a preferred embodiment of the invention will now be described with reference to fig4 . fig4 is similar to fig7 of u . s . pat . no . 5 , 348 , 005 , which patent is hereby incorporated herein by reference . fig4 is a circuit diagram of the oximeter test instrument according to an embodiment of the invention . as shown in fig4 the circuitry includes a pair of photo diodes represented by the reference numeral 10 which feed a pulse separator and edge timing circuit 12 , a pair of dc multipliers m1a , m1b which are coupled to the pulse separator and edge timing circuit 12 via a pair of switches s1a and s1b , respectively , a pair of ac multipliers m2a and m2b which are connected to receive the outputs of dc multipliers m1a and m1b , respectively , a multiplier m3a which is coupled to receive one of the outputs of ac multipliers m2a and m2b depending on the position of switch s2b , and a switch s2a which is coupled to selectively pass one of the outputs of dc multipliers m1a and m1b . as shown in fig4 switches s1a and s1b are user controlled , whereas switches s2a and s2b are controlled according to an output of pulse separator and edge timing circuit 12 . as will be discussed in greater detail below , switches s2a and s2b are controlled in accordance with detected ir flashes . the circuitry shown in fig4 further includes an amplifier a2 having an inverting terminal (-) which receives the signal passed by switch s2a , an amplifier a3 having an inverting terminal coupled to receive the output of amplifier a2 summed with the output of multiplier m3a , a servo amplifier a4 having a non - inverting terminal (+) coupled to receive the output of amplifier a3 and coupled to the drain of fet q1 which has its source connected to ground and its gate coupled to receive an output of pulse separator and edge timing circuit 12 , and an inverting terminal of amplifier a4 is coupled to receive an output of a pulse amplifier with baseline restore circuit 14 . the circuit 14 is coupled to a photo diode 18 which detects light emitted from led bar 16 . in addition , the circuit of fig4 includes a driving transistor q2 , an led bar 16 , an ambient light simulation circuit 19 and a computer 20 for controlling the dc multipliers m1a , m1b , the ac multipliers m2a , m2b multiplier m3a and the ambient light simulation circuit 19 via a 12 - bit data line bus 22 . the ambient light simulation circuit 19 includes a multiplier m3b which attenuates a dc reference signal under control of computer 20 , an amplifier a5 having its non - inverting terminal (+) connected to receive an output of multiplier m3b , and a driving transistor q3 coupled between the led bar 16 and the output of amplifier a5 . fig4 is an implementation where the coupling to the oximeter is optical , using the oximeter &# 39 ; s probe leds as a cooperating half of the led current drive current detector , and using the oximeter &# 39 ; s probe photo diode as the cooperating half of a current driver opto isolator driving into the oximeter &# 39 ; s photo diode amplifier input . point &# 34 ; y &# 34 ; of fig1 is thereby similar to pulse separator 12 , and point &# 34 ; x &# 34 ; of fig1 is similar to the input to amplifier a4 , as shown in fig4 . it will be understood from the following that this invention applies to the modulation of the captured led drive waveforms , the exact means of their capture is not of importance , and may be any of those described above or known to the art . likewise , the current driver output configuration choice is not of consequence , and may be any of the ones described above or known to the art . the operation of the circuitry shown in fig4 will now be described . in general , the circuitry of fig4 uses one photodetector to capture the red and infra - red pulses from the pulse oximeter , and another photodetector which is filtered such that it captures infra - red pulses only . the pulse separator and edge timing circuit 12 receives the outputs of the photo diodes 10 , and in response thereto outputs four signals . a first signal ir switch ( represented by dotted lines ) is a switch control signal for ir . this signal controls switches s2a and s2b , and is used to select the ac and dc corresponding to the infra - red transmission pulse wave . that is , when the pulse separator and edge timing signal receives an ir , this signal is supplied to switches s2a and s2b to select the ac and dc corresponding to the infra - red transmission pulse wave . at all other times , the red values are selected so switches s2a and s2b are in the positions shown in fig4 . a second signal output by circuit 12 is the red plus infra - red ( r + ir ) pulses . as shown in fig4 this signal is supplied to the gate of fet q1 . a third signal provided by circuit 12 is an electrical analog to the pulse oximeter red flash ; this signal is provided to multiplier m1a via switch s1a . the fourth signal provided by circuit 12 is an electrical analog to the pulse oximeter infra - red flash ; this signal is supplied to multiplier m1b via switch s1b . the circuit shown in fig4 includes three multiplier chips m1a and m1b , m2a and m2b , and m3a and m3b . each of these chips contains dual multiplying digital - to - analog converters ( dacs ) with internal output amplifiers . this eliminates the amplifiers and their associated components from the circuit board , and brings them within desired multiplier accuracy specifications . the multipliers multiply by a computer - set value between 0 and - 1 ; that is , the multipliers are both attenuating and inverting . dual 12 - bit multipliers are used for setting the finger density ( dc attenuation ) and creating the blood pressure wave form ( ac attenuation ); multipliers m1a , m1b and m2a , m2b , respectively . a single dual 8 bit multiplier is used to attenuate the ac wave ( multiplier m3a ) and control simulated ambient light ( multiplier m3b ). the switches s1a , s1b allow selection between the analogues of the pulse oximeter flashes ( i . e ., ir or r ) and a fixed voltage ( e . g ., - 5 v ) as the dc references . when receiving the pulse oximeter light analogues , switches s1a , s1b are in the position shown in fig4 and the multipliers m1a and m1b receive the r and ir analogues , respectively . the attenuated dc reference voltage ( i . e ., the output of multipliers m1a and m1b ) becomes the reference for multipliers m2a and m2b . further , the attenuated dc reference voltage is inverted by amplifier a2 . the multipliers m2a and m2b serve to create the r and ir arterial waveforms . the ir waveform has a peak multiplier setting of 1000 , and the r waveform has a peak multiplier setting which varies from 400 to 3500 . multiplier m3a receives the output of either ac multiplier , depending on the position of switch s2b , and attenuates the output passing through switch s2b from its maximum value down to zero . this attenuation simulates the strength of the blood pressure wave . for example , the value zero would correspond to no heart beat . this attenuation is also for the pulse oximeter pulse loss detection test , and should allow demonstration of the pulse oximeter output in response to variance from the highest to the lowest ac / dc ratio . amplifier a2 , inverts the positive dc levels out of multiplier m1 . the inverted dc , which is now negative , is then summed with the positive ac from multiplier m3a . the dc is a negative voltage which will be proportional to base brightness , and the ac is a positive voltage representing attenuation of the blood pressure wave . the r1 / r2 resistor ratio at the input of amplifier a3 sets the maximum ac at 25 % of the dc applied to this summing and inverting stage . the actual ac is always less than this maximum , as the largest ac signal is only 3500 / 4096 times the dc out of multiplier m1a . the inverted and summed ac and dc from amplifier a3 are applied to amplifier a4 through resistor r3 and are chopped by q1 . q1 is switched by the pulse oximeter r + ir light pulse ; during the pulse , q1 is off and amplifier a4 is driven by amplifier a3 . on the other hand , when q1 is on , the led current ( brightness ) is commanded to be zero . amplifier a4 sets the brightness for the led bar 16 to be proportional to the input voltage of amplifier a4 when q1 is turned off . the led bar 16 is coupled to photo diode 18 which detects the light generated and feeds it back to amplifier a4 . this is done to ensure that the led bar output is linear . the test instrument controls the light output directly , rather than depending on the linearity and temperature stability of the led versus the led current . the ambient light simulation circuit 19 includes a multiplier m3b , an amplifier a5 and a driving transistor q3 and serves to generate a fixed current to the led bar in addition to the red and infra - red pulses in order to simulate ambient light . as shown in fig4 the multipliers m1a , m1b , m2a , m2b , m3a and m3b are controlled by computer 20 . this can be done using a simple program for setting the fixed parameters and then manipulating the r / ir ratio . the various control parameters for the multipliers are described below . in order to provide the dc , or non - arterial , level , the circuit includes the multipliers m1a and m1b which cover the range from opaque to transparent , and is settable by the computer 20 over this range in 4 , 096 steps . also , computer 20 is able to set the red and infra - red dc attenuation ( i . e ., multipliers m1a and m1b ) separately . as described above , multiplying dacs m1a and m1b are used as fixed attenuators of the red and infra - red light flash analogues . however , in the present invention , multiplying dacs m1a and m1b are conveniently manipulated by computer 20 to modulate in addition to attenuate . this provides the non - arterial wave modulation . the modulation percent ratios for r / ir set the oxygen level of the non - arterial pulse , and the non - arterial pulse amplitude and waveshape are under control of computer 20 , similar to the arterial waves . thus , by changing the percent ratio for r / ir , any desired oxygen level can be simulated for the non - arterial pulse . further , by varying the percent ratio for r / ir , the present invention is able to simulate a range of oxygen values whereby a pulse oximeter can be tested at various oxygen values in that range , instead of at just one set oxygen value . in a similar manner , various oxygen values can be simulated for the arterial wave . the ( now motion modulated ) outputs of m1a and m1b are fed respectively to multiplying dacs m2a and m2b where they are further modulated to simulate the arterial red and infra - red waveforms . in order to provide the ac , or arterial , level , the circuit includes the multipliers m2a and m2b . as indicated above , these multipliers create the arterial r and ir waveforms , with the ir waveform having a peak multiplier setting of 1000 , and the r waveform having a peak multiplier setting which varies from 400 to 3500 . because of the original intent of the design , the relative amplitudes of each wave &# 39 ; s modulation will be affected by the fact that the m1 dacs are summed with the output of the m2 dacs at amplifier a3 . obtaining an expected output means that the software wave amplitudes applied to the m1 dacs must be scaled accordingly . the arterial ac to dc ratio corresponds to the strength of the blood pressure wave , and this ratio is simulated by multiplier m3a . one of the tasks of a pulse oximeter is to sound an alarm if the blood pressure wave is lost . therefore , an important question is : &# 34 ; at what level of wave weakness is the alarm tripped ?&# 34 ; the computer 20 is able to set the wave amplitude ( i . e ., multiplier m3a ) from zero up to approximately 20 % of the dc level in 256 steps . a blood pressure wave corresponding to one heartbeat is generated by the computer 20 feeding the ac multipliers m2a , m2b a series of 64 numbers corresponding to blood pressure amplitude , starting at zero and returning to zero . the series of 64 numbers then repeats to form the next beat . the 64 numbers are selected such that if the series of numbers were plotted against time , then the resulting curve would be a blood pressure wave corresponding to one heart beat . a simulated heart rate is established by the computer 20 setting the time between the presentation of each of the 64 numbers . for example , if they are presented to the multipliers 1 / 64th of a second apart , the full wave takes one second to generate , corresponding to 60 beats / minute . the computer 20 can readily set the time between multiplier settings so that any reasonable simulated heart rate can be established . as indicated above , the ambient light simulation circuit 19 serves to drive the led bar 16 in order to simulate ambient light . computer 20 controls multiplier m3b of circuit 19 so as to allow for a settable minimum dc current through the led bar 16 . in an alternative mode of operation , note that switches s1a and s1b can be set in the alternate position to that shown in fig4 thereby providing a dc input to the modulators m1a and m1b . in this mode , the double modulated waves are created as continuous waves and are turned into the required pulse amplitude modulation signal format by q1 . the combined modulating signal is chopped by q1 to produce the final double modulated result . the above is , therefore , a second example of the many ways the functions of fig2 or 3 may be achieved by those skilled in the related art . as described above , the new simulation process of the present invention is adaptable to existing hardware in this instance by implementation of appropriate software in computer 20 . the foregoing has shown how motion may be simulated by modulating the red and infra - red pulses of an oximeter with more than one frequency or wave simultaneously . there are uses for this technology other than for simulating motion simultaneous with arterial oxygenation . one such use is in simulating respiration effects simultaneously with arterial oxygenation . to demonstrate how this technology can simulate respiration , it is necessary to first explain how respiration can be a frequency based parameter that can be detected by an oximeter . consider a person taking in a breath . the air being pulled into the lungs is full of oxygen . this oxygen starts to transfer to the blood , and as it does so , the rate of transfer drops . next , the air in the lungs is expelled , and a new breath taken with a fresh full supply of oxygen . again , oxygen transfer increases to the rate corresponding to the initial new breath . this process results in a fluctuation of blood oxygen at the frequency of the breath rate ; that is , at the respiration rate . in theory , an oximeter able to detect blood oxygen can extract the oxygen variation due to respiration using appropriate signal processing . in fact , at least one oximeter appears to have achieved this feat . more may be expected to follow . in general the technique takes advantage of the fact that the oximeter sees oxygen variations at both the heartbeat rate and the respiration rate . the heartbeat rate and the respiration rate are different , with the former usually being the higher of the two . this difference in rate makes it possible to use modern signal processing techniques to extract the two frequencies from the oximeter sensor signals . from the above it can be seen that the present invention , which can inject signals of a second frequency wave into the oximeter , in addition to the arterial heartbeat wave , ( plethysmographic wave ) is ideally adapted to respiration simulation . recall that the oxygenation of arterial blood is calculated from the normalized ratio of red fluctuation divided by the normalized ratio of infra - red fluctuation , or : ## equ1 ## where r is a value related to blood oxygen , and in the usual oximetry case , to arterial blood oxygen . the values r ac and r dc are the &# 34 ; ac &# 34 ; and &# 34 ; dc &# 34 ; values of the red wave , whereas ir ac and ir dc are the &# 34 ; ac &# 34 ; and &# 34 ; dc &# 34 ; values of the infra - red wave . it can be seen that if it is desired to introduce a fluctuation into r , the arterial blood oxygen value , then that fluctuation must be introduced into the numerator , the denominator , or both , as may be convenient . if fluctuation is introduced into both , then the fluctuations in the numerator and denominator must be different , or they will cancel out . it should be recalled that motion makes non - arterial oxygen detectable , at its own r value , separate from arterial oxygen . by contrast , respiration introduces a fluctuation into the arterial oxygen value only . the technology of the present invention allows manipulation of either the numerator , the denominator , or both . for example , the present invention can replicate the process used to simulate motion , but suppress the infra - red second frequency modulation signal . this results in a variation of only the numerator in the r equation at that frequency , because only the red second frequency modulation signal is used , which translates to a variation in the oxygen value measured by the oximeter at that frequency . the implementation shown in fig4 allows the oxygen variation thus achieved to be set at a desired frequency below the simulated heart rate , and at an amplitude commensurate with that expected due to respiration . the implementation shown in fig4 also allows frequencies higher than heart rate to be selected , as is usual in motion simulations . in fact , this particular implementation has a frequency range for a second modulation signal that goes from , for example , 0 . 333 hz to 75 hz . however , with changes common to the art of frequency synthesis , the above range could be readily extended at both ends . alternatively , the present invention can replicate the process used to simulate motion , but suppress the red second frequency modulation signal . this results in a variation of only the denominator in the r equation at that frequency , because only the infra - red second frequency modulation signal is used , which translates to a variation in the oxygen value measured by the oximeter at that frequency . the implementation shown in fig4 allows the oxygen variation thus achieved to be set at a desired frequency below the simulated heart rate , and at an amplitude commensurate with that expected due to respiration . alternatively , both numerator and denominator of the r equation could be set to a respiration rate , keeping in mind that their amplitude values would have to be different so as not to cancel out . as mentioned above , the multiple modulations of the red and infra - red oximeter signals may be accomplished either entirely mathematically by computer or by computer controlled hardware in various configurations , or combinations thereof , one such combination being presented herein . it is possible to simulate arterial oxygen , non - arterial oxygen and respiration simultaneously . the hardware architecture of fig4 can be used for such a simulation . however , at least 2 of the 3 frequency wave values would have to be combined in the computer , as the hardware is designed to support only 2 separate signals for hardware based modulation . as an aid to understanding of the present invention , think of the red and infra - red oximeter impulses as carriers at two frequencies , much as am radio waves are carriers at different frequencies , wherein each frequency is capable of carrying voice and music . because the carrier frequency is much higher than the frequencies of the information impressed on it , it can reproduce them with fidelity . think of a quartet of musical instruments , or a whole orchestra . a trained listener can extract the melody of each instrument from the radio reproduction , even though they were all mixed on the same carrier . similarly , the present invention impresses the waves representative of plethysmographic action , motion and respiration onto the red and infra - red carriers ; slightly differently on each depending on the desired effect . the oximeter , then , plays the role of the skilled listener , extracting the appropriate information from each . there may be other frequency based parameters capable of detection through the oximetry sensing method besides arterial oxygen , non - arterial oxygen , and respiration . if so , it will be apparent to one skilled in the art that the multiple frequency modulation technology of the present invention is able to simulate them . it is contemplated that numerous modifications may be made to the simulator of the present invention without departing from the spirit and scope of the invention as defined in the following claims .
a problem in pulse oximetry is discriminating between arterial and non - arterial oxygen . non - arterial oxygen can become detectable by an oximeter when a patient moves , obscuring the oximeter &# 39 ; s measurement of arterial oxygen at critical times . recent advances in pulse oximetry have made it possible to make the discrimination between arterial and non - arterial blood oxygen values . to allow manufacturers , hospitals , and medical researchers to evaluate the new oximetry technology , and evaluate oximeters which use it , new simulation technology is presented which can simulate simultaneous arterial and non - arterial blood oxygen on demand , with precision as to oxygen value , waveform amplitude , and waveform frequency . this invention provides the required simulation by double amplitude modulating the red and infra - red oximeter pulses .