|Publication number||US20060235316 A1|
|Application number||US 10/531,764|
|Publication date||Oct 19, 2006|
|Filing date||Oct 16, 2003|
|Priority date||Oct 18, 2002|
|Also published as||EP1553869A1, EP1553869B1, US6881191, US20040077954, WO2004034896A1|
|Publication number||10531764, 531764, PCT/2003/4487, PCT/GB/2003/004487, PCT/GB/2003/04487, PCT/GB/3/004487, PCT/GB/3/04487, PCT/GB2003/004487, PCT/GB2003/04487, PCT/GB2003004487, PCT/GB200304487, PCT/GB3/004487, PCT/GB3/04487, PCT/GB3004487, PCT/GB304487, US 2006/0235316 A1, US 2006/235316 A1, US 20060235316 A1, US 20060235316A1, US 2006235316 A1, US 2006235316A1, US-A1-20060235316, US-A1-2006235316, US2006/0235316A1, US2006/235316A1, US20060235316 A1, US20060235316A1, US2006235316 A1, US2006235316A1|
|Inventors||Gary Ungless, Nigel Oakley|
|Original Assignee||Ungless Gary S, Oakley Nigel R|
|Export Citation||BiBTeX, EndNote, RefMan|
|Patent Citations (15), Referenced by (29), Classifications (17), Legal Events (1)|
|External Links: USPTO, USPTO Assignment, Espacenet|
This invention relates to a cardiac monitoring apparatus and method for monitoring a user's heart rate, or other parameters derived from heart-beat sensing.
Heart rate is a physiological parameter that is measured in a wide variety of situations, for example to determine the health status and fitness of a person or animal. It can be used, for example, to give a measure of energy expenditure of an individual and a number of devices exist for doing this by converting heart rate to calories used. Many conventional systems comprise a belt worn around a user's chest and carrying a heart-beat sensor and a radio transmitter for transmitting measured data to a wrist-worn display unit.
Such conventional systems are generally uncomfortable or impractical to wear for extended periods and also suffer a significant problem in that correlating heart rate with calories used may only be effective for exercise rates achieving significant heart rate increases. Smaller increases in heart rate can be due to, for example, stress rather than physical exertion and may therefore be misinterpreted by conventional heart-rate monitoring systems.
The invention provides an apparatus and a method for monitoring a user's heart as defined in the appended independent claims. Preferred or advantageous features of the invention are set out in dependent subclaims.
The invention may thus advantageously provide a monitor for monitoring a user's heart, comprising a cardiac sensor and a support means for mounting the monitor only on a single adhesive pad, which is preferably an electrocardiogram (ECG) electrode. The monitor is then advantageously both physically supported by the single electrode and electrically connected to it for receiving signals for monitoring the user's heart. A lead extends from the monitor to receive signals from a second ECG electrode, spaced from the first, to enable cardiac monitoring. Further leads coupling the monitor to further ECG electrodes may advantageously allow monitoring of more than one ECG channel. The leads may either extend from a monitor housing or plug into sockets in the monitor housing.
The monitor may comprise a memory for recording data from the cardiac sensor over a period of time, which may then be downloaded for analysis. If more than one ECG channel is to be monitored, it preferably contains sufficient memory to store data from multiple channels for an extended period, such as 24 hours or more. Since the monitor is advantageously of light weight and small size, its housing preferably being of smaller lateral dimension than an ECG pad, it may advantageously be comfortable to wear continuously for periods of as long as days or more.
In a preferred embodiment, the apparatus of the invention consists of a small, lightweight monitor that may measure not only heart rate but also inter-beat interval and/or other cardiac parameters.
The following description of the invention refers mainly to a preferred embodiment in which the monitor further comprises an accelerometer for actigraph measurement. It should be noted, however. that the skilled person will be readily able to identify and assess those features and advantages of this embodiment which similarly apply to the cardiac monitor mounted on a single ECG pad described above.
In the preferred embodiment, the invention may advantageously provide a monitor comprising a heart-beat sensor and an accelerometer which can be secured in position on a single adhesive pad for sensing a user's heart-beat and movement, or activity. The monitor further comprises a processor for receiving signals from the heart-beat sensor and the accelerometer and for generating heart-rate or other cardiac data, and movement or activity data. The monitor preferably comprises a memory in which the data can be stored.
The monitoring of both a user's heart rate and movement addresses the problem outlined above, that heart rate increases are not necessarily correlated to physical exertion. Thus, a record of the user's movement can be correlated with heart rate measurements to improve evaluation of the user's energy expenditure. The range of uses for such an apparatus or method in the medical field is widespread. For instance, it can be used in cardiology, sleep medicine, diabetes, obesity, eating disorders, psychiatric disorders etc. It can also be used in monitoring the fitness levels of individuals and as a means for assessing their energy expenditure. This may be done for a variety of reasons, such as weight loss, rehabilitation, encouragement to exercise etc.
The monitor is preferably couplable to a conventional adhesive electrocardiogram (ECG) electrode or pad attachable to the user's chest. Two such ECG electrodes are preferably used, as in conventional ECG measurement. The monitor may then clip directly to one of the ECG electrodes, achieving both electrical connection and mechanical support. An electrical lead may then couple the monitor to the other ECG electrode.
Many different types of ECG electrode pads are available for many different applications, for example to cater for different patient skin types, shapes, and sensitivity, or for long term or short term applications. Thus, some types of electrode have adhesive allowing for easy removal after short term use and others have stronger adhesive allowing for long term skin adhesion. As illustrated in
Preferably, a zero insertion force clip is used to connect the monitor embodying the invention to a conventional ECG electrode. If an ECG electrode comprises an electrode gel as described above, and a large force is applied to connect the monitor to such a pad, then this gel may be forced out past the adhesive surrounding it. Advantageously, a zero insertion force clip, for example a slider clip, may prevent the gel being forced out. A high application force for attaching a monitor to a clip may also cause the ECG electrode to deform thereby making attachment of the monitor difficult or even damaging to the electrode. This problem may be exacerbated if the user, or patient, has normal or large amounts of body fat. A zero insertion force clip may, advantageously, make the monitor easier to mount and prevent distortion of the ECG electrode during mounting of the monitor.
Preferably, the unit is securely fixed to the ECG electrode pad so that it will not rotate on the pad during normal use. Any rotation of the monitor on the pad may cause a loss of resolution of the movement (preferably vertical movement) detected by the accelerometer. Advantageously, a clip with a high clamping force may reduce rotation on the pad during normal use. A high clamping force may also, advantageously, reduce contact resistance problems. These factors may favour a high clamping force and so may further exacerbate the problems arising if a zero-insertion-force clip is not used, because otherwise a high clamping force typically requires a high insertion force. In a preferred embodiment, therefore, the monitor is attached to the electrode pad by means of a zero insertion force slider clip, clamping force being provided by a spring contact and the spring being manually retracted as the monitor is attached. Being small and of light weight, the monitor is advantageously unobtrusive and can be worn for long periods by people of all ages and health or fitness status.
Data from the heart-beat sensor and the accelerometer are advantageously stored in a memory within the monitor, which negates the need for radio or other transmission of data from the monitor. Data may then be downloaded from the monitor by interfacing it to, for example, a computer such as a PC. In a preferred embodiment, the monitor interfaces to the PC through the same contacts as used for coupling to the ECG electrodes. Particularly advantageously, the same contacts may also be used for charging a battery within the monitor.
By analysing data downloaded to a PC, it may advantageously be possible to establish whether small but significant changes in heart rate (usually increases in heart rate) are due to physical exertion or not, and therefore whether heart rate increases may be due to, for example, stress. This may improve estimation of energy expenditure derived from physical activity and its consequences in terms of heart rate and performance.
Alternatively, by identifying changes in heart rate which are not associated with physical activity, conditions such as stress may be identified and/or monitored.
In another embodiment, the monitor may interface with an external device such as a wrist-worn actigraphy device, by means of radio transmission. In this embodiment, the ECG input lead may be used as an antenna for RF output. Heart rate and activity data may then be transmitted to a wrist-worn actigraphy device. Advantageously, for example this wrist-worn actigraphy device may sense reduced upper-body activity whilst the user is seated and engaged in activities such as typing or knitting, which might otherwise cause a wrist-worn actigraph, on detecting significant movement, to estimate an inaccurately high level of energy expenditure. The device may then combine all the data to further enhance the measurement of physical activity and stress. More accurate measurements may be made using both chest-worn and wrist-worn actigraphs in this way, but in alternative embodiments other systems may be implemented. For example a chest-worn monitor for cardiac and activity data may transmit data by radio transmission to a fixed receiver, for example next to an exercise machine for monitoring the user's heart rate and activity while exercising.
Alternatively a chest-worn cardiac monitor (not incorporating an actigraph) could transmit cardiac data to a wrist-worn actigraph or to a fixed receiver.
Normal commercial electrode pad adhesives are designed to retain normal ECG leads and clips. In many monitoring applications, longer lead wires are required, and are separately supported to prevent pulling on the electrode pad. Preferably, the monitor embodying the invention is of similar weight to a single short ECG lead wire and clip. This means that the weight of the monitor does not pull on a normal electrode pad beyond the pad's design load. By being light weight, the monitor places a low load on the adhesive pad. Advantageously, this means that the monitor does not require the separate safety straps or wires that are deemed necessary for other, heavier, units mounted on multiple pads.
Preferably, the weight of the monitor is less than 50 g, or particularly preferably less than 25 g or 15 g. In a preferred embodiment the monitor weighs about 10 g or less.
Devices that mount on to multiple adhesive pads, or any device mounted on a single adhesive pad larger than a conventional ECG electrode pad, will disadvantageously require complicated mechanical arrangements, for example articulation or a flexible housing, to allow for the free movement of the body and resulting skin expansion and contraction. Advantageously, mounting at a single point, particularly on a standard ECG electrode pad, reduces the problems associated with free body movement and skin expansion and contraction. It is notable that this problem is taken into account in designing conventional ECG electrodes; these are of limited size in order to avoid problems arising from skin stretching and contraction.
These features of preferred embodiments of the invention may solve a number of problems in prior art heart-rate monitors. In prior art systems, for example, the transmission of data from a chest band using a radio link is subject to a wide range of interference, such as from electric motors, televisions, telephones etc., which typically leads to a large number of data points being lost and classed as “dropouts”. Typically 10-20% of data points are lost in this way per day of monitoring. On-board storage of data within the apparatus embodying the invention solves this problem, as well as advantageously eliminating any electromagnetic transmissions from the apparatus which may interfere with other apparatus, such as medical apparatus.
In prior art systems, there is a lack of data storage facilities to allow for long-term accumulation of data, for example over periods of more than 24 hours. The memory in the monitor embodying the invention solves this problem.
The use of a chest-worn band for supporting a heart-rate monitor is not suitable for various categories of people, such as the very young, the very old and the obese, and is not comfortable for long-term use. The use of ECG electrodes-to support and connect the monitor of the embodiment solves this problem and makes the monitor more comfortable to use.
Prior art heart-beat sensors are typically only used to measure heart-rate itself and not other important cardiac parameters such as inter-beat interval. The on-board processor of the embodiment can be programmed to measure any such parameters, particularly when combined with the use of ECG electrodes as these provide a very clear heart-beat signal.
In a preferred embodiment, when the monitor is supported on a user's chest or torso, the accelerometer should be oriented to detect vertical movements of the user's chest or torso. The inventors have found that this provides the most effective sensing of user movement, or activity.
The inventors have also found that the processing of the heart-beat sensor output to extract heart-rate and other cardiac information may advantageously be modified in response to the output from the accelerometer. Thus, for example, the gain and thresholds for ECG measurement are preferably adjusted based on the current user activity level measured by the accelerometer. During periods of activity, noise artefacts tend to be induced in the ECG signal by variations in skin potentials and using the activity data to improve the signal-to-noise ratio of the ECG signal helps to ensure a clean and uninterrupted data stream.
Although reference has been made to storing movement and heart-rate measurements in a memory housed within the apparatus of a preferred embodiment, other possibilities are envisaged within the scope of the invention. Thus, heart-beat or heart-rate data and movement data may be downloaded or transmitted to a remote display unit or data storage unit during use so that these signals may be monitored by a user, for example during exercise. If a user is engaged in a repetitive physical exercise such as, for example, running, output from the movement sensor may not only be valuable in combination with heart-rate measurement as described above but may also be used to determine the user's stride rate or the number of strides performed, for example.
An apparatus or method embodying the invention may be used for monitoring human or animal users.
Specific embodiments of the invention will now be described by way of example, with reference to the accompanying drawings, in which:
The clip 4 of the monitor 2 mounts on the electrical contact of one electrode 6. The monitor comprises an electrical lead 10 for coupling to the other ECG electrode 8. The lead carries at one end a plug 12 which is removably insertable into a socket in one side of the monitor housing, and at the other end a clip 14 which is removably connectable to the ECG electrode contact.
For user comfort, the lead 10 should be longer than the distance between the ECG electrodes, to accommodate user movement.
The monitor comprises an accelerometer, as described below, which is primarily sensitive to movement in a particular direction. In the embodiment the accelerometer is mounted within the monitor so as to detect vertical motion of the user's chest, which requires that the monitor is mounted and retained in the correct orientation on the ECG pad. The correct orientation for mounting the monitor is indicated to the user by a marking on the monitor casing. Once fitted to the ECG electrode, the clip 4 holds the monitor in position. The lead connecting the monitor to the second ECG pad also helps to orient the monitor correctly.
As shown in
The monitors illustrated in
Preferably, the monitor is less than 35 mm in diameter (or lateral or vertical dimension). The preferred position for both actigraphy measurement and ECG electrode pad positioning is on or near the sternum. In order to fit comfortably between female breasts, the size of the monitor housing should be similar to or smaller than that of many normal ECG electrodes. Advantageously, a diameter of about 30 mm, or a lateral dimension of about 30 mm, is of this order.
In addition, the monitor should advantageously be less than 15 mm in thickness and particularly preferably less than 10 mm or less than 6 mm in thickness. These dimensions aim to ensure user comfort.
Advantageously, these thickness dimensions mean that the monitor housing is of low profile. A low profile may, advantageously, render the monitor almost invisible when worn under clothing. The low profile may also reduce interactions between the monitor and clothing which would otherwise cause movement or tipping of the monitor, or even rip the monitor from its mounting. Interaction with clothing may cause undesirable movement of a monitor of larger diameter or a monitor having a greater thickness. Devices that hang from an ECG electrode by a wire may also suffer from the same excessive movement problem.
When the monitor is clipped to an electrode pad, there may be a gap between the monitor and the pad. Preferably, this gap is narrow. A large gap may allow the monitor to tip or allow clothing to rip the monitor from the pad. Tipping of the monitor is also undesirable as it may generate spurious movement data or affect the ability of the accelerometer to detect vertical movement. A narrow gap, or no gap, between monitor and pad may, advantageously, lessen these undesirable effects.
Movements of the monitor, such as twisting or tipping, on the electrode pad may cause ECG noise artifacts. A small size and low profile may help to reduce excessive noise artifacts caused by movement of the monitor. The monitor may then, advantageously, be used during vigorous exercise without generating excessive noise artefacts.
The circuit comprises a microcontroller 30 which receives inputs from a clock (crystal oscillator) 32, an accelerometer 34, two ECG electrodes 6, 8 and a communications and power management module 38. The microcontroller 30 is also coupled to a memory 40 and a battery (re-chargeable coin cell) 42. All of these components are mounted on a printed circuit board (PCB) which is housed within a monitor casing or housing such as illustrated in FIGS. 1 to 4.
The accelerometer is a piezoelectric accelerometer, which is mounted on the PCB in a predetermined orientation such that it is most sensitive to motion in a predetermined direction when the PCB is housed in the monitor casing and the monitor is in use. For example, in the chest-mounted embodiments of FIGS. 1 to 4, the accelerometer is oriented to be most sensitive to movement in the vertical plane (i.e. sensitive to physical movement in the up/down direction), during use when the user is upright. In this way, a good approximation of the physical activity of the user may be deduced. In other applications for sensing other movements of a human or animal body it may be desirable to mount the accelerometer in different predetermined orientations within the monitor casing.
The signal from the accelerometer is amplified by an amplifier 44 and filtered by a filter 46 before being input to an analog input of the microcontroller.
The ECG electrodes are usually attached to the mid-left region of the user's chest and the monitor is coupled between them. The monitor may comprise a small light emitting diode (LED) which flashes for several beats to indicate when an ECG signal is initially detected. It may additionally flash whenever a heartbeat is detected, allowing the user to confirm that the monitor is picking up an ECG signal.
Preferably, the LED flash is modulated at high frequency so that a light receiver can easily detect its light. Advantageously, this enables remote electrically-isolated short-ranqe readout of the heart rate in fitness tests such as treadmill tests.
The signals from the ECG electrodes pass through two monitor contacts 48 and are amplified in two stages by two amplifiers 50, 52 and filtered by a filter 54 before being input to an analog input of the microcontroller.
The ECG signal is processed within the microcontroller to remove noise artefacts. As the monitor is totally self-contained, there are no problems with interference from radio frequency devices or other sources of electromagnetic interference.
The microcontroller uses a 4.0 MHz internal clock for instruction timing but uses an external 32.768 kHz oscillator, shown in
The communications and power management block 38 is coupled to the monitor contacts 48 and comprises discrete circuitry which allows various signal levels and frequencies at the contacts to be discriminated by the microcontroller. This allows the monitor contacts to be used as monitor inputs or outputs for multiple functions depending on the device to which the contacts are coupled. Thus, if the contacts are coupled to ECG electrodes, ECG signals can be identified and received by the microcontroller. If the contacts are coupled to an interface unit or reader as described below, the same contacts can be used by the microcontroller to download data, re-charge the battery, or other applications as described below.
The battery 42 is a surface-mounted manganese lithium secondary (re-chargeable) coin cell that provides up to 22 days of continuous operation from a full charge. During operation, the monitor may continuously record heart rate and physical activity at one minute intervals. All of the other components are also surface-mounted on the PCB to provide compact size, simplified production and increased reliability.
The circuit is provided with protection from reverse polarity connection, over-voltage and ESD (electro-static discharge). The ultra-low power and integrated nature of the monitor ensures no EMI (electromagnetic) emissions.
The device is waterproof and can hence be worn continually to provide an uninterrupted data stream.
In the monitor, certain firmware (embedded software) is programmed into an internal ROM (read only memory) area of the microcontroller 30 and controls many of the monitor's functions. In particular, the firmware enables the sampling of signals from the accelerometer and the ECG electrodes under timed interrupts, with movement being sampled at 16 Hz and ECG at 128 Hz or 256 Hz. These signals are sampled at different rates to reflect the different rates at which the signals typically vary. The movement data are integrated over one minute epochs and stored into non-volatile memory 40. The heart rate data are stored as beats per minute in the non-volatile memory.
The microcontroller performs several signal processing functions and executes internal algorithms on the ECG data. The key processing functions are as follows.
Dynamic threshold: the threshold for detection of the ECG R-wave pulse is dynamically adjusted within a window period to aid discrimination of true pulse signals during periods of high noise.
Variable gain: the gain and dV/dt (rate of change of voltage) thresholds for ECG measurement are adjusted based on the current user movement level detected by the accelerometer. During periods of movement, noise artefacts are induced by variations in the user's skin potentials. Using the movement data to improve the signal-to-noise ratio of the ECG signal helps to ensure a clean and uninterrupted data stream.
The monitor uses a digitally computed reference level to determine whether the dV/dt (rate of change of voltage) of the input signal meets the requirements of an ECG R-wave. This threshold varies with time and has an absolute minimum level to prevent spurius noise being seen as an R-wave. During periods of high activity the minimum threshold level is raised, as described above, to prevent spurius triggering on movement noise artifacts.
IBI Tracking: the inter-beat interval (IBI) is computed and used to update an internally stored histogram. The histogram contains discrete time windows and an IBI value falling within a histogram window causes the histogram to be incremented. An indication of variation of the inter-beat interval is very useful in determining certain medical conditions.
IBI variability logging: normal regular heart-rate data are stored as beats per minute. If serious variability is detected, the heart rate is automatically stored at a higher resolution to allow a more detailed analysis.
The reader is thus a small module that contains the electronics necessary for level shifting to and from RS232 (or USB) in addition to providing control signals for power management of the monitor. Once the monitor is connected to the reader via the ECG leads, after simply unclipping the monitor from the ECG electrodes and connecting the same contacts to the reader, bi-directional communications may take place between the monitor and the serial port of the PC. As well as allowing data to be downloaded from the monitor to the PC, the reader can also charge the monitor battery, drawing power from the PC serial port or optionally from a plug-in mains adaptor.
This software runs on a PC having a serial port to which the monitor may be coupled via the reader described above. The software is a 32-bit Windows application written in Visual Basic with an underlying database used for data management. The software has the following broad functions.
Store details of users and test data in structured and manageable database tables.
Write user and test parameters to the monitor.
Read logged data from the monitor.
Present reports in a user-friendly and flexible manner.
Provide portable data storage. This means that data can be exported to other software packages for additional analysis.
A core database 100, which is Access compatible, contains tables for user information such as name, date of birth, height etc. The database also has tables to contain downloaded heart rate, or other cardiac data, and movement, or activity, data. The tables have relational interlinking and the software generates queries to present users seamlessly with the correct downloaded data.
When a new user is added 102, their personal details are stored into the database. A set of test-specific parameters (i.e. user weight, test start date and time etc.) are also set and stored 106. Alternatively, existing users may be located 108 from the database using search facilities and the test parameters then set or selected. Set-up information is then transferred to the monitor by means of a communications module 104 and a serial link (coupled through the reader to the monitor).
The communications module 104 also controls monitor status management 116, including monitoring the level of charge in the monitor battery and re-setting the monitor microcontroller where required.
In addition, data may be downloaded through the serial link under the control of the communications module from the monitor to the database 100 and viewed using a graphical reports module 110. Graphical reports may be printed 112 or data may be exported 114 directly from the database or via the clipboard from the graphical reports module.
Functionality of the Monitor Contacts
As described above, the monitor comprises two electrical contacts, which can be coupled either to ECG electrodes for heart-beat sensing or to an external device such as the reader for various other purposes.
In total, the two contacts for the ECG electrodes are also used for five other functions: reading data, writing data, charging battery, power management and re-setting the CPU of the microcontroller. This shared functionality of connections allows greatly reduced size and complexity of the electronics of the monitor and provides a simplified user interface.
As shown in
When the monitor contacts are coupled to a PC via a serial interface (202), data can be written by the PC to the monitor. This allows set-up data to be written to the monitor, including user identification and any other desired test parameters.
Similarly, when the monitor contacts are coupled to the serial interface (204), data can be read from the monitor by the PC. This allows stored movement (activity) and cardiac data to be downloaded.
When the monitor contacts are coupled either to a suitable serial interface or to a battery charger (206), the same connections allow the internal re-chargeable battery to be charged.
When the monitor contacts are coupled to a suitable interface, such as the reader described above, battery status can be monitored and managed (208).
Finally, when the monitor contacts are coupled to a suitable interface such as the reader described above, the micro-controller can be re-set (210) following a total discharge or re-charge of the battery.
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|International Classification||A61B5/00, A61B5/0432, A61B5/11, A61B5/04|
|Cooperative Classification||A61B5/6823, A61B5/11, A61B5/1118, A61B5/721, A61B5/04325, A61B5/0006, A61B2560/0412, A61B2562/0219|
|European Classification||A61B5/00B3B, A61B5/11Q, A61B5/72B2B, A61B5/11|
|May 12, 2006||AS||Assignment|
Owner name: CAMBRIDGE NEUROTECHNOLOGY LIMITED, UNITED KINGDOM
Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:UNGLESS, GARY STEVEN;OAKLEY, NIGEL ROBERT;REEL/FRAME:017610/0405
Effective date: 20050816