referring to fig1 the instrument housing 26 of this invention is illustrated . outwardly , the housing includes a digit display 1 , circuitry select button array 2 through 5 , alarm status lights 6 through 9 , an optically coupled adjustment knob 10 , sync status light 11 , led digital viewmeter 12 , and power switch 13 . a speaker 15 is placed under and in the instrument housing . from a connector ( not shown ) in housing 26 there extend leader wires 27 . wires 27 extend to a detector probe 29 . detector 29 is placed upon the finger 14 of a patient 28 . utilizing the placement of the detector 29 at the finger 14 , all of the readings in this invention are made possible . the oximeter housing also includes a motion indicator 30 . when lit up , this indicator shows that motion has been detected . in addition , the digital display 1 will provide a blinking pulse reading with alternating dashes to indicate that the reliability is suspect due to the detection of motion . a description of the electronic circuitry of the nellcor n - 200 pulse oximeter will be first presented , to enable understanding of the present invention . this is only an example of one pulse oximeter in which the present invention may be used . referring to fig2 sensor circuit 100 has red led 110 and infrared led 120 connected in parallel , anode to cathode , so that the led drive current alternately illuminates one led and then the other led . circuit 100 also includes photodetector 130 , preferably a photodiode , which detects the level of light transmitted through the patient &# 39 ; s tissue , e . g ., finger 140 , as a single , analog optical signal containing both the red and infrared light plethysmographic , detected optical signal waveforms . patient module 200 includes preamplifier 210 for preamplifying the analog detected optical signal of photodetector 130 . alternately , the preamplifier may be in the oximeter itself . preamplifier 210 may be an operational amplifier configured as a current to voltage converter , biased by a positive voltage to extend the dynamic range of the system , thereby converting the photocurrent of photodiode 130 into a usable voltage signal . patient module 200 also includes leads for passing the led drive voltages to leds 110 and 120 . saturation analog front end circuit 300 receives the analog optical signal from patient module 200 and filters and processes the detected signal to provide separate red and infrared analog voltage signals corresponding to the detected red and infrared optical pulses . the voltage signal is passed through low pass filter 310 to remove unwanted high frequency components , ac coupled through capacitor 325 to remove the dc component , passed through high pass filter 320 to remove any unwanted low frequencies and passed through buffer 320 and passed through programmable gain stage 330 to amplify and optimize the signal level presented to synchronous detector 340 . synchronous detector 340 removes any common mode signals present and splits the time multiplexed optical signal into two channels , one representing the red voltage signals and the other representing the infrared voltage signals . each signal is then passed through respective filter chains having two 2 - pole 20 hertz low pass filters 350 and 360 , and offset amplifier 370 and 380 . the filtered voltage signals now contain the signal information corresponding to the red and infrared detected optical signals . analog - to - digital converter ( adc ) 1000 provides the analog to digital conversions required by the n - 200 oximeter . the aforementioned two voltage signals , the red detected optical signal and the infrared detected optical signal from patient module 200 , are input to adc 1000 . these signals are conventionally multiplexed and digitized by an expanded range 12 - bit analog - to - digital conversion technique , yielding 16 - bit resolution . the input signals are passed through multiplexor 1010 and buffer amplifier 1020 . the converter stage includes offset amplifier 1030 and programmable gain circuitry 1040 which allows a portion of the signal to be removed and the remainder to be further amplified for greater resolution , sample and hold circuit 1050 , comparator 1060 , and 12 - bit digital to analog convertor 1080 . the buffered signal is passed through offset amplifier 1030 to add a dc bias to the signal wherein a portion of the signal is removed and the balance is amplified by being passed through programmable gain circuitry 1040 to improve the resolution . the amplified signal is then passed through sample and hold circuit 1050 , the output of which is fed to one input of comparator 1060 . the other input of comparator 1060 is the output of digital to analog ( dac ) converter 1080 so that when the inputs to comparator 1060 are the same , the analog voltage at the sample and hold circuit is given the corresponding digital word in dac converter 1080 which is then stored in an appropriate memory device as the digitized data for the sample and the next sample is sent to sample and hold circuit 1050 to be digitized . dac 1080 also generates the sensor led drive voltages , under the control of microprocessor 2040 , using analog multiplexor 610 , which separates the incoming analog signal into one of two channels for respectively driving the red and infrared leds , having respective sample and hold circuits 620 and 630 , and led driver circuit 640 for converting the respective analog voltage signals into the respective positive and negative bipolar current signals for driving leds 110 and 120 . digital signal processor ( dsp ) 2000 controls all aspects of the signal processing operation including the signal input and output and intermediate processing . the apparatus includes 16 - bit microprocessor 2040 and its associated support circuitry including data bus 10 , random access memory ( ram ) 2020 , read only memory ( rom ) 2030 , a conventional led display device 2020 ( not described in detail ), and system timing circuit 2050 for providing the necessary clock synchronizing signals . interrupt programs control the collection and digitization of incoming optical signal data . as particular events occur , various software flags are raised which transfer operation to various routines that are called from a main loop processing routine . fig3 illustrates a pulse oximeter detector signal 32 with bloodflow pulses being regularly detected in a first period 34 . at a time 36 , no more qualified pulses are detected . this cab be due to noise , motion artifact , or the absence of a blood pulse . the oximeter will continue looking for qualified pulses for a 10 second period 38 after the last qualified pulse . if no qualified pulse is detected within this time , a probationary state 40 is entered . in the first portion of the probationary state , a 6 . 3 second timer is set for a period 42 . referring to fig4 as well , probationary state 40 is indicated in the state diagram of fig4 as including a motion state 42 and a noise state 44 . when the 6 . 3 second timer is set , this is initially the noise state 44 . the noise state preferrably has affirmative criteria , but can also simply be the absence of motion or a qualified signal . an example of an affirmative criteria is the lack of correlation between the ir and red channels for a pulse . in the preferred embodiment , at least 2 pulses ( noise or otherwise ) must be detected as noise in the 6 . 3 second period . if no pulse is detected for 3 . 1 seconds , the preceding 3 . 1 second period is presumed to be a pulse , and is analyzed accordingly . if motion is detected , motion state 42 is entered and the 6 . 3 second timer is halted . this can continue for the maximum probation period of 50 seconds . if motion continues to be detected after 50 seconds , an alarm is generated upon alarm state 46 of fig4 being entered . the alarm will also be generated when the 6 . 3 second timer runs out . fig5 is a flowchart illustrating the software used to implement the states of fig4 . this software would reside in ram 2020 of fig2 . after the start , a startup routine ( step a ) is entered wherein pulses are qualified and a good pulse signal is indicated after four consecutive qualified pulses . the qualification is done according to well - known techniques . once this startup is completed , the software enters a normal qualification state ( step b ). after each pulse is detected , a 10 second timer is started ( step c ). if 10 seconds has passed since the last qualified pulse was detected , the system enters the probation state and a 50 second timer is set ( step d ). the 6 . 3 second timer is also set ( step e ). the signal is then monitored for the detection of an ir ( infrared ) pulse ( step f ). the ir channel is monitored because the ir tends to be a lower noise source than the red signal . if no qualified pulse is detected for 6 . 3 seconds ( step g ) the alarm is sounded ( step h ). the 50 second timer is also checked ( step i ) in case it expires before a particular 6 . 3 second period . if an ir pulse is detected in the probation period , a test is then done to see if motion is detected ( step j ). the detection of motion is shown in more detail in the motion detection flowchart of fig6 . upon the detection of motion , the motion display on the monitor is illuminated ( step k ), and the 6 . 3 second timer is reset ( step e ) and the system continues to monitor for another pulse . if a pulse is detected and there is no motion , a test is done to determine fit should be rejected as being noisy ( step l ). in the noise state , a slower averaging algorithm is used than in the normal qualified state to insure that a false indication of a good blood pulse is not generated . if there is no noise rejection , it is a qualified pulse , and a qualified pulse count is incremented ( step m ). upon the count equalling four consecutive pulses ( step n ), the probationary period is exited after turning off the display ( step o ). the motion detection can be from a separate signal , motion sensor , such as an accelerometer or piezoelectric device attached to the oximeter sensor . preferably , however , motion detection is accomplished by analyzing the optical detector signal itself . fig6 illustrates a typical qualified blood pulse . the pulse has a rising side 46 , and then , after peaking , has a slowly trailing side 48 . the derivative of this signal is calculated in microprocessor 2040 of fig2 of the pulse oximeter . a plot of the derivative is also shown in fig6 for the blood pulse . the derivative has a rising portion 50 corresponding to portion 46 of the pulse . after the peak of the pulse , the derivative of the signal rapidly progresses from a positive peak 52 to a negative peak 54 , and then slowly approaches zero again . the height of the positive peak of the derivative signal , a , and the height of the negative peak , b , have been observed to have an a / b ratio of greater than 1 - 1 . 4 for a typical blood pulse . motion artifact , on the other hand , typically has a 1 / 1 ratio . accordingly , the oximeter of the present invention , after determining the derivative of the pulse signal , calculates the ratio of a / b and compares it to a threshold to indicate whether it is a blood pulse signal or a motion signal pulse . preferably , the threshold is in a range of 1 . 0 - 1 . 4 . in a preferred embodiment , a ratio of 260 / 256 is used , which equals 1 . 0196 / 1 . the selection of the exact threshold is tradeoff between rejecting good pulses and rejecting motion . a ratio of 1 . 4 has been observed to reject approximately 95 % of motion artifact , but may also reject some good pulses as well . the ratio of 1 . 0196 provides a conservative level to retain most qualified pulses , will giving a good level of rejection of motion artifact . fig7 is a flowchart for the software routine for determining if a pulse is due to motion . when the routine is called , it first determines the derivative of the pulse signal ( step p ). next , the ratio a / b of the positive to negative peak of the derivative signal is determined ( step q ). if the ratio is less than 1 . 0196 / 1 ( step r ), the signal is presumably a motion pulse . if it is greater , it is an indication that the pulse is not motion ( either qualified or noise pulse ) ( step s ) and there is a return from the subroutine . an optional second or alternative motion test may be used in addition to or in place of the ratio test . it has been observed by the inventors that for a motion signal , there will be correlation of the pulses in the infrared and red channels . noise , on the other hand , tends to be uncorrelated , with different values in the ir and red channels . the correlation of the ir and red pulses are thus determined ( optional step s ) and compared ( optional step t ), and if they are not correlated , the pulse is presumably noise , and there is a return from the subroutine . if the infrared and red pulses are correlated , this is an indication that the pulse is due to motion , and a motion flag is set ( step u ), and there is a return from the subroutine . alternately , a different motion test could be used . for instance , the saturation value of a pulse could be determined using the ratio of ratios , as is well known in the industry . this calculation can be done for several different parts of the pulse . for a qualified blood pulse , the values should be approximately the same . if the values differ , it could be motion or noise . the correlation test could then be run to determine if it is noise or motion . as will be understood by those familiar with the art , the present invention may be embodied in other specific forms without departing from the spirit or essential characteristics thereof . for example , only a single one of the motion tests of fig8 could be used , or the use of a piezoelectric accelerometer sensor could be substituted for the optical signal analysis in order to determine whether a motion signal is present . accordingly , the disclosure of the preferred embodiment of the invention is intended to be illustrative , without limiting the scope of the invention which is set forth in the following claims .
a pulse oximeter which modifies the alarm condition when motion is detected . basically , if the lack of a pulse is determined to be as a result of motion artifact , the generation of an alarm is postponed . in addition , the display indicates that motion is present and that the last reading is questionable due to the presence of motion . the invention also determines if motion artifact is present from the pulse oximeter detector signal itself . the ratio of the positive and negative peaks of the derivative of the pulse signal are compared to a motion / blood pulse threshold .