APPARATUS AND METHOD FOR ASSESSING THE SEVERITY OF CHRONIC OBSTRUCTIVE PULMONARY DISEASE, COPD, IN A SUBJECT

Abstract

According to an aspect there is provided a method of assessing the severity of chronic obstructive pulmonary disease, COPD, in a subject, the method comprising determining measurements of the breathing rate of the subject, the activity level of the subject, a measure of the respiratory effort of the subject and a measure of the severity or intensity of coughing by the subject; and combining the measurements of the breathing rate, the activity level, the measure of the respiratory effort and the measure of the severity or intensity of coughing to determine a score representing the severity of COPD in the subject.

Claims

1. A method of assessing the severity of chronic obstructive pulmonary disease, COPD, in a subject, the method comprising: determining by means of an accelerometer measurements of a breathing rate of the subject, an activity level of the subject, a measure of the respiratory effort of the subject and a measure of the severity or intensity of coughing by the subject; and combining the measurements of the breathing rate, the activity level, the measure of the respiratory effort and the measure of the severity or intensity of coughing to determine a score representing the severity of COPD in the subject.

2. A method as claimed in claim 1, wherein the breathing rate of the subject, the activity level of the subject, the measure of the respiratory effort of the subject and the measure of the severity or intensity of coughing by the subject are determined from measurements of the accelerometer only.

3. A method as claimed in claim 1, wherein the breathing rate of the subject, the activity level of the subject, the measure of the respiratory effort of the subject and the measure of the severity or intensity of coughing by the subject are determined from measurements of the accelerometer and from measurements of at least one additional sensor.

4. A method as claimed in claim 1, wherein the step of combining the measurements to determine a score representing the severity of COPD in the subject comprises: comparing each of the measurements of the breathing rate, the activity level, the measure of the respiratory effort and the measure of the severity or intensity of coughing to a respective severity range to determine a score for each of the measurements; and adding the determined scores to determine the score representing the severity of COPD in the subject.

5. A method as claimed in claim 1, the method further comprising the step of calibrating the score representing the severity of COPD in the subject against a Body mass index, Obstruction, Dyspnea and Exercise, BODE, score.

6. A method as claimed in claim 1, the method further comprising the step of: comparing the measure of the intensity or severity of coughing to a threshold value to determine if there is a high risk of an exacerbation event or if an exacerbation event is ongoing.

7. A method as claimed in claim 1, the method further comprising the steps of: detecting when the subject coughs or gasps; and temporarily interrupting the step of determining measurements or the use of the measurements in the step of combining when the subject coughs or gasps.

8. A computer program product comprising a computer readable medium having computer readable code embodied therein, the computer readable code being configured such that, on execution by a suitable computer or processor, the computer or processor is caused to perform the method of claim 1.

9. An apparatus for assessing the severity of chronic obstructive pulmonary disease, COPD, in a subject, the apparatus comprising: a control unit configured to determine by means of an accelerometer measurements of a breathing rate of the subject, an activity level of the subject, a measure of the respiratory effort and a measure of the intensity or severity of coughing, and to combine the measurements of the breathing rate, the activity level, the measure of respiratory effort and the measure of the intensity or severity of coughing to determine a score representing the severity of COPD in the subject.

10. An apparatus as claimed in claim 9, wherein the control unit is configured to determine the measurements of the breathing rate of the subject, the activity level of the subject, the measure of the respiratory effort of the subject and the measure of the severity or intensity of coughing by the subject from measurements from the accelerometer only.

11. An apparatus as claimed in claim 9, the apparatus further comprising the accelerometer.

12. An apparatus as claimed in claim 9, wherein the apparatus comprises the accelerometer and at least one additional sensor, wherein the control unit is configured to determine the measurements of the breathing rate of the subject, the activity level of the subject, the measure of the respiratory effort of the subject and the measure of the severity or intensity of coughing by the subject from measurements from the accelerometer and the at least one additional sensor.

13. An apparatus as claimed in claim 12, wherein the at least one additional sensor is a sensor for measuring the motion and/or position of the subject.

14. A system for assessing the severity of chronic obstructive pulmonary disease, COPD, in a subject, the system comprising: the accelerometer for measuring characteristics of the subject; and an apparatus as claimed in claim 9.

15. A system as claimed in claim 14, further comprising at least one additional sensor for measuring the motion and/or position of the subject.

Description

BRIEF DESCRIPTION OF THE DRAWINGS

[0038] For a better understanding of the invention, and to show more clearly how it may be carried into effect, reference will now be made, by way of example only, to the accompanying drawings, in which:

[0039] FIG. 1 is a table illustrating the derivation of the BODE index;

[0040] FIG. 2 is a block diagram of an apparatus according to an aspect of the invention;

[0041] FIG. 3 is a flow chart illustrating a method of assessing the severity of COPD in a subject;

[0042] FIG. 4 is a table illustrating the derivation of a COPD severity index according to an embodiment; and

[0043] FIG. 5 is a series of graphs and a flow chart illustrating how breathing rate can be determined from accelerometer measurements according to an embodiment;

[0044] FIG. 6 is a set of graphs illustrating how the ratio of inhaled to exhaled breath can be determined from accelerometer measurements according to an embodiment;

[0045] FIG. 7 is a graph illustrating how the activity level can be determined from accelerometer measurements according to an embodiment;

[0046] FIG. 8 is a graph illustrating how the number of coughs in a predetermined time period can be determined from accelerometer measurements in an embodiment; and

[0047] FIG. 9 is a diagram that provides an overview of the sensors and physiological parameters that can be used for determining COPD severity in according with various embodiments of the invention.

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

[0048] FIG. 2 is a block diagram illustrating an apparatus 2 according to an aspect of the invention. The apparatus 2 is to be worn or carried by a subject and comprises a sensor for measuring the movements or motion of the subject. In particular, the sensor is for measuring at least the motion or movements of the chest or other part of the body of the subject so that characteristics of the breathing of the subject (e.g. breathing rate, a measure of respiratory effort such as a ratio of inhalation to exhalation, and a measure of the severity or intensity of coughing, such as the number of coughs in a predetermined time period) can be determined from the measurements.

[0049] Preferably, the sensor is an accelerometer 4, although those skilled in the art will appreciate that other types of sensors can be used to obtain the measurements required for assessing COPD severity according to the invention. In some embodiments the accelerometer 4 is a three-dimensional accelerometer that measures the accelerations in three dimensions, but in other embodiments the accelerometer 4 comprises three one-dimensional accelerometers arranged orthogonally to each other. The accelerometer 4 measures the magnitude and direction of the acceleration acting on the apparatus 2 and outputs an acceleration signal indicating the acceleration in three dimensions to a control unit 6. The accelerometer 4 can operate according to any desired operating or sampling frequency to measure the acceleration, for example 50 Hz.

[0050] In preferred embodiments, the only sensor required to obtain the measurements for assessing the COPD severity according to the invention is the accelerometer 4 (i.e. the output from a single or the same sensor 4 is used to determine the parameters according to the invention). These embodiments provide a low-cost, simple, apparatus 2 for assessing COPD severity. However, in other embodiments, the apparatus 2 can comprise one or more additional sensors for obtaining measurements that can be used to determine the breathing characteristics and other characteristics of the subject used in the assessment of COPD severity, and/or that can be used to determine other parameters for the subject that may or may not be used to assess the COPD severity. Such sensors can include sensors for measuring the motion and/or position of the subject, for example a gyroscope, a magnetometer, a satellite positioning system (e.g. GPS) receiver (any some or all of which can be used as part of assessing the activity or activity level of the subject), a microphone for measuring the sound of the subject's breathing (and which can be used to determine the breathing rate and/or determine when the subject coughs) and/or a temperature sensor (for measuring the subject's temperature).

[0051] The control unit 6 controls the operation of the apparatus 2 according to the invention. The control unit 6 can comprise one or more processors, processing units, multi-core processors or processing modules. The apparatus 2 further comprises a memory module 8 for storing computer readable program code that can be executed by the control unit 6 to perform the method according to the invention. The memory module 8 can also be used to store the sensor (acceleration) measurements before, during and after processing by the control unit 6 and any intermediate products of the processing.

[0052] In this illustrated embodiment of the invention, the apparatus 2 comprises a single unit or device that is worn or carried by the subject and that collects and processes the acceleration measurements (in the control unit 6) to determine the COPD severity. In alternative embodiments, the processing of the measurements can be performed in a control unit that is remote from the accelerometer 4 (for example in a unit that is worn on a different part of the body of the subject, in a base unit or computer that can be located in the subject's home, or a remote server located in the premises of a healthcare service provider), in which case the apparatus 2 will comprise a sensor unit to be worn by the subject (that is similar to that shown in FIG. 2) and that comprises suitable transmitter, transceiver or communication circuitry 10 for transmitting the measurements to a control unit in the remote unit. In either embodiment, the apparatus 2 can be part of a COPD severity monitoring system which comprises a display or other visual indicator (that can themselves be part of or separate from the apparatus 2) that can be used to indicate the determined COPD severity score to the subject or a clinician.

[0053] In preferred embodiments of the invention the apparatus 2 is sized and/or shaped so that it can be worn or carried on the upper body of the subject, for example on the chest, thorax or abdomen (and in particular in the subclavian chest area or on the abdomen below the diaphragm). The apparatus 2 can be provided with some means to enable the apparatus 2 to be held in contact with the subject so that the sensor 4 can obtain the required measurements of the motion of the subject to enable the breathing characteristics to be determined. For example, the apparatus 2 can be provided with a belt or strap, or the apparatus 2 can be part of an adhesive patch.

[0054] In practical implementations, the apparatus 2 may comprise other or further components to those shown in FIG. 2 and described above, such as a user interface 12 that allows the subject to activate and/or operate the apparatus 2, and a power supply, such as a battery, for powering the apparatus 2. The user interface 12 may comprise one or more components that allow a user (e.g. the subject) to interact and control the apparatus 2. As an example, the one or more user interface components could comprise a switch, a button or other control means for activating and deactivating the apparatus 2 and/or measurement process. The user interface components can also or alternatively comprise a display, or other visual indicator (such as a light) for providing information to the subject about the operation of the apparatus 2, including displaying the determined COPD severity score. Likewise, the user interface components can comprise an audio source for providing audible feedback to the subject about the operation of the apparatus 2, including an audible indication of the determined COPD severity score.

[0055] It will be appreciated that in some embodiments the apparatus 2 is a dedicated apparatus for determining COPD severity (i.e. the sole purpose of the apparatus 2 is to determine the COPD severity). However, in other embodiments, the COPD severity score according to the invention can be determined by any type of apparatus or device that comprises a sensor 4 that is able to obtain the required measurements for determining the COPD severity score. For example, the apparatus 2 can be a user-worn or carried activity or motion monitor that monitors the physical activity of the subject, for example for personal fitness purposes, for supporting injury or fall prevention, or for detecting falls. In some embodiments, the apparatus 2 can be in the form of a smart phone executing a suitable application.

[0056] To assess the severity of COPD, the invention makes use of various clinical indicators of COPD severity that can be easily measured by a simple apparatus 2, and that can be measured simultaneously and continuously, if required.

[0057] Four parameters of a subject have been identified that can be combined and used to assess COPD severity. These parameters are the activity level of the subject, the breathing rate of the subject, a measure of respiratory effort (such as the ratio of inhaled to exhaled breath) and a measure of the severity or intensity of coughing (such as the number of coughs in a predetermined period of time, for example a minute or hour). These parameters are all clinically known to be highly sensitive for the determination of COPD severity and are closely linked to respiratory system function. The close correlation between the parameters is illustrated for instance by the fact that a subject with moderate to severe COPD will almost always experience an increased breathing rate during physical activity along with an increased coughing rate and decreased inhaled to exhaled breath ratio.

[0058] Although these parameters are sensitive to COPD severity, individually they do not provide a reliable measure of COPD sensitivity in a subject. Therefore, the invention provides that measurements of these four parameters are combined to determine a COPD severity score, which is similar in concept to the BODE score described above.

[0059] Since these parameters can be measured continuously or frequently throughout the day, the invention provides significant advantages over existing solutions as it can be used to monitor the progression of COPD severity over time. Moreover, continuous monitoring allows daily variations and artefacts to be distinguished better than a point-of-care solution and it permits long-term COPD disease progression to be assessed. With continuous or frequent monitoring the COPD severity score according to the invention can provide early warnings of impending exacerbations and be used for COPD therapy management, e.g. medication dosing and exercise scheduling. In some embodiments, to improve and maintain the clinical reliability of the invention, a BODE-equivalent score can be obtained from the four parameters set out above and compared to a standard BODE score obtained during a scheduled out-patient, point-of-care visit with a doctor.

[0060] The flow chart in FIG. 3 illustrates a method of assessing the severity of COPD in a subject according to the invention. In a first step, step 101, measurements of the breathing rate, the activity level, a measure of respiratory effort and a measure of the severity or intensity of coughing are determined. As noted above, these measurements are preferably determined from the output of a single sensor 4, such as an accelerometer.

[0061] Then, in step 103, the measurements of the parameters are combined to determine a score representing the severity of the COPD in the subject. Those skilled in the art will appreciate that there are a number of ways in which a COPD severity score can be formed from the measurements. In some embodiments, severity ranges can be defined for measurements of each of the four parameters, with score values being assigned to each severity range, and the COPD severity score obtained by summing the score values associated with the measurements of each parameter. This way of determining the COPD severity score is illustrated by the exemplary table in FIG. 4 (in which the measure of respiratory effort is represented by a ratio of inhalation to exhalation and the measure of the severity or intensity of coughing is represented by the number of coughs over an hour) and is similar to the way in which the BODE score is determined.

[0062] FIGS. 5-8 illustrate exemplary ways in which the breathing rate, a measure of respiratory effort (in particular the ratio of inhaled to exhaled breath), activity level and a measure of the severity or intensity of coughing (in particular the number of coughs in a predetermined time period) can be determined from accelerometer measurements.

[0063] The breathing rate is typically measured in terms of the number of breaths per minute (bpm). In some embodiments, the breathing rate can be determined from the acceleration measurements by applying a filter to the raw accelerometer signal in the frequency domain that passes frequencies in a range corresponding to typical or possible breathing rate. This is shown in FIG. 5(a). For example, the filter can pass frequencies in the range of 0.15-0.70 Hz (corresponding to breathing rates between 9-42 bpm). It will be appreciated that a higher breathing rate is associated with more severe levels of COPD and decreased respiratory function.

[0064] FIG. 5(b) illustrates an exemplary way of processing the acceleration signals to determine the breathing rate. The signals from the accelerometer 4 (111 and shown in FIG. 5(c)) are processed (in 113) to determine the energy expenditure over a predetermined time period (1 minute in this example). Those skilled in the art will appreciate that 113 can be performed in a number of ways. For example the type of activity that the subject is performing (e.g. walking, riding a bike, etc.) can be detected and a given energy expenditure for the particular activity assumed. Alternatively, the physical activity energy expenditure can be estimated directly from the accelerometer signals. The result of 113 is divided into three parts, representing low energy expenditure, medium energy expenditure and high energy expenditure, and each is bandpass filtered to obtain breathing vectors (115). The bandpass filter should pass at least frequencies corresponding to typical breathing rates (e.g. 12-15 breaths per minute, bpm, for normal adults), and perhaps some of the harmonics of those frequencies as well. The breathing vectors are shown in FIG. 5(d). In 117 the vectors are processed using a principle component analysis (PCA) method to obtain a ‘breathing wave’ (as shown in FIG. 5(e)). Then, in 119, the respiration rate is computed by analyzing the breathing wave using a power spectrum analysis technique.

[0065] The ratio of inhaled to exhaled breath is the ratio of the time taken to inhale to the time taken to exhale. Like the breathing rate, in some embodiments the ratio of inhaled to exhaled breath can be determined from the acceleration measurements by applying a filter to the raw accelerometer signal to distinguish the time period required for inspiration versus expiration. FIG. 6(a) shows measurements of airway pressure as a subject inhales and exhales (it will be appreciated that this graph is provided to illustrate how the ratio is calculated, in the preferred embodiments the ratio of inhaled to exhaled breath is measured from accelerometer measurements as described below, although in less preferred embodiments an air pressure sensor could be used instead). During inhalation, the chest will generally move outwards; during exhalation, the chest will move in the opposite direction. Changes in the movement direction can be identified in the accelerometer measurements as zero crossings (i.e. where the acceleration in the direction parallel to the movement of the chest is zero). Therefore the period between zero crossings represents the duration of both inhalation and exhalation. FIG. 6(b) shows an exemplary signal from an axis of the accelerometer that is optimally attached to the subject so that the inward and outward movements of the chest or abdomen are represented in the signal. The signal is low pass filtered to obtain the signal in FIG. 6(c), from which the zero crossings can easily be identified. The cut-off frequency for the filter can be selected so that it passes frequencies corresponding to typical breathing rates (e.g. a typical breathing rate for a normal adult is 12-15 bpm, so the cut-off frequency should pass these frequencies). The periods between the zero crossings represent the duration of the inhalation or exhalation.

[0066] For patients with COPD greater effort is required for exhalation than inhalation, which means that there is a significant difference in the momentum change (i.e., acceleration) of the chest and abdomen during inhalation and exhalation, which can be easily detected by the accelerometer. Inhaled to exhaled breath ratios less than 1 represent higher COPD severity than ratios greater than 1. It will be appreciated that measures of the respiratory effort other than the ratio of inhalation to exhalation can be determined in alternative embodiments of the invention. For example, measures representing the energy, intensity or strength of the respiration can be used, such as the amplitude, the root-mean-squared, RMS, value, the average or the Teager energy ratio of a respiration signal isolated or separated from the acceleration signal.

[0067] The activity level of the subject represents the physical activity/movement level of the subject in a given period of time. Those skilled in the art will be aware of various ways in which the activity level of a subject can be determined. In some embodiments, the activity level can be detected by quantifying the amplitude and frequency of the detected accelerations in time intervals of, for example, 1 or 2 minutes, to determine whether the subject is moving or exerting physical effort. An exemplary acceleration signal that has been processed to detect activities is shown in FIG. 7. The y-axis represents acceleration, and the arrows indicate detected activities. The activity level can be used to determine the state of the subject at the time that their breathing rate and the ratio of inhaled versus exhaled breathing effort is measured, and also to give an indication of how active or sedentary a subject is during the course of the day. The paper “The technology of accelerometry-based activity monitors” by Chen et al. Med Sci Sports Exercise 2005 Nov; 37(11 Suppl): S490-500 describes a suitable approach for calculating the activity level of the subject.

[0068] The number of coughs over a predetermined period of time (e.g. per minute, per hour, etc.), which can also be referred to as a ‘cough rate’, can be determined by detecting artefacts in the acceleration measurements. In particular artefacts can be detected in the filtered accelerometer measurements used to detect the breathing rate above (e.g. as shown in FIG. 5(e)) or the filtered acceleration measurements used to determine the measure of respiratory effort (e.g. as shown in FIG. 6(c)). An extract from a suitable signal is shown in FIG. 8. In FIG. 8, the parameter a represents the maximum amplitude of the breathing signal, the parameter b represents the minimum amplitude and the parameter c represents the average amplitude. Coughing can be detected using a classification algorithm that detects short, high impulse, large-amplitude motion signals as coughs, and longer, low-amplitude motion signals as gasps. It will be appreciated that measures of the intensity or severity of coughing other than the number of coughs over a predetermined period of time can be determined in alternative embodiments of the invention. For example, measures representing the energy, intensity or strength of the coughing can be used, such as the amplitude, the root-mean-squared, RMS, value, the average or the Teager energy ratio of a signal representing the coughing that is isolated or separated from the acceleration signal.

[0069] The number of coughs over a certain period of time, for example 1 hour, can be used to assess the respiratory condition and can also be used as an aid in the prediction of exacerbation events. In particular, a high cough count (high compared to an average for the COPD population or high for the specific subject being assessed) can be an indicator that the subject may be at risk of, or experiencing, an exacerbation in their symptoms. Therefore, the cough count or other measure of the intensity or severity of coughing can be compared to a threshold value to determine if there is a high risk of an exacerbation event or an exacerbation event is ongoing.

[0070] In some embodiments, when a cough or gasp is detected, the control unit 6 may temporarily interrupt the calculation or use of the other parameters in determining a COPD severity score until the coughing or gasping has stopped or subsided since the coughing or gasping may affect the accuracy of the other parameters determined from the accelerometer signal.

[0071] As noted above, there are a number of ways in which a COPD severity score can be formed from the measurements determined in step 101.

[0072] A scoring system to assess respiratory function and COPD severity can be developed by classifying the measured parameters (i.e. activity level, breathing rate, respiratory effort and measure of the severity or intensity of coughing) based on a simplified version of the BODE score. Preferably, baselining and calibration of the COPD severity score according to the invention against the existing BODE score can result in both scores providing a similar clinical value (although the COPD severity score according to the invention is more readily obtainable).

[0073] The table in FIG. 4 illustrates how parameters can be weighed and combined to assess COPD severity according to an exemplary embodiment of the invention. In this embodiment, for each parameter measurement, the deviation with respect to a desired ‘normal’ range is scored (e.g. given a value of 0, 1, 2 or 3), which is also referred to as a ‘severity range’, and the scores are added to arrive at a COPD severity score. It will be appreciated that the range of parameter values within each level of severity (e.g. 600-899 activity counts for a score of 1) illustrated in FIG. 4 is exemplary and other ranges can be used.

[0074] An exemplary system for the COPD severity score could be: very mild COPD (0-3 ponts), mild COPD (4-6 ponts), moderate COPD (7-9 ponts), and severe COPD (>9 points).

[0075] It will be appreciated that there are alternative ways of calculating the COPD severity score to the use of the table shown in FIG. 4. For example, analysis of the parameters to determine an indication of the COPD severity can use a classification algorithm (such as a Bayesian classification algorithm or a neural network) to adaptively weight the parameter values in order to determine the COPD severity.

[0076] Two ways of determining the ‘normal’ and other severity ranges for each parameter are set out below.

[0077] In a first technique, an initial clinical diagnosis by a general practitioner (GP) of COPD based on the clinically accepted standard BODE score (obtained using traditional approaches with multiple sensors) is compared to a BODE-equivalent score obtained from measurements of the four parameters (along with measurements of FEV and BMI). The derivation of a BODE-equivalent score from the measurements of the four parameters used herein is described in more detail below. The standard (full) BODE score has established ranges for each parameter (FEV, BMI, 6MWD and Dyspnea) as shown in FIG. 1. By comparing a BODE-equivalent score obtained from the four parameters, the ranges in the full BODE score will also be intrinsically incorporated into the BODE equivalent COPD severity score. Adjustment or calibration of the BODE score obtained from the four parameters can be achieved, for example, by finding the ratio of the BODE score obtained in the standard manner to the BODE score obtained from the four parameters measured according to the invention, and using the ratio as a multiplication factor for the equivalent BODE score obtained using the invention. This ratio can be adjusted each time that a new BODE score is obtained using the standard approach during a clinical visit. Those skilled in the art will be aware of other ways of calibrating the equivalent-BODE score obtained using the invention to the standard BODE score. In one alternative, the calibration can be based on individual parameter weighting factors that are derived, for example, by calibrating the activity level to the 6-minute walking distance, and calibrating the breathing rate and respiratory effort to the MMRC Dyspnea scale (FEV and BMI are the same for both the standard BODE score and the equivalent BODE score obtained using the invention). In this way the COPD severity scoring system according to the invention is calibrated and highly correlated with the standard BODE score.

[0078] Moreover, since COPD is a progressive, degenerative respiratory disease with no cure, the respiratory function of the subject will, without exception, decline over time. Thus each parameter measurement obtained during use of the apparatus 2 can be normalized using the initial or baseline value obtained by the apparatus 2 at the initial clinical diagnosis (and compared to the full BODE score obtained in the conventional manner) or at the first use of the apparatus 2. ‘Baselining’ also ensures that a subject-specific COPD severity score is obtained since it allows the current COPD severity of a subject to be compared to their initial baseline severity score, which means that at any given time an assessment can be made as to how severe or mild the COPD symptoms of the subject are (i.e. an assessment of the disease progression). If this was not done, then a subject can be compared to a statistical average of the COPD population, although this may not allow small fluctuations or degradations in COPD severity to be detected.

[0079] In a second technique, statistical analysis (e.g. using a bias corrected and accelerated bootstrap method, Lilliefors testing, Shapiro-Wilk W testing, principal component analysis, etc.) of a database of data for a set of subjects with COPD and/or of an elderly population group, including healthy individuals and subjects with COPD can be used to identify suitable ranges of values. This analysis can also compare factors such as age and ambulatory status (e.g. does the subject use a walking aid) and the results of this comparison can be used to further refine these ranges to ensure appropriate specificity.

[0080] In some embodiments, regardless of how the normal and increasing severity ranges are determined, the ranges for some or all of the parameters can be set or adjusted based on the ambulatory state or capability of the subject, which means that different subjects can have different normal values/ranges. In particular a subject that uses equipment to assist them to walk, such as a frame or walking stick, will have a different ambulatory capability than subjects that are able to walk unassisted. In these embodiments it is therefore important to take the ambulatory state of the subject into account when assessing the COPD severity in order to arrive at an appropriate value for the COPD severity score. Since the ambulatory state of the subject (for example in terms of whether walking aids are required) is not something that is typically expected to vary day-to-day, the ambulatory state of the subject can be input to the apparatus 2 during a set-up or calibration phase. For a less-capable subject the normal value ranges for activity count may be at least 50% less than for a more-capable subject, and the scoring ranges for the activity count parameter can be adjusted accordingly. Other parameters, such as the measure of respiratory effort, are not affected as significantly, but some smaller adjustment to the scoring ranges can be made if required.

[0081] Based on the COPD severity score determined according to the invention, an appropriate clinical intervention can be made. This may involve a clinician adjusting the dosing of the bronchodilators or adjusting the timing of the dose or the timely administration of corticosteroids to avert a predicted exacerbation event. It may also or alternatively involve providing the subject with an indication that an exacerbation event may occur and advising them to take a dose of bronchodilators.

[0082] In further or alternative embodiments, in addition to determining the COPD severity score according to the invention, the apparatus 2 can also be used to derive a ‘full’ BODE score (e.g. as shown in FIG. 1). In this case, either the apparatus 2 can be provided with measurements of the BMI and the FEV for the subject (for example by the subject or a clinician manually inputting them into the apparatus 2) and the apparatus 2 can calculate the full BODE score, or the parameters measured by the apparatus 2 can be output to another device which can calculate the BODE score. It will be appreciated that the BMI and FEV are measurements that are routinely taken by clinicians during periodic patient check-up visits. The 6-minute Walking Distance and MMRC Dyspnea Scale required for the full BODE score can be derived from the activity level, position tracking (if the apparatus 2 includes a suitable sensor for determining the location or position of the subject) and breathing rate measurements obtained through the day, e.g. during dressing and undressing, when walking around the house or when walking to and from the supermarket. In some cases initial starting input values may be used by the device to generate an initial BODE score prior to optimization or personalization for the subject. Over time as measurements are acquired by the apparatus 2 it will generate a more optimal or personalized score. Other subject-specific starting settings might include the timing of generating the unobtrusive COPD severity score. For example, if a subject typically goes for a walk at a specific time of day, the apparatus 2 can schedule a COPD severity score measurement at that time.

[0083] As noted above, in further embodiments, the apparatus 2 can include additional sensors to the accelerometer 4 for measuring other parameters that can improve the assessment of the COPD severity or of the general health of the subject. One such sensor is a temperature sensor, e.g. a zero heat flux temperature sensor, which can be used to detect changes in the body temperature of the subject that can occur when a respiratory infection occurs. The measurements from the temperature sensor can be used in the clinical management of COPD patients (for example to determine whether to adjust a medication level or determine that a new medication may be required, e.g. in the case of a respiratory infection).

[0084] In further or alternative embodiments, the apparatus 2 can improve the assessment of the activity level of the subject beyond a simple activity count. In some embodiments, the control unit 6 can implement an activity classifier algorithm to attempt to classify the activity that the subject is engaging in (e.g. sitting down, lying down, walking, exercising, etc.). Suitable classifier algorithms will be known to those skilled in the art. In some embodiments, the apparatus 2 can include a satellite position system receiver to track the location of the subject (and thus also provide an indication of the speed of movement of the subject). This location and speed information can be used to improve the estimate of the activity being performed by the subject, since some activities, e.g. bicycle riding, will provide a low activity count according to the technique described above since only the subject's legs are moving. This will greatly improve the reliability of the device.

[0085] Although in preferred embodiments the parameters are measured continuously or frequently throughout the day, it will be appreciated that it is possible in some circumstances that values for one or more parameters cannot be calculated by the apparatus 2. This means that the COPD severity score cannot be calculated at that time. Instead, values for the missing parameters can be input to the apparatus 2 at a later stage to enable the calculation of the COPD severity score to be completed.

[0086] FIG. 9 provides an overview of various ones of the embodiments described above. FIG. 9 shows the sensors that can be provided in the apparatus 2, the parameters that can be derived from the sensor measurements, and the processing steps or analysis that can be performed on the sensor measurements. The accelerometer 4 and parameters derived from the acceleration measurements (activity level, breathing rate, measure of the respiratory effort and measure of the severity or intensity of coughing) are shown with a solid outline to indicate that they are used in all embodiments, and the other sensors (GPS tracker, activity classifier and temperature sensor) and parameter (temperature) are shown with a dashed outline to indicate that they are optional features. Thus, as described above, the parameters derived from the acceleration measurements are compared to respective severity ranges to determine a COPD severity score (step 150), and the parameters or scores can be weighted and/or combined in step 152 to generate a simplified BODE score or a full BODE score (if measurements of FEV and BMI are provided—step 153). Feedback on the score can then be provided to the clinician or subject or another person (step 154), and, if necessary, a warning of an imminent exacerbation can be given.

[0087] As noted above, the invention provides an apparatus and method which determines measurements of several physiological characteristics of a subject that are clinical indicators of COPD severity (breathing rate, activity level, measure of respiratory effort and measure of the severity or intensity of coughing and that combines them into a single COPD severity score. The nature of the physiological characteristics used to form the score means that it is possible to continuously, automatically and reliably monitor or indicate COPD severity and respiratory function for the subject. The apparatus and method according to the invention improves the clinical management of subjects suffering from COPD. In addition, the apparatus and method may also be useful for the monitoring of other respiratory diseases including pneumonia, tuberculosis, emphysema, and chronic bronchitis, among others.

[0088] While the invention has been illustrated and described in detail in the drawings and foregoing description, such illustration and description are to be considered illustrative or exemplary and not restrictive; the invention is not limited to the disclosed embodiments.

[0089] Variations to the disclosed embodiments can be understood and effected by those skilled in the art in practicing the claimed invention, from a study of the drawings, the disclosure and the appended claims. In the claims, the word “comprising” does not exclude other elements or steps, and the indefinite article “a” or “an” does not exclude a plurality. A single processor or other unit may fulfill the functions of several items recited in the claims. The mere fact that certain measures are recited in mutually different dependent claims does not indicate that a combination of these measures cannot be used to advantage. A computer program may be stored/distributed on a suitable medium, such as an optical storage medium or a solid-state medium supplied together with or as part of other hardware, but may also be distributed in other forms, such as via the Internet or other wired or wireless telecommunication systems. Any reference signs in the claims should not be construed as limiting the scope.