A SYSTEM FOR DETERMINING THE CONDITION OF A PATIENT'S HEART

Abstract: A system for determining the condition of a patient's heart comprises a plurality of electrodes (10, Fig. 1), for producing cardiac signals and means for converting the cardiac signals into digital form. Data processing means (2, Fig. 2), is programmed to process the digital cardiac signals to determine a plurality of parameters of the patient's heartbeat and determine the condition of the patient's heart using a binary decision tree algorithm. The algorithm has a plurality of decision nodes (102-112) each of which makes a decision based upon the value(s) of a subset of the parameters, the decision criterion of at least one of the said decision nodes being modified according to the value of at least one parameter not of the subset. In addition, at at least one node the respective subset of parameters may be determined according to the value of at least one parameter not of the subset.

Description: A SYSTEM FOR DETERMINING THE CONDITION OF A PATIENT'S HEART This invention relates to a system for determining the condition of a patient's heart. The use of electrocardiographic (ECG) information to detect ischaemic heart disease (IHD) is not new. The standard twelve lead ECG has been used by clinicians for decades for early detection of ischaemic events. The procedure involves the use of 10 appropriately placed electrodes and suitable instrumentation amplifiers to acquire 12 separate ECG signals. These signals are then interpreted either visually or by automated software to identify ischaemic signs. Unfortunately, the area of the torso covered by these 10 electrodes is insufficient to detect ischaemic events from all areas of the heart. This means that the standard twelve lead ECG in many instances fails to provide unequivocal diagnosis. An improved method is the use of unipolar body surface mapping (BSM) which uses a multitude of electrodes (typically between 32 and 200 electrodes) distributed across both the anterior and posterior surface of the torso. With such a system the amount of information being presented to the user is impractical. Furthermore, with large numbers of electrodes, the system requires a significant amount of time to be applied to" the patient. One approach of particular interest is by Lux et al. - "Redundancy reduction for improved display and analysis of Body Surface Potential Maps I spatial compression", Circulation Res, Vol.49, 186-196; where a Karhunen-Loeve method is described which allows a minimal lead set to be recorded and then later expanded mathematically to a more detailed lead set . Investigations concerning the analysis of such BSM' s both directly recorded and expanded mathematically has resulted in various different analysis techniques. All of these however are essentially enhancements to the analysis techniques used to interpret the standard 12 Lead ECG. BSM information is unique in that it provides an overall body surface electrical pattern. This pattern is distinctive and must be analysed in a way which takes advantage of the information contained within it. The use of vectors in ECG interpretation is known, the most famous being Vectorcardiographic systems which are no longer common. All of these vector analysis techniques however concentrate upon the discrete amplitude of the vector drawn between a maximum and a minimum point of electrical potential. One such system is disclosed in European Patent Specification EP-A-0512 719 Bl where a system is described for detecting -coronary artery disease by use of a discriminant function. Here one such parameter which could be analysed is the overall QRST vector. This would be a vector drawn between the maximum and the minimum point of a QRST isointegral BSM. The use of discriminant functions as described above has been for many years arguably the best method for analysing the parameters and features extracted from BSM' s . One notorious problem with a discriminant function approach is the lack of determinisim associated with such a technique. Given any particular case or set of parameters it is very difficult to see what output a given function will provide and given an output it is very difficult to determine how the function arrived at that decision. The use of a more conventional decision tree approach has not been considered appropriate since the problem possesses so many dimensions. Having obtained a decision node (using binary comparison of a given parameter to a preset threshold) which will reliably and accurately detect one given patient condition it is later found that the same decision fails when complicated by other real life conditions. For example, having devised a decision tree which can be useful in detecting acute myocardial infarction occurring in all areas of the myocardium, this same algorithm then fails when there are two areas of the myocardium infarcting at the same time, when the heart is abnormally shaped due for instance to hypertrophy or when the infarct is complicated by a disorder of the conduction system. It is an object of the present invention to provide a means for analysing cardiac information which can provide an improved diagnostic capability with a clearly traceable path to the resulting decision. Accordingly, the invention provides a system for determining the condition of a patient's heart, comprising: (a) a plurality of electrodes each capable of detecting the electrical activity associated with a heartbeat of the patient and producing a corresponding cardiac signal, (b) means for converting the cardiac signals into digital form, and (c) data processing means programmed to: (1) process the digital cardiac signals to determine a plurality of parameters of the patient's heartbeat, (2) determine the condition of the patient's heart using a binary decision tree algorithm, such algorithm having a plurality of decision nodes each of which makes a decision based upon the value (s) of a respective subset of the parameters, the decision criterion of at least one of the said decision nodes being modified according to the value of at least one parameter not of the respective subset, and (3) provide an output indicative of the condition of the patient's heart so determined. An embodiment of the invention will now be described, by way of example, with reference to the accompanying drawings, in which: Fig. 1 is a schematic view of a system according to the embodiment ; Fig. 2 is a block diagram of the storage, processing and display unit of Fig. 1; Fig. 3 is a flowchart of the program stored in the unit of Fig. 2; and Fig. 4 is an example of spatial resultant vectors (static vectors) measured on the body surface with reference to the Wilson Central Terminal (WCT) . Referring now to the drawings, a system according to the invention includes a two-dimensional array 10 of a plurality of ECG electrodes removably attachable to a human patient's torso 15. In Fig. 1 the electrodes are shown attached to the anterior surface of the torso but they can extend substantially fully around the torso. The number of electrodes in the array can typically vary from 20 to 100; in the present case it is assumed there are 96 electrodes. The array 10 also includes right arm (RA) , left arm (LA) , right leg (RL) and left leg (LL) electrodes and may be constructed as described in International Application Number PCT/IB95/01043 (WO96/14015) . Each electrode is capable of detecting the electrical activity associated with the patient's heartbeat and producing a corresponding cardiac signal, and it will be appreciated that each electrode in the array 10, although detecting the same activation of the heartbeat at any given instant, receives the signal with a different voltage having regard to its different spatial position relative to the heart. Since the electrode signal typically has a strength in millivolts it requires amplification prior to further processing. This is achieved in an interface unit 11 which performs front end amplification and analogue-to-digital (A/D) data conversion. The unit 11 may be constructed as described with reference to Fig. 4 of International Application Number PCT/IB97/01631 (W098/26712) . Briefly, however, the total set of 96 signals from the array 10 is divided into six channels of 16 signals per channel. Each channel contains 16 banks of amplification, filtering and sample/hold devices, and a respective 16-to-l analogue signal multiplexer in each channel is used to sequentially switch through each of the 16 signals during each sample/hold period to enable a single channel digital conversion to be used. A microcontroller controls the process of freezing the 16 analogue signals in each channel and during each sample/hold period the analogue multiplexer is selected 16 times with each step sequentially switching one of the 16 signals through to an A/D converter. The sampling frequency is at least 500Hz and preferably at least lkhz. The interface unit 11 therefore produces successive sets of 96 sampled and analog to digital converted signal values, each set having been derived during a respective sample/hold period and therefore constituting a "snapshot" of the electrode voltages at the respective sampling instant. With a sampling frequency of lKHz, 1000 sets of 96 signals will be produced per second. The digitised cardiac signals are passed via a direct digital link 13 to a storage, processing and display unit 12, Fig. 2, comprising a microprocessor 22, a storage device 23, an electronic display device such as a CRT monitor 24, a printer 25 and a user interface such as a keyboard 26. The microprocessor 22 polls each of the channels to transfer sampled data into the storage device 23. In particular, once patient hook-up is satisfactorily completed, the microprocessor 22 stores a pre-selected time frame (typically 5 seconds) of all the channels into the storage device 22. The microprocessor 22 is programmed to process the stored digital data according to the flowchart shown in Fig. 3. First, step 100, the program extracts certain parameters from the digital signals. In the present embodiment these are QRS Integral, ST-T Integral, STOms Isopotential, STδOms Isopotential, STlOOms Isopotential and Vs y mmetry Apart from Vgymmetry these parameters are well known in the art and methods for their extraction are also well known. The parameter Vsymmetry i- s given by: I v Sym etry I = I v Max I ~ I v Min I where V .3X is the maximum STδOms isopotential static vector and V^ n is the minimum ST60ms isopotential static vector, ST60ms isopotential being defined as the isopotential map constructed from all electrode locations at the time instant 60 milliseconds after the Λ J' point in the ECG cycle. These vectors are described in International Application Number PCT/EP98/01446 (WO 98/40010) . Referring to Fig. 4, it can be seen that the V Max vector is the vector drawn from the WCT to the overall maximum location on the body surface and Vm n is the vector drawn from the WCT to the overall minimum location. The length shown in Fig. 4 is for demonstration only and in reality does not reflect the distance between the WCT and the body surface, but rather the magnitude of the electrical signal detected on the body surface. The vectors are referred to as "static" to denote that the vectors are either snapshots or averages of dynamically changing information. Having extracted these parameters, the program implements a binary decision tree algorithm comprising, in this embodiment, six binary decision nodes 102 to 112 which test as follows: Node 102 - Ischaemic/Normal? Node 104 - Normal/Abnormal Conduction? Node 106 - AMI (Acute Myocardial Infarction) with Conduction Disorder? Node 108 - Classic AMI? Node 110 - AMI with LVH (Left Ventricular Hypertrophy)? Node 112 - AMI with ST Depression? As indicated by the dashed line on the RHS of Fig. 3, at each node 102-112 the respective test is made on the basis of the value (s) of one or more of the parameters QRS Integral, ST-T Integral, STOms Isopotential, ST60ms Isopotential and STlOOms Isopotential, the relevant parameter (s) being compared with respective threshold (s) associated with the node to determine the binary outcome, yes (Y) or no (N) , of the node. For example, node 108 tests to see if both STOms Isopotential and STδOms Isopotential are above certain respective thresholds, node 110 tests to see if both STδOms Isopotential and ST-T Integral are below certain respective thresholds, while node 112 tests to see if both STOms Isopotential and STδOms Isopotential are below certain respective thresholds. The nature of the tests made at the nodes 102-112 will be known to those skilled in the art. By following through the logic of the flowchart, it will be seen that, depending upon the decisions at the nodes, the program will output "Normal" (step 120) indicating that the heart is normal, "AMI" (step 122) indicating Acute Myocardial Infarction or "Other" (Step 124) indicating some other abnormality. The output is displayed in human-readable form on the CRT monitor 24, Fig. 2, or may be printed out or otherwise displayed. In order to improve the accuracy of the diagnosis, the static vector symmetry, which changes depending upon the condition of the heart, is used to adaptively control the thresholds used by the decision algorithm. Thus, in the present embodiment and as indicated by the dashed line on the LHS of Fig. 3, the parameter thresholds associated with each of the nodes 108, 110 and 112 are varied according to the magnitude of v symmetry This may be achieved by storing, e.g. in a look-up-table, a number of different thresholds for each parameter ST-T Integral, STOms Isopotential and/or STδOms Isopotential tested by the node and selecting a particular one of the thresholds according to the magnitude of V syMie try In a simple case there will be two thresholds stored for each parameter tested by a node, and one or other will be selected according to whether V symmetr y is itself above or below a certain threshold (i.e. above or below a certain symmetry level) . However, since A/symme t ry is a continuously variable parameter, the nodes could use a function f(V S y mmetr y) to select the parameter threshold. It should be noted that unlike a discriminant function or an artificial neural network (ANN) which are probalistic, the adaptive algorithm described above is deterministic in that for any given case it is easy to determine how the algorithm will perform and also that given an output it is very easy to determine how the algorithm arrived at its decision. The above is given only as an example of the invention, and modifications are possible. For example, the binary decision tree algorithm may be more or less complex than that shown, and may use more or less, and/or different, parameters in its operation. Thus, the V Max and V M -j_ n vectors used to derive V S y mmetr y are only given by way of example since similar vectors usable in the invention can be constructed from QRS isointegral maps, STT isointegral maps, as well as STOms isopotential and STlOOms isopotential maps. Also, although only one parameter, Vs y ^n^^, has been used to adaptively control certain of the decision nodes, in general, and depending on the complexity of the binary decision tree algorithm, more than one parameter can be used to adaptively control the nodes. This may include using more than one parameter to adaptively control an individual node or using different parameters to adaptively control different nodes. In addition, one or more parameters may be used to determine which of the other parameters are used at a decision node. For example, in Fig. 3, node 110 may use the parameters ST-T Integral and STδOms Isopotential if Vsymmetry is below a certain value and use the parameters ST-T Integral and STOms Isopotential if Vsymmetry is above that value. Furthermore, the decision thresholds for the chosen parameters may themselves be varied according to the value of another parameter. For example, in the case above, the value of Vsymmetry is used to select which two out of three parameters to use at decision node 110. The value of the QRS integral may then be used to determine the decision thresholds to apply to those selected parameters . The invention is not limited to the embodiments described herein which may be modified or varied without departing from the scope of the invention.

Claims: CLAIMS 1. A system for determining the condition of a patient's heart, comprising: (a) a plurality of electrodes each capable of detecting the electrical activity associated with a heartbeat of the patient and producing a corresponding cardiac signal, (b) means for converting the cardiac signals into digital form, and (c) data processing means programmed to: (1) process the digital cardiac signals to determine a plurality of parameters of the patient's heartbeat, (2) determine the condition of the patient's heart using a binary decision tree algorithm, such algorithm having a plurality of decision nodes each of which makes a decision based upon the value (s) of a respective subset of the parameters, the decision criterion of at least one of the said decision nodes .being modified according to the value of at least one parameter not of the respective subset, and (3) provide an output indicative of the condition of the patient's heart so determined. 2. A system as claimed in claim 1, wherein at each node the decision is made according to whether or not the value(s) exceed respective threshold (s) , the threshold (s) being varied according to the value of the said at least one parameter not of the subset. 3. A system as claimed in claim 2, wherein the threshold (s) are varied acording to whether or not the value of the said at least one parameter not of the subset exceeds a certain threshold. 4. A system as claimed in claim 1, 2 or 3, wherein at at least one node the respective subset of parameters is determined according to the value of at least one parameter not of the subset. 5. A system as claimed in any preceding Claim, , where at at least one of the nodes the said at least one parameter not of the subset is | Vmax | - | Vmin | where Vmax is the maximum isopotential static vector taken at a predetermined time instant in the ECG cycle and Vmin is the minimum isopotential static vector taken at substantially the same time instant in the ECG cycle. 6. A system as claimed in Claim 5, wherein the time instant is 60 milliseconds after the 'J' point. 7. A system as claimed in Claim 5, wherein the time instant is the 'J' point.

Inventors: ALLEN JAMES, ANDERSON JOHN MCCUNE, ALLEN, JAMES, ANDERSON, JOHN, MCCUNE
Applicants: ALLEN JAMES, ANDERSON JOHN MCCUNE, ALLEN, JAMES, ANDERSON, JOHN, MCCUNE
Application year: 1999
Main classification: A61B5
IPC codes: A61B5