Abstract:
A system and method of identifying and removing artifact from radio frequency noise from biopotentials identifies epochs contaminated with radio frequency noise. Contaminated epochs are then replaced with recent uncontaminated epochs stored in a buffer, depending on the current level of artifact and the availability of suitable data. Discontinuities arising at the beginning of the replaced epochs are smoothed by means of a windowing function.

Description:
CROSS REFERENCE TO RELATED APPLICATION 
   This application claims priority under 35 U.S.C. 119(e) to U.S. Provisional application Ser. No. 60/299,983, filed Jun. 21, 2001. 

   BACKGROUND OF THE INVENTION 
   Patient monitors that acquire and process electroencephalographic (EEG) signals are commonly used in surgical settings to monitor the patient&#39;s state or hypnosis and sedation. The EEG is characterized by amplitudes in the microvolt range and frequencies in the 0-50 Hz frequency band. The use of processed EEG can be impaired by radio frequency electrical noise in the operating room environment. It is common surgical practice for a surgeon to use electrosurgical devices as cutting and coagulating tools. Electrosurgical devices typically use AC voltages in the 500 KHz to 3 MHz frequency range. Typical amplitudes may be 100 to 5000 volts. The application of the electrosurgical scalpel frequently causes electrical arcing, generating wide-band electrical noise. In addition, the electrosurgical waveform may be modulated by switching it on and off at a certain duty cycle. This modulation also generates wide-band electrical noise. Electrical noise arising from electrosurgical devices are easily picked up by other monitoring devices in the operating room. Due to their large amplitude and wide-band frequency characteristics, electrosurgical devices are a major source of operating room electrical interference. 
   SUMMARY OF THE INVENTION 
   The present invention provides a system and method of identifying and removing artifact from radio frequency noise from biopotential signals. Biopotential signals are divided into epochs and epochs contaminated with radio frequency noise are identified. Epochs with radio frequency noise are replaced with epochs without such noise. In order to avoid errors in the process, each epoch must be identified by two different artifact identification techniques as containing radio frequency noise. Discontinuities arising at the beginning of replaced epochs are smoothed by means of a windowing function. 

   
     BRIEF DESCRIPTION OF THE DRAWINGS 
       FIG. 1  is a block diagram EEG analysis with electrosurgical artifact detection. 
       FIG. 2  is a circuit diagram of electrosurgical artifact detection circuit used in the system of FIG.  1 . 
       FIG. 3  is a flow chart of the steps for performing RMS sudden change of the present invention. 
       FIG. 4  is a representation of an epoch data structure used in the present invention. 
       FIG. 5  is a flow chart of the steps for performing slew rate detection of the present invention. 
       FIG. 6  is a flow chart of the steps for performing artifact classification of the present invention. 
       FIG. 7  is a flow chart of the steps for performing epoch replacement of the present invention. 
       FIG. 8  is a graph of a half Hanning window. 
   

   DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS 
     FIG. 1  shows an electroencephalographic (EEG) analysis system. This system consists of a set of electrodes that are positioned on the head of a patient (not shown) to be monitored. Preferably at least three electrodes are used: a measuring electrode  10 , a reference electrode  20  and a ground electrode  30 . In a preferred embodiment the electrodes are silver/silver chloride electrodes, but any type of biopotential electrode may be used. An amplifier  40 , which in a preferred embodiment is a differential amplifier, amplifies the voltage difference between the measuring electrode  10  and the reference electrode  20 . This voltage difference is referred to as the EEG signal. The ground electrode  30  is connected to the amplifier ground to provide a common voltage baseline for the amplifier  40 . The amplifier  40  may also filter the EEG signal obtained from the EEG electrodes  10  and  20 . The output of the EEG amplifier  40 , the EEG signal, is provided as an input to an analog/digital converter  45  which samples the analog output from amplifier  40  and converts it into a digital sequence for subsequent computer analysis. The amplifier  40  is isolated from earth ground  90  by a patient isolation circuit  80  to protect the patient from electric shock hazard. In the preferred embodiment patient isolation circuit  80  is a high isolation transformer. The output of the analog/digital converter  45  is provided as an input to the isolation circuit  80 , and from there it is input to a computer  50 . The computer  50  may optionally have a display system  60  for communicating to a clinician or technician the various metrics calculated from the amplified EEG signal. The EEG analysis system also incorporates an electrosurgical artifact detection circuit  70  that detects whenever an electrosurgical device is operating, whether the device is in actual surgical use or simply being switched into the operating mode without patient contact. The input to this circuit is the signal from the measuring electrode  10 . The detection circuit  70  must also be isolated from earth ground. The output of this circuit, denoted as ˜ESU, is provided as an input to the isolation circuit  80 , and from there to a computer  50 . 
   Referring to  FIG. 2 , the electrosurgical artifact detector circuit  70  is shown. The electrosurgical artifact detector circuit  70  is sensitive to electro-surgery current passing from a patient lead or leads  10 ,  20 ,  30  through the stray capacitance of the patient isolation circuit  80  as well as other stray capacitances, to the earth ground of the bio-potential monitor enclosure. These currents constitute a common mode signal. The current is also sensitive to voltage differences between the patient measuring electrode  10  and patient ground electrode  30 . These voltages constitute differential mode signals. The electrosurgical artifact detection circuit  70  is capacitively coupled to the measuring electrode lead  10  in order to provide sensitivity to high frequency interference only. In the present invention, electrosurgical artifact detection circuit  70  will detect electrosurgical artifact within a range of 100 KHz and 3 MHz. As can be seen in  FIG. 2 , the base of a first stage transistor,  92 , is capacitively coupled through capacitor  91  to a patient lead  10  while the emitter of this transistor is connected to the local, isolated, ground  93 . The local, isolated ground  93  has capacitance to earth ground. A second transistor  94 , is directly coupled to the first stage so as to provide an output capable of interfacing with a logic level input. 
   The operation of the first stage is novel in that it uses RF energy to turn off the first transistor  92 . Other amplitude modulation detectors use RF current to turn on the detector. Using the RF energy to turn off the first transistor is advantageous for this application, as there is no need to extract information from the RF being detected, it is simply the presence of RF to which this detector is designed to respond. The advantage here, is that it is possible to set a threshold current level to which the detector will respond. Since the supply voltage is regulated and the base emitter changes only 2.2 mv per degree centigrade, the base bias current is supplied from the regulated supply to the base of the first transistor  92 , via a single resistor  95 . In the preferred embodiment the current is approximately 20 micro-amperes. This current is fixed and varies little with temperature. Thus, the minimum sensitivity level of the detector circuit  70  is easily set by the selection of the base bias resistor  95 . 
   The operation of the electrosurgical artifact detection circuit  70  will now be described. Transistor  92  is normally on, keeping transistor  94  off. When an electrosurgical unit generator is operated and the peak RF current through the patient leads into the detector exceeds the base bias current, transistor  92  turns off on half cycles of the RF from the electrosurgical unit generator. Any current higher than the base bias current will also cause this result. When transistor  92  turns off, transistor  94  turns on and this information is detected by a logic circuit and passed to the controller processing the data stream. Even if the output of transistor  94  is not sampled at a rate equal to or higher than the RF frequency of the electrosurgical unit there are a half million chances per second to notice that RF current is present. 
   In addition to detecting electrosurgical artifact by using the circuit of  FIG. 2 , various digital signal-processing (DSP) techniques may also be used to detect artifacts. These techniques may be designed to detect different characteristics of the electrosurgical artifact. In a preferred embodiment, the present invention uses two such DSP techniques. 
   Electrosurgical artifact typically contains high frequency (HF) noise. This HF noise is presumed to arise from arcing that occurs when an electrosurgical device is in close proximity, but not in contact with, grounded tissue. The dose proximity creates a spark gap, which may be jumped if the voltage difference is high enough. This high frequency noise may be continuous, lasting 30 seconds or longer. In order to detect this HF noise, the present invention examines the root mean square (RMS) power of the EEG signal for changes that are characteristic of this type of HF noise. 
   In the present invention, this RMS sudden change artifact-processing process is applied to one epoch of data at a time. An epoch length of one second is preferably used, and each new epoch overlaps the previous one by 50% (a new epoch every half second). 
   The process compares the 30 th  percentile of the log RMS power values of the entire epoch of data to the maximum of log RMS power values of successive short time slices within the epoch. Epochs are marked as potentially containing artifact when the difference in log RMS power values is greater than a threshold. A software artifact flag, the Sudden Change Flag, is used to store this information. A separate artifact flag is maintained for each epoch. The 30 th  percentile of the values in the long buffer is used to reduce the effect of high power noise spikes; this has the effect of ignoring the 70% of values with the highest power. This technique is effective for signals with intermittent periods of noise. However, the use of a value derived from the data means the artifact detection process will adapt to continuous high frequency noise. Thus, artifact detection will eventually fail if the high frequency noise is present in more than 70% of the epochs from which the values in the long buffer are computed. For this reason, the buffer length should be set to 1.5 times the longest expected period of continuous artifact. In the present invention, a buffer length of 1.5 minutes is used, enabling up to 1.05 minutes of artifact to be handled correctly (70% of 1.5 minutes). This process will now be described with reference to FIG.  3 . 
   In step  100  the system samples the EEG signal at 128 samples per second. The sample signal is then filtered in step  101  using a 4 th  order high pass Butterworth filter with a −3 dB frequency at 35 Hz. For each epoch of sampled data, the system calculates the log of the total RMS power in step  102  and uses this value to update the long buffer in step  103 . The long buffer is a first in, first out (FIFO) buffer, in which the oldest value is deleted when the newest value is added. The long buffer contains all the 1 second RMS power values from the most recent 1.5 minutes of data. For each epoch of sample data the log of the total RMS power is also calculated for each of the consecutive 8 sample periods in each epoch in step  105 . In step  106 , the values are stored in a second FIFO buffer. This second buffer is referred to as the short buffer and contains all the eight-sample RMS power values from the most recent 1.5 minutes of data. 
   In step  108  the difference between the 30 th  percentile of values in the long buffer and a maximum of the values in the short buffer over the last 30 seconds is computed. This difference is compared to an RMS sudden change threshold in step  109 . In preferred embodiment of the present invention, the threshold value is 0.4. The threshold is selected such that there is acceptable variance in the biologic process being measured. If the difference is greater than the sudden change threshold, a sudden change flag  146  is set for the current epoch in step  110 . Otherwise the sudden change flag  146  is cleared for the current epoch in step  111 . 
   A second method of detecting electrosurgical artifact is shown in FIG.  5 . This method is based on the rate of change of the sampled data, commonly known as the slew rate. An artifact flag (the slew rate flag) is used to store this information, with a separate slew rate flag being maintained for each epoch. This method operates by first sampling the EEG signal at 1024 samples per second in step  150 . In step  151 , each epoch of sample data is filtered using a band pass filter. In a preferred embodiment the filters are comprised of two 4 th  order Butterworth filters with one being a high pass filter with a −3 dB frequency at 200 Hz and the other being a low pass filter with a −3 dB frequency at 300 Hz. Next, in step  152 , a sample-by-sample slew rate is calculated and the results for the entire epoch are stored in a buffer. In step  154  the maximum slew rate value in the buffer is calculated and then in step  155  such maximum slew rate in a current epoch is compared with a slew rate threshold, which in a preferred embodiment is 100 microvolts/sec. If the maximum slew rate exceeds the slew rate threshold, a slew rate flag  144  is set for the current epoch  140  in step  156 . Otherwise, it is cleared for the current epoch in step  157 . Finally, the slew rate buffers are cleared in preparation for processing the next epoch in step  158 . 
   The method of artifact processing used in the present invention dynamically filters the EEG signal, effectively removing the electrosurgical artifact from the ongoing EEG signal. For this reason, the method of electrosurgical artifact filtering is applied only when an electrosurgical artifact is detected in a particular epoch by both the artifact detection circuit  70  and at least one of the two software detection methods. This process of electrosurgical artifact classification will now be described with reference to FIG.  6 . 
   The EEG signals are typically analyzed epoch by epoch, and the present invention preferably uses an epoch length of 1 second. For this reason, it is desirable to classify the EEG as to whether or not each epoch contains electrosurgical artifact. For this reason, the output signal ˜ESU is typically used to set a flag. In step  200  the ESU flag is set by the ˜ESU signal output of the electrosurgical artifact detection circuit  70 . After each epoch of EEG signal is acquired, the electrosurgical unit flag is examined in step  201  in order to determine whether it is set to a logic zero. If the electrosurgical unit flag is set, the hardware electrosurgical artifact (HESA) flag  142  is then set in step  202 . If the electrosurgical unit flag is not set then the HESA Flag  142  is cleared in step  203 . Regardless of the electrosurgical unit flag value, it is cleared in step  204  before acquisition of the next epoch begins. 
   In order for an epoch to be classified as containing electrosurgical artifact, the HESA flag must be set. In addition, either the slew rate flag  144  or the sudden change flag  146  must be set. If this combination of conditions is found to be met in step  205 , the artifact flag  147  is set for the current epoch  140  in step  206 . The HESA flag  142  is also cleared in step  208 . 
   The essential function of the artifact-processing process is to replace epochs containing electrosurgical artifact with previously acquired artifact-free epochs. EEG is generated by cerebral activity, which in the strictest sense is a non-stationary process. However, metrics derived from the EEG using various signal processing measures such as power spectral analysis, bispectral analysis and time-domain analysis are robust to the assumption that cerebral activity is weakly stationary. For this reason error introduced into the EEG signal by replacing an artifact-contaminated epoch with an artifact-free epoch is small compared to the benefit gained from additional data as long as the epoch used for replacement is from the recent past As the age of the replacement epoch increases, so does the potential introduced error. For this reason, the age of the epoch used to replace the artifact-contaminated epoch is limited in a preferred embodiment of the present invention to no more than 1 minute. 
   Another means of limiting the potential error introduced by data replacement is to perform the replacement only if the proportion of epochs contaminated by artifact in the recent past is relatively large, which increases the importance of each artifact-free epoch to the final result. If artifact replacement is performed when the proportion of artifact-contaminated epochs is small, the potential increased error resulting from artifact replacement is not sufficiently out-weighed by the benefit of additional data. In the present invention, whether or not artifact-contaminated epochs are replaced depends upon the prevalence of artifact of all types. The ratio of non-artifact-contaminated epochs to the total number of epochs in the last minute is called the Signal Quality Ratio (SQR). In a preferred embodiment of the present invention, an electrosurgical artifact-contaminated epoch is replaced only if the SQR is less than 50% (the electrosurgical artifact ratio threshold); that is, if more than 50% of the epochs from the last minute of data have been classified as containing artifact. If an electrosurgical artifact contaminated epoch is not replaced, it is excluded from further processing. 
   Two data buffers are used for the artifact-processing process. The first buffer (the EEG buffer) stores artifact-free EEG signal. The second buffer (the Flag buffer) stores the various artifact flags of the corresponding epochs in the EEG buffer as well as a pointer to the location of those epochs in the EEG buffer. The Flag buffer also stores a replacement flag, which tracks whether or not the epoch has been used for artifact replacement. Only artifact-free epochs are stored in the EEG buffer. While the methods of artifact detection described here are limited to electrosurgical artifact, in practice the artifact detection software will include detectors that are filters for a variety of different types of artifact, such as movement artifact, 60 Hz noise, base-line wander, ECG and pacer artifact, etc. The Flag buffer will contain a flag (the Artifact Flag) indicating whether any artifacts were detected in the corresponding epoch. The artifact flag will generally be set if any of the individual artifact flags are set. In order to be used as replacement data, an epoch must be completely artifact free; that is, the artifact flag must be clear (not set). Alternately, the Flag buffer may contain flags for each of the different artifacts and these may be tested individually to ascertain whether the epoch in question is free of detected artifact 
   The memory requirements of the EEG buffer depend on the maximum age of epochs used for replacement of artifact-contaminated epochs, the electrosurgical artifact ratio threshold, the sampling rate and the data word length. A preferred embodiment of the present invention uses data no older than 1 minute for replacement and an electrosurgical artifact ratio threshold of 50%. Therefore, because neither artifact-contaminated data nor data older than one minute need be saved, the EEG buffer need only be large enough to store 30 seconds of EEG signal. 
   When the acquisition of a new epoch is complete, the Flag buffer is updated so that the electrosurgical artifact and artifact flags and the EEG buffer pointer corresponding to the oldest epoch is shifted out (overwritten), effectively deleting it. If the new epoch is artifact-free, the EEG buffer is also updated to ensure that the buffer contains only the most recent artifact-free epochs. The EEG signal in the EEG buffer is used only once to replace artifact-contaminated epochs. 
   The process for the replacement of epochs that are classified as artifact-contaminated is shown in FIG.  7 . For simplicity, this discussion will be directed to electrosurgical artifact, though those skilled in the art will recognize that this invention may be used with any number of different artifact types. Artifact processing begins after acquisition of the current epoch is complete, the epoch has been classified as to its artifact status (contaminated or artifact-free, both ESA and other artifacts), and the SQR has been updated. First, the ESA flag  148  is checked to ascertain the ESA classification of the current epoch  140  in step  250 . If the ESA flag  148  is not set (is clear), the current epoch  140  is free of electrosurgical artifact. If the artifact flag  147  is also not set as determined in step  253 , the current epoch  140  is artifact-free and may thus be used for processing in step  255  without replacement. If the artifact flag  147  is determined to be set in step  253 , the epoch  140  contains artifact other than electrosurgical artifact, and the epoch is not used for processing and is discarded in step  280 . If the system determines in step  260  that the previous epoch came from the EEG buffer (i.e., it was replaced by this artifact processing process), the transition between the end of the previous epoch and the start of the current epoch is smoothed in step  265  using the process described below. The discontinuity is a result of the two epochs being non-contiguous in time. If it is determined in step  260  that the previous epoch did not come from the EEG buffer, there is no need to smooth the transition between the previous and current epoch. In either event, the current epoch, smoothed or not, is processed to derive the various EEG metrics from it in step  270 . The current epoch may also be displayed on a display device as the ongoing artifact-corrected EEG signal. 
   If the system finds the ESA flag  148  is set in step  250 , the current epoch is contaminate with electrosurgical artifact. The epoch is thus a candidate for replacement if the current level of electrosurgical artifact is high and there is data in the EEG buffer to use for replacement. To this end, the current SQR is compared against the electrosurgical artifact ratio threshold in step  275 . If the SQR is greater than or equal to the electrosurgical artifact ratio threshold, the current epoch is not replaced. The current epoch is marked as artifacted so that it will be excluded from further processing in step  280 . It may also be displayed on a display device as the ongoing EEG signal. 
   If the SQR is less than the electrosurgical artifact ratio threshold, it is next determined in step  285  whether there are epochs in the EEG buffer available for use as replacement epochs. Recall that only non-artifacted epochs are stored in the buffer. In addition, epochs may be used for replacement only once. To ascertain the replacement status of the epochs in the EEG buffer, the replacement flags in the flag buffer are checked. If there are no epochs in the EEG buffer whose corresponding replacement flags indicate that they have not been used for replacement, the current epoch is not replaced, and it will be excluded from further processing in step  280 . It may also be displayed on a display device as the ongoing EEG signal. 
   If there is a non-artifacted epoch in the EEG buffer that has not been used for replacement and the SQR is less than the electrosurgical artifact ratio threshold, the available epoch in the EEG buffer is used to replace the current epoch in step  290 . The replacement epoch is used for output and its replacement flag  149  is set to indicate that it has now been used for replacement. The transition edge between the end of the previous epoch and the beginning edge of the replacement epoch are adjusted in step  265 . The adjusted replacement epoch is processed to derive the various processed EEG metrics from it in step  270 . The adjusted replacement epoch may also be displayed on a display device as the ongoing artifact-corrected EEG signal. 
   When an epoch from the EEG buffer is used to replace the current EEG epoch, a discontinuity may be created between the first sample of the replacement epoch and the last sample of the previous epoch. In order to transition smoothly from the previous epoch to the replacement epoch, the left edge of the (replacement) current epoch will be adjusted by applying a half Hanning window to the left half of the epoch. The half Hanning window as shown in  FIG. 8  is computed as 
         win   i     =       1   2     +       1   2     ⁢           ⁢     cos   ⁢             ⁢             (       π   ·   i         N   2     -   1       )             
 
where N is the number of samples in the EEG epoch and the sample number i=0, 1, 2, . . . (N/2)−1.
 
   The half Hanning window ranges from 0 to 1 as it approaches the middle of the epoch. As a result, the first value in the adjusted epoch will be equal to the last value of the previous epoch. The right half of the adjusted epoch will be identical to the original signal. Note that win 0 =1 and win N/2−1 =0. 
   As a first step, the replacement epoch is copied to a temporary output buffer. SmoothedData i =NewData i    
   
       
       
         
           where i=0, 1, 2, . . . N−1 
           NewData [ ] is the replacement epoch 
           SmoothedData [ ] is epoch to be output 
         
       
     
  
   The half Hanning window is used to smooth the left half of the replacement EEG epoch so that it transitions smoothly between the last value in the previous EEG epoch and the middle of the replacement epoch. 
         SmoothedData   i     =       (       win       N   2     -   i   -   1       ·     (       SmoothedData   i     -     PreviousData     N   -   1         )       )     +     PreviousData     N   -   1             
           where   ⁢           ⁢   i     =   0     ,   1   ,   2   ,       …   ⁢           ⁢     N   /   2       -   1         
           PreviousData     N   -   1       ⁢             ⁢             ⁢   is   ⁢           ⁢   the   ⁢           ⁢   last   ⁢           ⁢   value   ⁢           ⁢   in   ⁢           ⁢   the   ⁢           ⁢   previous   ⁢           ⁢   epoch     ;       
 
   The smoothed epoch in the temporary buffer SmoothedData is then output as the current epoch. 
   While the foregoing invention has been described with reference to its preferred embodiments, various alterations and modifications will occur to those skilled in the art. All such variations and modifications are intended to fall within the scope of the appended claims.