recess 274 . the unique sound caused by the objects striking the bobbin is picked up by microphone 164 and recorded on the voice track of microcassette recorder 161 . these sounds can later be identified to confirm that defibrillation pulses have actually been delivered . after a defibrillation pulse , ferrous objects 278 return to the position indicated in fig6 ready for a subsequent pulse to be recorded . fig7 a through 7f illustrate a flow chart for a program suitable for operation of the microprocessor of data processor 100 . block 300 represents the point at which program execution begins when power is first supplied to the microprocessor , or when line 204 ( fig4 b ) goes high . block 302 tests the status of line 184 ( fig4 b ) to determine whether the power - on is a result of a test or actual operation of the device . if it is a test , then control passes to block 304 where appropriate tests are performed to verify that system battery 174 has sufficient voltage and that data processor 100 is capable of proper operation . in one embodiment , block 304 tests a digitized battery voltage sample provided by adc 102 over bus 104 . block 306 determines whether the tests have been successfully passed . if they have not , then control returns to block 304 and the tests are repeated . if the tests are passed , then block 308 causes tone generator 108 to beep three times , block 310 delays program execution for three seconds , and control then returns to block 304 to repeat the tests . in the usual case , the person performing the test procedure will remove the magnet ( test card ) 182 when the beeps are generated , terminating the test and shutting down the system . if the three beeps are not heard , it is an indication that the tests have not been passed and that maintenance is required . when the power - on ( in block 300 ) is due to an actual opening of the defibrillator , then control passes from block 302 to block 312 where variable cpr is set to 1 . this variable controls the number of times that the cpr sequence ( fig3 b ) is repeated , as described below . block 316 then enables interrupts rsta and rstb . interrupt rsta is used to restart the microprocessor after a defibrillation shock has been delivered . the rsta restart point is indicated by entry point 314 , so that program execution returns at block 316 after a shock has been delivered . referring to fig4 a and 4b , interrupt rstb is provided whenever a not connected signal is generated by analog preprocessor 140 . in response to an rstb interrupt , the microprocessor executes the interrupt service routine shown in fig7 f , and then returns control to the main program at entry point a , recommencing execution with block 312 . when the defibrillator is first opened for actual operation , electrodes 30 and 36 will not be connected , and the analog preprocessor will pull line 158 low , causing an rstb interrupt signal to be sent to data processor 100 . in this circumstance , the enabling of interrupt rstb in block 316 will cause an immediate jump to block 452 of the interrupt service routine of fig7 f . block 452 generates the display shown in fig3 a , and block 454 checks to see whether 20 seconds have elapsed since the defibrillator was opened . if 20 seconds have not elapsed , program execution is delayed for one second by block 456 , after which program flow returns to block 312 in fig7 a . if the electrodes are not yet connected , interrupt rstb will immediately vector the program back to the interrupt service routine , and this loop will continue until the electrodes are connected and interrupt rstb is no longer present . for the first 20 seconds after the device is opened , block 454 causes a jump directly to block 456 each time the interrupt service routine is executed . between 20 - 25 seconds after the device is opened , blocks 454 and 458 direct control through block 460 and a series of beeps is produced . after 25 seconds the beeps terminate and the program loops between the interrupt service routine and the main routine until the electrodes are connected . when the electrodes are connected , interrupt rstb is no longer present and control passes through block 316 to block 318 , where the message indicated in fig3 b is displayed . block 320 then causes generation of a characteristic tone sequence , and block 322 tests to see whether yes pushbutton switch 52 has been pressed . when the yes switch is pushed , or when 25 seconds have elapsed , control passes to block 324 where the number of passes through the loop consisting of blocks 316 - 322 is compared to variable cpr . after a poweron , this test will be satisfied after the first pass , since cpr was set to 1 in block 312 . whenever this test is not satisfied , program execution returns to block 316 , and another cpr sequence is performed . when the number of cpr sequences specified by variable cpr have been completed , control passes to block 326 which checks the number of shocks that have been delivered . the defibrillator of the present invention is intended to deliver up to a maximum of three defibrillation shocks . if three shocks have already been delivered , then block 326 returns control to block 316 , and the cpr sequence is continued indefinately . if three shocks have not been delivered , then control passes to block 328 , where the voltage level of system battery 174 is checked by examining the battery voltage sample provided by adc 102 over bus 104 . if the battery level is too low for reliable operation , then the cpr sequence continues as indicated . if the battery level is sufficient , then control passes to block 330 ( fig7 b ). block 330 prompts the operator to indicate whether or not the patient is unconscious . after generating this display , block 332 directs program execution to either block 338 or 334 , depending upon whether or not the operator indicated that the patient was conscious the last time the question in block 330 was answered . if the patient was not conscious in the previous pass , then block 334 outputs a characteristic tone sequence . as indicated by block 336 , this tone sequence continues until the operator responds by pushing either the yes or no pushbutton switch . when the operator does respond , control passes to block 340 . when the patient was conscious in the previous pass , then control passes directly from block 332 to block 338 , where the program loops until the operator responds and then continues to block 340 . block 340 determines whether the operator of the defibrillator has indicated that the patient is unconscious . if the patient is not unconscious , then block 342 outputs the display indicated in fig3 d , block 344 outputs a characteristic tone sequence , block 346 causes a four second delay , and program execution returns to block 330 to again ask whether the patient is unconscious . by such means , the defibrillator will be prepared to respond in an appropriate manner should a presently conscious patient later lose consciousness . if the patient is unconscious , control passes to block 350 ( fig7 c ), and the message indicated in fig3 e is displayed . block 352 then outputs a single tone through tone generator 108 , and the program commences the collection of tti ( transthoracic impedance ) and ecg data from the unconscious patient . as described previously , adc 102 alternately supplies digital tti and ecg samples to data processor 100 , issuing interrupt signal rstc whenever a sample is ready . block 354 enables the rstc interrupt , and the program then waits in block 356 for tti data to be supplied . when an rstc interrupt is received , program control is vectored to rstc entry point 358 , the data sample is input by block 360 , and block 362 determines whether the sample is tti or ecg data . if the sample is tti data , then execution continues with block 364 . block 364 analyzes successive tti values to determine whether excessive motion is present in the patient . by way of example , block 364 could detect excessive motion by determining whether the last two tti values exceed a threshold . if excessive motion is present , then block 366 generates the display indicated in fig3 f , block 368 causes production of a steady tone by tone generator 108 , block 370 causes a one second delay , and block 372 determines whether the excessive motion has been present for 15 seconds . if it has not been present for 15 seconds , the program returns to block 350 , and the data collection sequence is begun again . if excessive motion has been present for 15 or more seconds , then the program returns to block 316 ( fig7 a ), corresponding to the display in fig3 b . the defibrillator of the present invention checks the patient for excessive motion because such motion could result in invalid ecg data , and because excessive motion could indicate that the patient should not be shocked . for example , excessive motion could indicate that the patient is conscious , that the patient is being moved , or that the patient is moving internally due , for example , to cardiac output . if excessive motion is not present , then the defibrillator waits in block 374 for ecg data . when such data is ready , it is input by block 360 , and block 362 directs program flow to block 376 . block 376 attenuates 60 hz noise in the ecg data , and block 378 then tests the amplitude of the most recent ecg data point . if the amplitude is too large , block 380 decreases the gain of the analog preprocessor 140 by modifying gain select signal 156 ( fig4 a and 4b ), and data collection is restarted at block 350 . if the ecg amplitude is not too large , then block 382 provides a second level of filtering adapted to remove rumble below the ecg frequency range . if there is more data to be collected , block 384 then returns control to block 356 for acquisition of the next tti and ecg data samples . when a sufficient number of ecg data samples have been collected and stored , control passes to block 386 in fig7 d . block 386 disables interrupt rstc , thereby preventing adc 102 from subsequently interrupting program flow . block 388 then analyzes the ecg data points to determine the repetition rate ( frequency ) of the dominant complex in the ecg signal ( e . g ., the qrs complex ). if the rate is less than 2 . 3 hz or greater than 12 hz , then block 390 directs program flow to block 392 , where the shock flag for this pass is set to zero , indicating that the patient is not presently in a shockable condition . if the rate is within the shockable range , then block 394 checks to see whether the frequency variance of the ecg data exceeds a maximum limit . if the variance is too large , then the shock flag is set to zero in block 392 . if the frequency variance is consistent with the application of defibrillation shock , then block 396 checks the average amplitude of the ecg signal . if the average amplitude is too low , then no conclusions can be reliably drawn from the data , and the shock flag is set to zero . if the amplitude is sufficient , block 398 determines whether r waves are present in the ecg signal . if r waves are present , then the patient should not be shocked , and the shock flag is set to zero in block 392 . if r waves are not present , then block 400 performs a slope histogram analysis of the ecg data . in this analysis , the differences between adjacent ecg data points are determined , and the slopes ( differences ) falling within a series of ranges are counted . block 402 then checks the relative frequency of low slope values . if such relative frequency is too high to be consistent with a shockable arrhythmia , then the shock flag is set to zero in block 392 . if the relative frequencies of the lower histogram ranges are within shockable limits , then block 404 sets the shock flag for this pass to one , signifying that the patient &# 39 ; s ecg signal indicates that a defibrillation shock is medically appropriate . it is to be understood that other known tests could be used , either singly or in combination , to determine whether a shockable ecg rhythm is present , and the invention herein is not limited to any particular method of making this determination . the defibrillator makes two or three successive passes through the data acquisition and analysis steps just described . when the first pass is complete , blocks 406 and 408 direct program flow to block 350 ( fig7 c ) to begin the second pass . when the second pass is complete , block 410 checks the shock flag for the second pass . if the second shock flag is not equal to one , then control passes to block 438 ( fig7 e ) and a shock not required message is displayed to the operator . if both the first and second shock flags are equal to one , then control passes to block 416 ( fig7 e ), and a shock sequence is commenced . if the second shock flag is one , but the first shock flag is zero , then control returns to block 350 , and a third pass is commenced . when the third pass is complete , block 406 directs control to block 414 , and the third shock flag is tested to determine whether or not a shock should be administered . if a shock is to be administered , then block 416 causes the data processor to drive line 200 high ( fig4 b ), enabling shock pushbutton switch 56 . block 418 then causes generation of the display indicated in fig3 g , and block 420 causes production of a characteristic tone sequence . the program then executes a loop consisting of blocks 422 and 424 until the operator pushes the shock switch , or until 30 seconds have elapsed . if the shock switch is pushed , block 426 causes generation of the display indicated in fig3 h , block 428 causes output of a warning tone , block 430 sets variable cpr to 2 , and block 432 then waits for processor controller 110 to issue ready and shut down signals , as previously described . if the operator does not push the shock switch within 30 seconds , block 434 causes line 200 to be pulled low , disabling the shock switch . block 436 then sets variable cpr equal to 4 , and returns control to the cpr sequence commencing with block 316 ( fig7 a ). if the tests shown in fig7 d indicate that a shock is not to be applied , then control passes to block 438 where the indicated message is displayed . block 440 then causes output of a characteristic tone sequence , and block 442 causes a 5 second delay . block 436 then sets variable cpr to 4 , and control returns to block 316 . the values of cpr set in blocks 430 or 436 will subsequently result in block 324 causing either 2 or 4 cpr sequences to be executed , depending upon whether or not a shock was administered to the patient . while the preferred embodiments of the invention have been illustrated and described , it should be understood that variations will become apparent to those skilled in the art . accordingly , the invention is not to be limited to the specific embodiments illustrated and described herein , but rather the true scope and spirit of the invention are to be determined by reference to the appended claims .
a portable , interactive medical electronic device exemplified by a defibrillator . the device obtains information about a patient &# 39 ; s condition , such as ecg and transthoracic impedance data , directly from the patient , and information pertinent to the treatment of the patient indirectly through an operator of the device , and produces a medically appropriate action such as a defibrillation shock in response . indirect information is obtained through information processing means that includes means for prompting the operator of the device and means for receiving the operator &# 39 ; s responses thereto . prompts may include both questions and instructions , and in one embodiment the information processing means obtains the assent of the operator before causing the defibrillation shock . indirect information may include information as to whether the patient is conscious , and as to whether or not cardiopulmonary resuscitiation has been performed . the ecg and transthroacic impedance data may be collected through a common pair of electrodes . in one embodiment the device produces an indication that the ecg data is invalid if the transthoracic impedance data indicates excessive motion on the part of the patient . when a difibrillation shock is determined to be medically appropriate , a control signal is produced that causes the charging of an energy storage means and the subsequent discharging of such energy storage means through the patient without further operator intervention . the device also includes a tape recorder for allowing later analysis of the use of the device , and means for holding the tape recorder drive means in a disengaged position until the device is opened for use . the device also includes testing means for enabling a person to test the condition of the device without opening the case in which it is enclosed , means for producing and recording a distinctive sound when and if a defibrillation pulse is delivered , and means for allowing the electrodes to be quickly disconnected so that emergency personnel can conveniently use the electrodes with their own equipment .