What’s in Photoplethysmography Data? A Look at the Interaction Between Sensor Performance and Algorithms

Whether a sensor can provide reliable data depends on the target information, the algorithm deployed, and the specific details of a given use case. Optical biosensing has become a mainstream feature in smart watches and fitness wearables. This article will provide an overview of the interaction around photoplethysmography (PPG) data collected by optical biosensors.

PPG measures the reflected (back-scattered) or transmitted light through tissue to investigate the variations in blood volume which occur with each heartbeat. Researchers and physicians have derived information including heart rate, respiratory rate, oxygen saturation, blood vessel viscosity, venous reflux, cold sensitivity, blood pressure, and cardiac output by processing PPG data with different algorithms. Whether the captured PPG data can provide all of these insights reliably depends on many factors.

In a previous article on optical biosensors, we presented the following equation:


where SNR is the signal-to-noise ratio of the PPG data, ILED is the LED current, CTR is the transfer ratio between LED current and photodetector (PD) current, PI is the perfusion index of the subject, and NTX, NPD, and NRX are the noises in the transmitter (LED driver), PD, and receiver (analog-to-digital conversion), respectively.


Figure 1. Smart watches and other wearables designed with optical biosensors can provide a wealth of health insights via heart-rate and blood-oxygen monitoring.

When we take SNR as a measure of PPG data reliability, we see that the measurement environment in a specific end-use and the underlying PPG system design play fundamental roles in assuring reliability. Consider these parameters:

  • Optical configuration, which includes the wavelength of the light(s), the efficiency and field of view of the LED(s), the responsiveness of the PD, and the design of the optical path. Each of these factors contributes to the CTR of the sensing system.

  • Subject's skin tone, skin temperature, blood perfusion, and location of the sensor on the body all contribute to the PI. For most use cases, the subjects' skin characteristics are beyond the control of the designers. Although medical practices typically take PPG data from fingers and ear lobes, those locations may not be convenient for ambulatory and long-term monitoring. Consequently, many designs expect and accept lower PI values.

  • Optical components and system design ultimately control the noises in a PPG system. In most wearable applications, NTX and NRX can be minimized by selecting an analog front-end with better intrinsic signal-to-noise performance. This is particularly important as CTR is typically a small number, especially when miniaturization or other industrial design considerations may constrain optical design. As such, the noise terms in the equation's denominator begin to dominate.

  • Boosting SNR by increasing LED power consumption. When all else fails, the equation assures designers that they can still get reliable PPG data by boosting ILED, which, of course, substantially increases system power consumption. Furthermore, excessive power consumption may lead to other complexities in the system that compromise data reliability.

Whereas poor SNR represents a lack of data reliability in general, other factors such as motion artifacts may affect the reliability of different PPG data-derived information to different extents. To explain this, we shall look at a few examples of information that could be embedded in the PPG data. As the discussion below illustrates, it is useful to examine PPG data in the frequency domain.

Heart Rate or Pulse Rate

The most prevalent application of PPG is for monitoring heart rate, which is also the most reliably obtainable data (Figure 1 conveys average target heart rates by age). The human heart rate is below 3Hz. That it is largely tonal means that it is a narrowband signal and, therefore, relatively straight-forward to recover via algorithms applied to most PPG data from most background noises. In use cases where motion is expected, higher bandwidths may be used to allow algorithms to differentiate true PPG signals from in-band motion artifacts using the features of a true PPG wave shape.

Target Heart Rate

Age in YearsAverage Maximum Heart Rate in Beats Per MinuteTarget Heart Rate Range in Beats Per Minute
4018090 to 153
4517588 to 149
5017085 to 145
5516583 to 140
6016080 to 136
6515578 to 132
7015075 to 128

Source: American Heart Association

Coronary Health information in Acceleration Plethysmogram (APG)

Because PPG measurements are low cost and non-invasive, many researchers have focused on using PPG data, taken under clinical settings, to diagnose peripheral vascular diseases such as atherosclerosis, where fatty deposits reduce the diameter of an artery.

A common way to process PPG data uses its second derivative, and the resulting waveform is often called an APG (see Figure 2). Over the course of many studies, researchers have categorized the shape of the APG waveform to help diagnose a subject's health and risk of coronary disease. Techniques in these studies include information at frequencies, often from 0.05Hz to 20Hz, which are significantly higher than fundamental heart rate. And because higher frequency components are much weaker, these PPG measurements require much higher SNR with less reliance on low-pass filters for signal conditioning. As examples, simple analyses of APG features include:

  • Arterial stiffness. The magnitude of the ratio b/a of the APG relates to the distensibility of the peripheral artery and may be a non-invasive index of atherosclerosis and arterial distensibility. Others have noted that c/a and d/a ratios reflect decreased arterial stiffness. Some studies even suggest positive correlation to the Framingham risk score, which has been used to estimate an individual's risk of cardiovascular disease.

  • Age estimate. There have been several publications suggesting different APG ratios, including (c+d-b)/a, as a means to estimate a subject's age.


Figure 2. Acceleration plethysmogram.

Heart-Rate Variability (HRV)/Pulse-Rate Variability (PRV)

PRV, measured using PPG, is similar to heart-rate variability (HRV) and is used to gauge the autonomic nervous system by analyzing the inter-beat interval generated from heart activity. Because inter-beat intervals vary slowly, the reliability challenge for wearable PPG data lies in maintaining good sensor-to-tissue contact over a long period. Furthermore, the sampling rate used to acquire PPG data must be high enough to avoid time-domain quantization, which affects the accuracy of the PRV variable analyzed.


Pulse oximetry, or SpO2, is more complex than the PPG measurements listed above because it involves lights of two different wavelengths. Researchers have proposed many different approaches to remove the effects of noise and motion artifacts, but the problem persists in wearable applications. This is due to the complexity of motion artifacts.

Movements can result in a change in the tissue-to-sensor coupling. It is a fundamental assumption that these two wavelengths share essentially the same optical path. Data becomes unreliable when movements of the subject causes momentary differences between the paths traveled by each light source. Furthermore, motion can also affect the movement of venous blood and other non-pulsatile components along the optical path, thereby altering the characteristics of the tissue under observation.

Here, data reliability requires an algorithm to understand whether the PPG data is clean or corrupted by motion. So, the bandwidth need for reliable data relates more to supporting this classification and what other sensor information may be available besides PPG, rather than on heart rate or the corrupting motion.

An Example: Power Spectral Density of PPG Data

Figure 3 is the power spectral density derived from a set of PPG data captured over fewer than 40s at 100 samples per second on an normally ambulatory subject. It has been truncated to show only the spectrum from 0 to 15Hz. The first prominent peak (below 3Hz) corresponds to heart rate. The higher frequency (>3 to 8Hz) spectral energies are dominated by motion artifacts. This illustrates the difficulties of deriving continuously usable data for higher order analyses such as using APG wave shapes. Algorithms must be capable of differentiating clean, usable data from data corrupted by motion or other artifacts.


Figure 3. Power spectral density from PPG data.


This article looked at the contributors to PPG data reliability from both a general signal-to-noise perspective and from how useful information may lie in the frequency domain. Designers can improve data reliability by:

  • Making sure the PPG hardware intrinsically provides optical signal-to-noise performance

  • Making sure the signal chain provides adequate bandwidth for the targeted information

  • Including other sensors, which may alert an algorithm when PPG data may become corrupted

With reliable PPG data collected by optical sensors designed into wearable devices, those wearing these devices can get a more insightful picture of their health and well-being.


These articles provided background for this blog post:

  • Motion Artifact Removal from Photoplethysmographic Signals By Combining Temporally Constrained Independent Component Analysis and Adaptive Filter

  • Photoplethysmography Assessments in Cardiovascular Disease

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