Patent Application
20100262031
The present invention relates to respiratory monitoring and, more particularly, to a method and system for classifying respiratory phases in a single channel acoustic signal as inspiratory and expiratory using explicit labeling with label verification, and for automatically recovering phase after signal interruption. Without extra channels, the present invention addresses the difficulty in distinguishing between the inspiratory and expiratory phases that arises from the lack of a universal signal characteristic to differentiate these phases for all people. Moreover, the present invention provides for automatic recovery of phase after a loss of phase tracking due to reasons such as loss of signal or noisy signal.
Respiration in humans is typically characterized by two phases: inspiration, or the intake of air into the lungs, and expiration, or the expelling of air from the lungs. Data that characterize respiratory phases is very important in individual respiratory health determinations and the study of pulmonary diseases. For example, a low fractional inspiratory time (i.e. inspiratory phase time divided by respiratory cycle time) or a low inspiratory to expiratory time ratio (i.e. inspiratory phase time divided by expiratory phase time, also known as I:E ratio) may reflect a prolonged expiratory phase that is indicative of obstruction of the airways. A high fractional inspiratory time or I:E ratio may be used to inform as to the present status of a monitored subject, for example, that the subject is snoring or speaking. The trend in fractional inspiratory time and I:E ratio may also be instructive in some applications.
One method for obtaining respiratory phase data is the lung sound method, sometimes called auscultation. The lung sound method has become increasingly popular due in part to the low cost and ready availability of lung sound detection systems. In the lung sound method, one or more body mounted respiratory sound transducers records sounds from which respiratory phase data are determined. Tracheal sounds, typically heard over the supreasternal notch or at the lateral neck near the pharynx, are often chosen for respiratory sound detection because the sounds have a high signal-to-noise ratio and a high sensitivity to variation in flow that enable accurate determination of respiratory phase starting points.
One problem with known implementations of the lung sound method is the inability to distinguish inspiratory and expiratory phases of a respiration cycle from a single sound transducer (i.e. single channel sound signal). There is no universal signal characteristic to differentiate the inspiratory and expiratory phases for all people. For example, the difference in amplitude between inspiratory and expiratory tracheal sounds varies greatly among subjects. For many people, inspiratory sounds are louder while for others there is not much difference and for still others expiratory sounds are louder. Therefore, distinguishing between the inspiratory and expiratory phases of a respiratory cycle can be difficult using tracheal sounds alone. One way to address this shortcoming of the lung sound method is to install additional sound transducers on parts of the subject's body, such as on the subject's chest and/or back, that generate lung sounds from which the inspiratory and expiratory phases can be better distinguished. However, reliance on additional sound transducers (i.e. multi-channel sound signal) can add to subject discomfort as well as system complexity and computational overhead.
Another problem with known implementations of the lung sound method is phase recovery after signal interruption. A method for identifying inspiratory and expiratory phases may lose track of phase for any number of reasons. One reason may be signal loss due to unreliable network connectivity. Another reason may be a noisy signal induced by, for example, the surrounding environment, the subject's speech or the subject's motion. Requiring the subject to manually intervene to recover phase every time there is a loss of phase tracking is burdensome and can be a cause of frustration.
The present invention, in a basic feature, provides a method and system for classifying respiratory phases in a single channel acoustic signal as inspiratory and expiratory using explicit labeling with label verification. In the method and system, a subject explicitly indicates through a user input the start of a respiratory cycle (i.e. start of inspiration). The phase indication is applied to provisionally label several consecutive phases of a single channel acoustic signal as inspiratory and expiratory. A provisional phase rule set is then generated based on characteristic differences between the inspiratory and expiratory phases. The phase indication, provisional labeling and provisional rule set generation steps are then repeated. The two generated provisional rule sets are then compared for a match to verify the accuracy of the subject's phase indications and the ability to automatically recover phase in the event of signal loss.
In one aspect of the invention, a system for classifying respiratory phases comprises a data processor, a respiratory sound transducer and a user interface, wherein the data processor receives a respiratory signal from the respiratory sound transducer and an first respiratory phase indication from the user interface and labels a first multiple of respiratory phases in the respiratory signal as inspiratory and a first multiple of respiratory phases in the respiratory signal as expiratory based on the first respiratory phase indication.
In some embodiments, the data processor generates a first phase rule set based on a comparison of characteristics of the first multiple of respiratory phases labeled as inspiratory with the first multiple of respiratory phases labeled as expiratory.
In some embodiments, the first phase rule set comprises rules indicative of differences between the first multiple of respiratory phases labeled as inspiratory and the first multiple of respiratory phases labeled as expiratory.
In some embodiments, the first phase rule set comprises a rule indicative of a difference in one or more of phase duration, maximum amplitude, slope from start of phase to maximum amplitude, slope from maximum amplitude to end of phase, phase width or phase surface area under envelope.
In some embodiments, the data processor receives a second respiratory phase indication from the user interface and labels a second multiple of respiratory phases in the respiratory signal as inspiratory and a second multiple of respiratory phases in the respiratory signal as expiratory based on the second respiratory phase indication, wherein the data processor generates a second phase rule set based on a comparison of characteristics of the second multiple of respiratory phases labeled as inspiratory and the second multiple of respiratory phases labeled as expiratory, and wherein the data processor compares the first and second phase rule sets for a match and generates a permanent phase rule set in response to a match.
In some embodiments, the data processor automatically labels a third multiple of respiratory phases in the respiratory signal as inspiratory and a third multiple of respiratory phases in the respiratory signal as expiratory based on the permanent phase rule set.
In some embodiments, the data processor performs the automatic labeling after recovery from a temporary interruption of the respiratory signal.
In another aspect of the invention, a method for classifying respiratory phases comprises the steps of receiving a respiratory signal, receiving a first respiratory phase indication based on a first user input and labeling a first multiple of respiratory phases in the respiratory signal as inspiratory and a first multiple of respiratory phases in the respiratory signal as expiratory based on the first respiratory phase indication.
In some embodiments, the method further comprises the step of generating a first phase rule set based on a comparison of characteristics of the first multiple of respiratory phases labeled as inspiratory with the first multiple of respiratory phases labeled as expiratory.
In some embodiments, the first phase rule set comprises rules indicative of differences between the first multiple of respiratory phases labeled as inspiratory and the first multiple of respiratory phases labeled as expiratory.
In some embodiments, the first phase rule set comprises a rule indicative of a difference in phase duration.
In some embodiments, the first phase rule set comprises a rule indicative of a difference in maximum amplitude.
In some embodiments, the first phase rule set comprises a rule indicative of a difference in slope from start of phase to maximum amplitude.
In some embodiments, the first phase rule set comprises a rule indicative of a difference in slope from maximum amplitude to end of phase.
In some embodiments, the first phase rule set comprises a rule indicative of a difference in phase width.
In some embodiments, the first phase rule set comprises a rule indicative of a difference in phase surface area under envelope.
In some embodiments, the method further comprises the steps of receiving a second respiratory phase indication based on a second user input, labeling a second multiple of respiratory phases in the respiratory signal as inspiratory and a second multiple of respiratory phases in the respiratory signal as expiratory based on the second respiratory phase indication, generating a second phase rule set based on a comparison of characteristics of the second multiple of respiratory phases labeled as inspiratory and the second multiple of respiratory phases labeled as expiratory, comparing the first and second phase rule sets for a match and generating a permanent phase rule set in response to a match.
In some embodiments, the method further comprises the step of automatically labeling a third multiple of respiratory phases in respiratory signal as inspiratory and a third multiple of respiratory phases in the respiratory signal as expiratory based on the permanent phase rule set.
In some embodiments, the automatic labeling step is performed after recovery from a loss of phase tracking due to a loss of network connectivity.
In some embodiments, the automatic labeling step is performed after recovery from a loss of phase tracking due to a noisy respiratory signal.
In some embodiments, the method further comprises the step of verifying that the phase in the respiratory signal that is addressed by the first respiratory phase indication and the phase in the respiratory signal that is addressed by the second respiratory phase indication are separated by an odd number of intervening phases.
These and other aspects of the invention will be better understood by reference to the following detailed description taken in conjunction with the drawings that are briefly described below. Of course, the invention is defined by the appended claims.
In some embodiments, elements 105, 110, 115, 120, 125 and 140 reside on an acoustic transducer device that captures a respiratory signal, provides on-board processing, and has a wireless interface that supports communication with a portable electronic device, such as a mobile phone or personal data assistant (PDA) on which user interface 150 is resident.
In other embodiments, elements 105, 110, 115, 120 and 125 reside on an acoustic transducer device that captures a respiratory signal and has a wireless interface that supports communication with a portable electronic device, such as a mobile phone or PDA on which processor 140 and user interface 150 are resident.
In still other embodiments, elements 105, 110, 115, 120 and 125 reside on an acoustic transducer device that captures a respiratory signal and has a wired interface, such as a Universal Serial Bus (USB) interface, that supports communication with a desktop or notebook personal computer on which processor 140 and user interface 150 are resident.
Transducer 105 detects a respiratory signal at trachea 130. Transducer 105 outputs the detected respiratory signal to pre-amplifier 110 as an analog voltage.
Pre-amplifier 110 provides impedance match for the respiratory signal received from transducer 105 and amplifies the respiratory signal to a level appropriate for the filter stage that follows.
Band-pass filters 115 include an analog high-pass filter that applies a cutoff frequency to the respiratory signal received from pre-amplifier 110 to reduce noise that may include, for example, heart sounds, muscle sounds and contact noise. Filters 115 also include a low-pass filter with a cutoff frequency applied to the respiratory signal following the high-pass filter.
Final amplifier 120 amplifies the respiratory signal received from band-pass filters 115.
Data acquisition element 125 performs analog/digital (A/D) conversion on the respiratory signal received from final amplifier 120 and down-samples, if necessary, the respiratory signal in order to reduce the sampled data length. Data acquisition element 125 transmits the resulting respiratory signal to data processor 140 for analysis.
Data processor 140 is a microprocessor having software executable thereon for classifying respiratory phases in the respiratory signal received from data acquisition element 125, including phase labeling, phase rule set generation and phase rule set comparison, and performing respiratory phase-independent and phase-specific analysis on the respiratory signal. In some embodiments, processor 140 generates respiratory phase data, such as fractional inspiratory time and/or I:E ratio, based on the respiratory signal on a continuous basis to enable real-time monitoring of the respiratory health of a patient.
User interface 150 includes an input device, such as one or more of a keyboard, keypad, touch screen or mouse, through which the subject inputs information, such as a phase indication that indicates the start of a respiratory cycle (i.e. start of inspiration). User interface 150 also includes an output device, such as one or more of an liquid crystal display (LCD) screen or light emitting diode (LED) display screen, on which the subject views various user screens, such as user screens providing explicit phase labeling status information and respiratory health status information.
Data processor 140 then generates a provisional phase rule set based on an analysis of characteristic differences between the inspiratory and expiratory phases in the six labeled respiratory phases (325). By way of example, characteristic differences that data processor 140 analyzes to generate the provisional rule set may include the following:
(1) Relative phase duration: This check determines whether the inspiratory or expiratory phase is longer. Turning to
(2) Relative maximum amplitude: This check determines whether the inspiratory or expiratory phase has a higher maximum amplitude. Referring to
(3) Relative slope from start of phase to maximum: This check determines whether the inspiratory or expiratory phase has a steeper slope from start of phase to maximum amplitude. Referring to
(4) Relative slope from maximum to end of phase: This check determines whether the inspiratory or expiratory phase has a steeper slope from maximum amplitude to end of phase. Referring to
(5) Relative phase width: This check determines whether the inspiratory or expiratory phase is wider. Referring to
(6) Relative phase surface area under envelope: This check determines whether the surface area under envelope of the inspiratory or expiratory phase is larger. Referring to
The provisional rule set may include a rule for each characteristic difference expressed in terms of one of four outcomes. One outcome is that the inspiratory phase values for the characteristic are consistently greater than the expiratory phase values. A second outcome is that the expiratory phase values for the characteristic are consistently greater than the inspiratory phase values. A third outcome is that the differences between the inspiratory phase values and the expiratory phase values for the characteristic are insignificant. For example, if the phase duration of each inspiratory phase is 2.01 seconds and the phase duration of each expiratory phase is 1.99 seconds, the third outcome would attach. A fourth outcome is that the differences between the inspiratory phase values and the expiratory phase values for the characteristic, while significant, are inconsistent. For example, if the inspiratory phase has a higher maximum amplitude than the expiratory phase for two out of three respiratory cycles and the expiratory phase has a higher maximum amplitude than the inspiratory phase for the third respiratory cycle, the fourth outcome would attach.
Provisional phase rule sets are expressed in binary codes. For example, for each characteristic, a code of “10” may be used if the inspiratory phase values are consistently greater than the expiratory phase values, “01” may be used if the expiratory phase values are greater than the inspiratory phase values, “00” may be used if the differences between the inspiratory and expiratory phase values are insignificant, and “11” may be used if the differences between the inspiratory and expiratory phase values, while significant, are inconsistent.
If the provisional phase rule set generated in Step 325 indicates no consistent difference for any characteristic, provisional rule set generation is deemed to have failed and a decision is made to either retry (i.e. reperform Steps 305-325) or abort the process (330).
If the provisional phase rule set generated in Step 325 indicates a consistent difference for at least one characteristic, provisional rule set generation is deemed successful and Steps 305-325 are repeated in a second instance (335).
Once two provisional phase rule sets have been successfully generated, the flow advances to Step 340 where the provisional phase rule sets are compared for a match to verify the accuracy of the subject's phase indications and the ability to automatically recover phase in the event of signal loss. A match is found if the binary codes for each characteristic in the provisional phase rule set generated in the first instance match the corresponding binary codes for each characteristic in the provisional phase rule set generated in the second instance. If a match is not found, permanent rule set generation is deemed to have failed and a decision is made to either retry (i.e. reperform Steps 305-325) or abort the process (360). If, however, a match is found, the provisional phase rules are saved as permanent phase rules (345), at which point data processor 140 begins permanent phase labeling based on the verified explicit label (350) and respiratory phase-specific analysis of the respiratory signal (355).
In some embodiments, data processor 140 counts the number of respiratory phases that have passed between the first and second respiratory phase indications and verifies that the phase addressed by the second respiratory phase indication and the phase addressed by the first respiratory phase indication are separated by an odd number of intervening phases before generating a provisional phase rule set based on the second respiratory phase indication. This check insures that both phase indications address the some type of phase (e.g. both inspiratory) and provides an additional safeguard against error in the patient's explicit labeling. If this check fails, a decision is made to either retry or abort the process.
It will be appreciated by those of ordinary skill in the art that the invention can be embodied in other specific forms without departing from the spirit or essential character hereof. The present description is considered in all respects to be illustrative and not restrictive. The scope of the invention is indicated by the appended claims, and all changes that come with in the meaning and range of equivalents thereof are intended to be embraced therein.
