Audioplethysmography for cardiac monitoring with hearable devices

Posted by Xiaoran "Van" Fan, Experimental Scientist, and Trausti Thormundsson, Director, Google The market for true wireless stereo (TWS) active noise canceling (ANC) hearables (headphones and earbuds) has been soaring in recent years, and the global shipment volume will nearly double that of smart wristbands and watches in 2023. The on-head time for hearables has extended significantly due to the recent advances in ANC, transparency mode, and artificial intelligence. Users frequently wear hearables not just for music listening, but also for exercising, focusing, or simply mood adjustment. However, hearable health is still mostly uncharted territory for the consumer market. In “APG: Audioplethysmography for Cardiac Monitoring in Hearables,” presented at MobiCom 2023, we introduce a novel active in-ear health sensing modality. Audioplethysmography (APG) enables ANC hearables to monitor a user's physiological signals, such as heart rate and heart rate variability, without adding extra sensors or compromising battery life. APG exhibits high resilience to motion artifacts, adheres to safety regulations with an 80 dB margin below the limit, remains unaffected by seal conditions, and is inclusive of all skin tones. APG sends a low intensity ultrasound transmitting wave (TX wave) using an ANC headphone's speakers and collects the receiving wave (RX wave) via the on-board feedback microphones. The APG signal is a pulse-like waveform that synchronizes with heartbeat and reveals rich cardiac information, such as dicrotic notches. Health sensing in the ear canal The auditory canal receives its blood supply from the arteria auricularis profunda, also known as the deep ear artery. This artery forms an intricate network of smaller vessels that extensively permeate the auditory canal. Slight variations in blood vessel shape caused by the heartbeat (and blood pressure) can lead to subtle changes in the volume and pressure of the ear canals, making the ear canal an ideal location for health sensing. Recent research has explored using hearables for health sensing by packaging together a plethora of sensors — e.g., photoplethysmograms (PPG) and electrocardiograms (ECG) — with a microcontroller to enable health applications, such as sleep monitoring, heart rate and blood pressure tracking. However, this sensor mounting paradigm inevitably adds cost, weight, power consumption, acoustic design complexity, and form factor challenges to hearables, constituting a strong barrier to its wide adoption. Existing ANC hearables deploy feedback and feedforward microphones to navigate the ANC function. These microphones create new opportunities for various sensing applications as they can detect or record many bio-signals inside and outside the ear canal. For example, feedback microphones can be used to listen to heartbeats and feedforward microphones can hear respirations. Academic research on this passive sensing paradigm has prompted many mobile applications, including heart rate monitoring, ear disease diagnosis, respiration monitoring, and body activity recognition. However, microphones in consumer-grade ANC headphones come with built-in high-pass filters to prevent saturation from body motions or strong wind noise. The signal quality of passive listening in the ear canal also heavily relies on the earbud seal conditions. As such, it is challenging to embed health features that rely on the passive listening of low frequency signals (≤ 50 Hz) on commercial ANC headphones. Measuring tiny physiological signals APG bypasses the aforementioned ANC headphone hardware constraints by sending a low intensity ultrasound probing signal through an ANC headphone's speakers. This signal triggers echoes, which are received via on-board feedback microphones. We observe that the tiny ear canal skin displacement and heartbeat vibrations modulate these ultrasound echoes. We build a cylindrical resonance model to understand APG’s underlying physics. This phenomenon happens at an extremely small scale, which makes the raw pulse signal invisible in the raw received ultrasound. We adopt coherent detection to retrieve this micro physiological modulation under the noise floor (we term this retrieved signal as mixed-down signal, see the paper for more details). The final APG waveform looks strikingly similar to a PPG waveform, but provides an improved view of cardiac activities with more pronounced dicrotic notches (i.e., pressure waveforms that provide rich insights about the central artery system, such as blood pressure). A cylindrical model with cardiac activities ℎ(𝑡) that modulates both the phase and amplitude of the mixed-down signal. Based on the simulation from our analytical model, the amplitude 𝑅(𝑡) and phase Φ(𝑡) of the mixed-down APG signals both reflect the cardiac activities ℎ(𝑡). APG sensing in practice During our initial experiments, we observed that APG works robustly with bad earbuds seals and with music playing. However, we noticed the APG signal can sometimes be very noisy and could be heavily disturbed by body motion. At that point, we determined that in order to make APG useful, we had to make it more robust to compete with more than 80 years of PPG development. While PPGs are widely used and highly advanced, they do have some limitations. For example, PPGs sensors typically use two to four diodes to send and receive light frequencies for sensing. However, due to the ultra high-frequency nature (hundreds of Terahertz) of the light, it's difficult for a single diode to send multiple colors with different frequencies. On the other hand, we can easily design a low-cost and low-power system that generates and receives more than ten audio tones (frequencies). We leverage channel diversity, a physical phenomenon that describes how wireless signals (e.g., light and audio) at different frequencies have different characters (e.g., different attenuation and reflection coefficients) when the signal propagates in a medium, to enable a higher quality APG signal and motion resilience. Next, we experimentally demonstrate the effectiveness of using multiple frequencies in the APG signaling. We transmit three probing signals concurrently with their frequencies spanning evenly from 30 KHz to 32 KHz. A participant was asked to shake their head four times during the experiment to introduce interference. The figure below shows that different frequencies can be transmitted simultaneously to gather various information with coherent detection, a unique advantage to APG. The 30 kHz phase shows the four head movements and the magnitude (amplitude) of 31 kHz shows the pulse wave signal. This observation shows that some ultrasound frequencies might be sensitive to cardiac activities while others might be sensitive to motion. Therefore, we can use the multi-tone APG as a calibration signal to find the best frequency that measures heart rate, and use only the best frequency to get high-quality pulse waveform. The mixed-down amplitude (upper row) and phase (bottom row) for a customized multi-tone APG signal that spans from 30 kHz to 32 kHz. With channel diversity, the cardiac activities are captured in some frequencies (e.g., magnitude of 31 kHz) and head movements are captured in other frequencies (e.g., magnitude of 30 kHz, 30 kHz, and phase of 31 kHz). After choosing the best frequency to measure heart rate, the APG pulse waveform becomes more visible with pronounced dicrotic notches , and enables accurate heart rate variability measurement. The final APG signal used in the measurement phase (left) and chest ECG signal (right). Multi-tone translates to multiple simultaneous observations, which enable the development of array signal processing techniques. We demonstrate the spectrogram of a running session APG experiment before and after applying blind source separation (see the paper for more details). We also show the ground truth heart rate measurement in the same running experiment using a Polar ECG chest strap. In the raw APG, we see the running cadence (around 3.3 Hz) as well as two dim lines (around 2 Hz and 4 Hz) that indicate the user’s heart rate frequency and its harmonics. The heart rate frequencies are significantly enhanced in signal to noise ratio (SNR) after the blind source separation, which align with the ground truth heart rate frequencies. We also show the calculated heart rate and running cadence from APG and ECG. We can see that APG tracks the growth of heart rate during the running session accurately. APG tracks the heart rate accurately during the running session and also measures the running cadence. Field study and closing thoughts We conducted two rounds of user experience (UX) studies with 153 participants. Our results demonstrate that APG achieves consistently accurate heart rate (3.21% median error across participants in all activity scenarios) and heart rate variability (2.70% median error in inter-beat interval) measurements. Unlike PPG, which exhibits variable performance across skin tones, our study shows that APG is resilient to variation in: skin tone, sub-optimal seal conditions, and ear canal size. More detailed evaluations can be found in the paper. APG transforms any TWS ANC headphones into smart sensing headphones with a simple software upgrade, and works robustly across various user activities. The sensing carrier signal is completely inaudible and not impacted by music playing. More importantly, APG represents new knowledge in biomedical and mobile research and unlocks new possibilities for low-cost health sensing. Acknowledgements APG is the result of collaboration across Google Health, product, UX and legal teams. We would like to thank David Pearl, Jesper Ramsgaard, Cody Wortham, Octavio Ponce, Patrick Amihood, Sam Sheng, Michael Pate, Leonardo Kusumo, Simon Tong, Tim Gladwin, Russ Mirov, Kason Walker, Govind Kannan, Jayvon Timmons, Dennis Rauschmayer, Chiong Lai, Shwetak Patel, Jake Garrison, Anran Wang, Shiva Rajagopal, Shelten Yuen, Seobin Jung, Yun Liu, John Hernandez, Issac Galatzer-Levy, Isaiah Fischer-Brown, Jamie Rogers, Pramod Rudrapatna, Andrew Barakat, Jason Guss, Ethan Grabau, Pol Peiffer, Bill Park, Helen O'Connor, Mia Cheng, Keiichiro Yumiba, Felix Bors, Priyanka Jantre, Luzhou Xu, Jian Wang, Jaime Lien, Gerry Pallipuram, Nicholas Gillian, Michal Matuszak, Jakub Wojciechowski, Bryan Allen, Jane Hilario, and Phil Carmack for their invaluable insights and support. Thanks to external collaborators Longfei Shangguan and Rich Howard, Rutgers University and University of Pittsburgh.

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The market for true wireless stereo (TWS) active noise canceling (ANC) hearables (headphones and earbuds) has been soaring in recent years, and the global shipment volume will nearly double that of smart wristbands and watches in 2023. The on-head time for hearables has extended significantly due to the recent advances in ANC, transparency mode, and artificial intelligence. Users frequently wear hearables not just for music listening, but also for exercising, focusing, or simply mood adjustment. However, hearable health is still mostly uncharted territory for the consumer market.

In “APG: Audioplethysmography for Cardiac Monitoring in Hearables,” presented at MobiCom 2023, we introduce a novel active in-ear health sensing modality. Audioplethysmography (APG) enables ANC hearables to monitor a user’s physiological signals, such as heart rate and heart rate variability, without adding extra sensors or compromising battery life. APG exhibits high resilience to motion artifacts, adheres to safety regulations with an 80 dB margin below the limit, remains unaffected by seal conditions, and is inclusive of all skin tones.

APG sends a low intensity ultrasound transmitting wave (TX wave) using an ANC headphone’s speakers and collects the receiving wave (RX wave) via the on-board feedback microphones. The APG signal is a pulse-like waveform that synchronizes with heartbeat and reveals rich cardiac information, such as dicrotic notches.

Health sensing in the ear canal

The auditory canal receives its blood supply from the arteria auricularis profunda, also known as the deep ear artery. This artery forms an intricate network of smaller vessels that extensively permeate the auditory canal. Slight variations in blood vessel shape caused by the heartbeat (and blood pressure) can lead to subtle changes in the volume and pressure of the ear canals, making the ear canal an ideal location for health sensing.

Recent research has explored using hearables for health sensing by packaging together a plethora of sensors — e.g., photoplethysmograms (PPG) and electrocardiograms (ECG) — with a microcontroller to enable health applications, such as sleep monitoring, heart rate and blood pressure tracking. However, this sensor mounting paradigm inevitably adds cost, weight, power consumption, acoustic design complexity, and form factor challenges to hearables, constituting a strong barrier to its wide adoption.

Existing ANC hearables deploy feedback and feedforward microphones to navigate the ANC function. These microphones create new opportunities for various sensing applications as they can detect or record many bio-signals inside and outside the ear canal. For example, feedback microphones can be used to listen to heartbeats and feedforward microphones can hear respirations. Academic research on this passive sensing paradigm has prompted many mobile applications, including heart rate monitoring, ear disease diagnosis, respiration monitoring, and body activity recognition. However, microphones in consumer-grade ANC headphones come with built-in high-pass filters to prevent saturation from body motions or strong wind noise. The signal quality of passive listening in the ear canal also heavily relies on the earbud seal conditions. As such, it is challenging to embed health features that rely on the passive listening of low frequency signals (≤ 50 Hz) on commercial ANC headphones.

Measuring tiny physiological signals

APG bypasses the aforementioned ANC headphone hardware constraints by sending a low intensity ultrasound probing signal through an ANC headphone’s speakers. This signal triggers echoes, which are received via on-board feedback microphones. We observe that the tiny ear canal skin displacement and heartbeat vibrations modulate these ultrasound echoes.

We build a cylindrical resonance model to understand APG’s underlying physics. This phenomenon happens at an extremely small scale, which makes the raw pulse signal invisible in the raw received ultrasound. We adopt coherent detection to retrieve this micro physiological modulation under the noise floor (we term this retrieved signal as mixed-down signal, see the paper for more details). The final APG waveform looks strikingly similar to a PPG waveform, but provides an improved view of cardiac activities with more pronounced dicrotic notches (i.e., pressure waveforms that provide rich insights about the central artery system, such as blood pressure).

A cylindrical model with cardiac activities ℎ(𝑡) that modulates both the phase and amplitude of the mixed-down signal. Based on the simulation from our analytical model, the amplitude 𝑅(𝑡) and phase Φ(𝑡) of the mixed-down APG signals both reflect the cardiac activities ℎ(𝑡).

APG sensing in practice

During our initial experiments, we observed that APG works robustly with bad earbuds seals and with music playing. However, we noticed the APG signal can sometimes be very noisy and could be heavily disturbed by body motion. At that point, we determined that in order to make APG useful, we had to make it more robust to compete with more than 80 years of PPG development.

While PPGs are widely used and highly advanced, they do have some limitations. For example, PPGs sensors typically use two to four diodes to send and receive light frequencies for sensing. However, due to the ultra high-frequency nature (hundreds of Terahertz) of the light, it’s difficult for a single diode to send multiple colors with different frequencies. On the other hand, we can easily design a low-cost and low-power system that generates and receives more than ten audio tones (frequencies). We leverage channel diversity, a physical phenomenon that describes how wireless signals (e.g., light and audio) at different frequencies have different characters (e.g., different attenuation and reflection coefficients) when the signal propagates in a medium, to enable a higher quality APG signal and motion resilience.

Next, we experimentally demonstrate the effectiveness of using multiple frequencies in the APG signaling. We transmit three probing signals concurrently with their frequencies spanning evenly from 30 KHz to 32 KHz. A participant was asked to shake their head four times during the experiment to introduce interference. The figure below shows that different frequencies can be transmitted simultaneously to gather various information with coherent detection, a unique advantage to APG.

The 30 kHz phase shows the four head movements and the magnitude (amplitude) of 31 kHz shows the pulse wave signal. This observation shows that some ultrasound frequencies might be sensitive to cardiac activities while others might be sensitive to motion. Therefore, we can use the multi-tone APG as a calibration signal to find the best frequency that measures heart rate, and use only the best frequency to get high-quality pulse waveform.

The mixed-down amplitude (upper row) and phase (bottom row) for a customized multi-tone APG signal that spans from 30 kHz to 32 kHz. With channel diversity, the cardiac activities are captured in some frequencies (e.g., magnitude of 31 kHz) and head movements are captured in other frequencies (e.g., magnitude of 30 kHz, 30 kHz, and phase of 31 kHz).

After choosing the best frequency to measure heart rate, the APG pulse waveform becomes more visible with pronounced dicrotic notches , and enables accurate heart rate variability measurement.

The final APG signal used in the measurement phase (left) and chest ECG signal (right).

Multi-tone translates to multiple simultaneous observations, which enable the development of array signal processing techniques. We demonstrate the spectrogram of a running session APG experiment before and after applying blind source separation (see the paper for more details). We also show the ground truth heart rate measurement in the same running experiment using a Polar ECG chest strap. In the raw APG, we see the running cadence (around 3.3 Hz) as well as two dim lines (around 2 Hz and 4 Hz) that indicate the user’s heart rate frequency and its harmonics. The heart rate frequencies are significantly enhanced in signal to noise ratio (SNR) after the blind source separation, which align with the ground truth heart rate frequencies. We also show the calculated heart rate and running cadence from APG and ECG. We can see that APG tracks the growth of heart rate during the running session accurately.

APG tracks the heart rate accurately during the running session and also measures the running cadence.

Field study and closing thoughts

We conducted two rounds of user experience (UX) studies with 153 participants. Our results demonstrate that APG achieves consistently accurate heart rate (3.21% median error across participants in all activity scenarios) and heart rate variability (2.70% median error in inter-beat interval) measurements. Unlike PPG, which exhibits variable performance across skin tones, our study shows that APG is resilient to variation in: skin tone, sub-optimal seal conditions, and ear canal size. More detailed evaluations can be found in the paper.

APG transforms any TWS ANC headphones into smart sensing headphones with a simple software upgrade, and works robustly across various user activities. The sensing carrier signal is completely inaudible and not impacted by music playing. More importantly, APG represents new knowledge in biomedical and mobile research and unlocks new possibilities for low-cost health sensing.

Acknowledgements


APG is the result of collaboration across Google Health, product, UX and legal teams. We would like to thank David Pearl, Jesper Ramsgaard, Cody Wortham, Octavio Ponce, Patrick Amihood, Sam Sheng, Michael Pate, Leonardo Kusumo, Simon Tong, Tim Gladwin, Russ Mirov, Kason Walker, Govind Kannan, Jayvon Timmons, Dennis Rauschmayer, Chiong Lai, Shwetak Patel, Jake Garrison, Anran Wang, Shiva Rajagopal, Shelten Yuen, Seobin Jung, Yun Liu, John Hernandez, Issac Galatzer-Levy, Isaiah Fischer-Brown, Jamie Rogers, Pramod Rudrapatna, Andrew Barakat, Jason Guss, Ethan Grabau, Pol Peiffer, Bill Park, Helen O’Connor, Mia Cheng, Keiichiro Yumiba, Felix Bors, Priyanka Jantre, Luzhou Xu, Jian Wang, Jaime Lien, Gerry Pallipuram, Nicholas Gillian, Michal Matuszak, Jakub Wojciechowski, Bryan Allen, Jane Hilario, and Phil Carmack for their invaluable insights and support. Thanks to external collaborators Longfei Shangguan and Rich Howard, Rutgers University and University of Pittsburgh.

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Best of both worlds: Achieving scalability and quality in text clustering

Posted by Sara Ahmadian and Mehran Kazemi, Research Scientists, Google Research

Clustering is a fundamental, ubiquitous problem in data mining and unsupervised machine learning, where the goal is to group together similar items. The standard forms of clustering are metric clustering and graph clustering. In metric clustering, a given metric space defines distances between data points, which are grouped together based on their separation. In graph clustering, a given graph connects similar data points through edges, and the clustering process groups data points together based on the connections between them. Both clustering forms are particularly useful for large corpora where class labels can’t be defined. Examples of such corpora are the ever-growing digital text collections of various internet platforms, with applications including organizing and searching documents, identifying patterns in text, and recommending relevant documents to users (see more examples in the following posts: clustering related queries based on user intent and practical differentially private clustering).

The choice of text clustering method often presents a dilemma. One approach is to use embedding models, such as BERT or RoBERTa, to define a metric clustering problem. Another is to utilize cross-attention (CA) models, such as PaLM or GPT, to define a graph clustering problem. CA models can provide highly accurate similarity scores, but constructing the input graph may require a prohibitive quadratic number of inference calls to the model. On the other hand, a metric space can efficiently be defined by distances of embeddings produced by embedding models. However, these similarity distances are typically of substantial lower-quality compared to the similarity signals of CA models, and hence the produced clustering can be of much lower-quality.

An overview of the embedding-based and cross-attention–based similarity scoring functions and their scalability vs. quality dilemma.

Motivated by this, in “KwikBucks: Correlation Clustering with Cheap-Weak and Expensive-Strong Signals”, presented at ICLR 2023, we describe a novel clustering algorithm that effectively combines the scalability benefits from embedding models and the quality from CA models. This graph clustering algorithm has query access to both the CA model and the embedding model, however, we apply a budget on the number of queries made to the CA model. This algorithm uses the CA model to answer edge queries, and benefits from unlimited access to similarity scores from the embedding model. We describe how this proposed setting bridges algorithm design and practical considerations, and can be applied to other clustering problems with similar available scoring functions, such as clustering problems on images and media. We demonstrate how this algorithm yields high-quality clusters with almost a linear number of query calls to the CA model. We have also open-sourced the data used in our experiments.

The clustering algorithm

The KwikBucks algorithm is an extension of the well-known KwikCluster algorithm (Pivot algorithm). The high-level idea is to first select a set of documents (i.e., centers) with no similarity edge between them, and then form clusters around these centers. To obtain the quality from CA models and the runtime efficiency from embedding models, we introduce the novel combo similarity oracle mechanism. In this approach, we utilize the embedding model to guide the selection of queries to be sent to the CA model. When given a set of center documents and a target document, the combo similarity oracle mechanism outputs a center from the set that is similar to the target document, if present. The combo similarity oracle enables us to save on budget by limiting the number of query calls to the CA model when selecting centers and forming clusters. It does this by first ranking centers based on their embedding similarity to the target document, and then querying the CA model for the pair (i.e., target document and ranked center), as shown below.

A combo similarity oracle that for a set of documents and a target document, returns a similar document from the set, if present.

We then perform a post processing step to merge clusters if there is a strong connection between two of them, i.e., when the number of connecting edges is higher than the number of missing edges between two clusters. Additionally, we apply the following steps for further computational savings on queries made to the CA model, and to improve performance at runtime:

We leverage query-efficient correlation clustering to form a set of centers from a set of randomly selected documents instead of selecting these centers from all the documents (in the illustration below, the center nodes are red).

We apply the combo similarity oracle mechanism to perform the cluster assignment step in parallel for all non-center documents and leave documents with no similar center as singletons. In the illustration below, the assignments are depicted by blue arrows and initially two (non-center) nodes are left as singletons due to no assignment.

In the post-processing step, to ensure scalability, we use the embedding similarity scores to filter down the potential mergers (in the illustration below, the green dashed boundaries show these merged clusters).

Illustration of progress of the clustering algorithm on a given graph instance.

Results

We evaluate the novel clustering algorithm on various datasets with different properties using different embedding-based and cross-attention–based models. We compare the clustering algorithm’s performance with the two best performing baselines (see the paper for more details):

To evaluate the quality of clustering, we use precision and recall. Precision is used to calculate the percentage of similar pairs out of all co-clustered pairs and recall is the percentage of co-clustered similar pairs out of all similar pairs. To measure the quality of the obtained solutions from our experiments, we use the F1-score, which is the harmonic mean of the precision and recall, where 1.0 is the highest possible value that indicates perfect precision and recall, and 0 is the lowest possible value that indicates if either precision or recall are zero. The table below reports the F1-score for Kwikbucks and various baselines in the case that we allow only a linear number of queries to the CA model. We show that Kwikbucks offers a substantial boost in performance with a 45% relative improvement compared to the best baseline when averaging across all datasets.

The figure below compares the clustering algorithm’s performance with baselines using different query budgets. We observe that KwikBucks consistently outperforms other baselines at various budgets.

A comparison of KwikBucks with top-2 baselines when allowed different budgets for querying the cross-attention model.

Conclusion

Text clustering often presents a dilemma in the choice of similarity function: embedding models are scalable but lack quality, while cross-attention models offer quality but substantially hurt scalability. We present a clustering algorithm that offers the best of both worlds: the scalability of embedding models and the quality of cross-attention models. KwikBucks can also be applied to other clustering problems with multiple similarity oracles of varying accuracy levels. This is validated with an exhaustive set of experiments on various datasets with diverse properties. See the paper for more details.

Acknowledgements

This project was initiated during Sandeep Silwal’s summer internship at Google in 2022. We would like to express our gratitude to our co-authors, Andrew McCallum, Andrew Nystrom, Deepak Ramachandran, and Sandeep Silwal, for their valuable contributions to this work. We also thank Ravi Kumar and John Guilyard for assistance with this blog post.

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Zero-shot adaptive prompting of large language models

Posted by Xingchen Wan, Student Researcher, and Ruoxi Sun, Research Scientist, Cloud AI Team

Recent advances in large language models (LLMs) are very promising as reflected in their capability for general problem-solving in few-shot and zero-shot setups, even without explicit training on these tasks. This is impressive because in the few-shot setup, LLMs are presented with only a few question-answer demonstrations prior to being given a test question. Even more challenging is the zero-shot setup, where the LLM is directly prompted with the test question only.

Even though the few-shot setup has dramatically reduced the amount of data required to adapt a model for a specific use-case, there are still cases where generating sample prompts can be challenging. For example, handcrafting even a small number of demos for the broad range of tasks covered by general-purpose models can be difficult or, for unseen tasks, impossible. For example, for tasks like summarization of long articles or those that require domain knowledge (e.g., medical question answering), it can be challenging to generate sample answers. In such situations, models with high zero-shot performance are useful since no manual prompt generation is required. However, zero-shot performance is typically weaker as the LLM is not presented with guidance and thus is prone to spurious output.

In “Better Zero-shot Reasoning with Self-Adaptive Prompting”, published at ACL 2023, we propose Consistency-Based Self-Adaptive Prompting (COSP) to address this dilemma. COSP is a zero-shot automatic prompting method for reasoning problems that carefully selects and constructs pseudo-demonstrations for LLMs using only unlabeled samples (that are typically easy to obtain) and the models’ own predictions. With COSP, we largely close the performance gap between zero-shot and few-shot while retaining the desirable generality of zero-shot prompting. We follow this with “Universal Self-Adaptive Prompting“ (USP), accepted at EMNLP 2023, in which we extend the idea to a wide range of general natural language understanding (NLU) and natural language generation (NLG) tasks and demonstrate its effectiveness.

Prompting LLMs with their own outputs

Knowing that LLMs benefit from demonstrations and have at least some zero-shot abilities, we wondered whether the model’s zero-shot outputs could serve as demonstrations for the model to prompt itself. The challenge is that zero-shot solutions are imperfect, and we risk giving LLMs poor quality demonstrations, which could be worse than no demonstrations at all. Indeed, the figure below shows that adding a correct demonstration to a question can lead to a correct solution of the test question (Demo1 with question), whereas adding an incorrect demonstration (Demo 2 + questions, Demo 3 with questions) leads to incorrect answers. Therefore, we need to select reliable self-generated demonstrations.

Example inputs & outputs for reasoning tasks, which illustrates the need for carefully designed selection procedure for in-context demonstrations (MultiArith dataset & PaLM-62B model): (1) zero-shot chain-of-thought with no demo: correct logic but wrong answer; (2) correct demo (Demo1) and correct answer; (3) correct but repetitive demo (Demo2) leads to repetitive outputs; (4) erroneous demo (Demo3) leads to a wrong answer; but (5) combining Demo3 and Demo1 again leads to a correct answer.

COSP leverages a key observation of LLMs: that confident and consistent predictions are more likely correct. This observation, of course, depends on how good the uncertainty estimate of the LLM is. Luckily, in large models, previous works suggest that the uncertainty estimates are robust. Since measuring confidence requires only model predictions, not labels, we propose to use this as a zero-shot proxy of correctness. The high-confidence outputs and their inputs are then used as pseudo-demonstrations.

With this as our starting premise, we estimate the model’s confidence in its output based on its self-consistency and use this measure to select robust self-generated demonstrations. We ask LLMs the same question multiple times with zero-shot chain-of-thought (CoT) prompting. To guide the model to generate a range of possible rationales and final answers, we include randomness controlled by a “temperature” hyperparameter. In an extreme case, if the model is 100% certain, it should output identical final answers each time. We then compute the entropy of the answers to gauge the uncertainty — the answers that have high self-consistency and for which the LLM is more certain, are likely to be correct and will be selected.

Assuming that we are presented with a collection of unlabeled questions, the COSP method is:

Input each unlabeled question into an LLM, obtaining multiple rationales and answers by sampling the model multiple times. The most frequent answers are highlighted, followed by a score that measures consistency of answers across multiple sampled outputs (higher is better). In addition to favoring more consistent answers, we also penalize repetition within a response (i.e., with repeated words or phrases) and encourage diversity of selected demonstrations. We encode the preference towards consistent, un-repetitive and diverse outputs in the form of a scoring function that consists of a weighted sum of the three scores for selection of the self-generated pseudo-demonstrations.
We concatenate the pseudo-demonstrations into test questions, feed them to the LLM, and obtain a final predicted answer.

Illustration of COSP: In Stage 1 (left), we run zero-shot CoT multiple times to generate a pool of demonstrations (each consisting of the question, generated rationale and prediction) and assign a score. In Stage 2 (right), we augment the current test question with pseudo-demos (blue boxes) and query the LLM again. A majority vote over outputs from both stages forms the final prediction.

COSP focuses on question-answering tasks with CoT prompting for which it is easy to measure self-consistency since the questions have unique correct answers. But this can be difficult for other tasks, such as open-ended question-answering or generative tasks that don’t have unique answers (e.g., text summarization). To address this limitation, we introduce USP in which we generalize our approach to other general NLP tasks:

Classification (CLS): Problems where we can compute the probability of each class using the neural network output logits of each class. In this way, we can measure the uncertainty without multiple sampling by computing the entropy of the logit distribution.
Short-form generation (SFG): Problems like question answering where we can use the same procedure mentioned above for COSP, but, if necessary, without the rationale-generating step.
Long-form generation (LFG): Problems like summarization and translation, where the questions are often open-ended and the outputs are unlikely to be identical, even if the LLM is certain. In this case, we use an overlap metric in which we compute the average of the pairwise ROUGE score between the different outputs to the same query.

Illustration of USP in exemplary tasks (classification, QA and text summarization). Similar to COSP, the LLM first generates predictions on an unlabeled dataset whose outputs are scored with logit entropy, consistency or alignment, depending on the task type, and pseudo-demonstrations are selected from these input-output pairs. In Stage 2, the test instances are augmented with pseudo-demos for prediction.

We compute the relevant confidence scores depending on the type of task on the aforementioned set of unlabeled test samples. After scoring, similar to COSP, we pick the confident, diverse and less repetitive answers to form a model-generated pseudo-demonstration set. We finally query the LLM again in a few-shot format with these pseudo-demonstrations to obtain the final predictions on the entire test set.

Key Results

For COSP, we focus on a set of six arithmetic and commonsense reasoning problems, and we compare against 0-shot-CoT (i.e., “Let’s think step by step“ only). We use self-consistency in all baselines so that they use roughly the same amount of computational resources as COSP. Compared across three LLMs, we see that zero-shot COSP significantly outperforms the standard zero-shot baseline.

USP improves significantly on 0-shot performance. “CLS” is an average of 15 classification tasks; “SFG” is the average of five short-form generation tasks; “LFG” is the average of two summarization tasks. “SFG (BBH)” is an average of all BIG-Bench Hard tasks, where each question is in SFG format.

For USP, we expand our analysis to a much wider range of tasks, including more than 25 classifications, short-form generation, and long-form generation tasks. Using the state-of-the-art PaLM 2 models, we also test against the BIG-Bench Hard suite of tasks where LLMs have previously underperformed compared to people. We show that in all cases, USP again outperforms the baselines and is competitive to prompting with golden examples.

Accuracy on BIG-Bench Hard tasks with PaLM 2-M (each line represents a task of the suite). The gain/loss of USP (green stars) over standard 0-shot (green triangles) is shown in percentages. “Human” refers to average human performance; “AutoCoT” and “Random demo” are baselines we compared against in the paper; and “3-shot” is the few-shot performance for three handcrafted demos in CoT format.

We also analyze the working mechanism of USP by validating the key observation above on the relation between confidence and correctness, and we found that in an overwhelming majority of the cases, USP picks confident predictions that are more likely better in all task types considered, as shown in the figure below.

USP picks confident predictions that are more likely better. Ground-truth performance metrics against USP confidence scores in selected tasks in various task types (blue: CLS, orange: SFG, green: LFG) with PaLM-540B.
Conclusion

Zero-shot inference is a highly sought-after capability of modern LLMs, yet the success in which poses unique challenges. We propose COSP and USP, a family of versatile, zero-shot automatic prompting techniques applicable to a wide range of tasks. We show large improvement over the state-of-the-art baselines over numerous task and model combinations.

Acknowledgements

This work was conducted by Xingchen Wan, Ruoxi Sun, Hootan Nakhost, Hanjun Dai, Julian Martin Eisenschlos, Sercan Ö. Arık, and Tomas Pfister. We would like to thank Jinsung Yoon Xuezhi Wang for providing helpful reviews, and other colleagues at Google Cloud AI Research for their discussion and feedback.

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