CN1124823C - Standard cardioelectric lead meauring method without wilson network - Google Patents
Standard cardioelectric lead meauring method without wilson network Download PDFInfo
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- CN1124823C CN1124823C CN 95108186 CN95108186A CN1124823C CN 1124823 C CN1124823 C CN 1124823C CN 95108186 CN95108186 CN 95108186 CN 95108186 A CN95108186 A CN 95108186A CN 1124823 C CN1124823 C CN 1124823C
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- 238000000034 method Methods 0.000 title claims abstract description 22
- 239000000872 buffer Substances 0.000 claims abstract description 21
- 210000003414 extremity Anatomy 0.000 claims description 36
- 238000000205 computational method Methods 0.000 claims description 9
- 210000003141 lower extremity Anatomy 0.000 claims description 4
- 210000001364 upper extremity Anatomy 0.000 claims description 2
- 230000000747 cardiac effect Effects 0.000 abstract description 8
- 238000005259 measurement Methods 0.000 abstract description 4
- 238000000691 measurement method Methods 0.000 abstract 2
- 238000003745 diagnosis Methods 0.000 description 4
- 230000003321 amplification Effects 0.000 description 2
- 238000010586 diagram Methods 0.000 description 2
- 238000003199 nucleic acid amplification method Methods 0.000 description 2
- 230000003190 augmentative effect Effects 0.000 description 1
- 238000009795 derivation Methods 0.000 description 1
- 230000000694 effects Effects 0.000 description 1
- 230000005611 electricity Effects 0.000 description 1
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Abstract
The present invention relates to a cardiac electrical measurement method, particularly to a standard cardiac electrical lead measurement method without a Wilson network. The standard cardiac electrical lead obtained by using the method is completely consistent with the traditional principle of Einthoven, Wilson and Goldberger. In a measurement system of N channel lead electrocardiograms, as long as N to 3 channel buffers, and N to 4 channel difference division amplifiers are used. The present invention is characterized in that N to 3 output signals of a human body electrode are outputted to the N to 3 channel buffers; the signals are outputted to the N to 4 channel difference division amplifiers by the N to 3 channel buffers; the signals are transduced by channel A/D transducers of which the number corresponds to that of the difference division amplifiers into analog signals which are sampled and calculated by a computer.
Description
Technical field
The present invention relates to a kind of electrocardio measuring method, the standard electrocardiographic lead measuring method of particularly a kind of no Weir inferior (Wilson) network.Adopt standard electrocardiographic lead that this method measures and traditional Einthoven, Wilson and Goldberger theory are on all four.
Background technology
Following problem can appear during the Wilson network measure electrocardiosignal that adopted in prior art:
1, owing to there is the Wilson network resistor, CMRR can produce bigger restriction to the electrocardio amplifying circuit;
2, want to obtain simultaneously N electrocardiographic recorder, just must use N ecg amplifier at least.
And the object of the present invention is to provide a kind of new electrocardio measuring method, this method meets Einthoven in theory, Wilson and Goldberger electrocardio measuring method are used to measure electrocardiosignal with computer technology, bio electricity amplifying technique and the combination of cardiac diagnosis lead principle.
The present invention proposes the pattern of the computational methods of finishing described measuring method and a kind of new amplifier.
Summary of the invention
A kind of standard electrocardiographic lead measuring method of not having the inferior network of Weir is characterized in that: in a standard N lead electrocardiogram measuring system, comprise N-3 body electrode, wherein 3 is limb electrode L, R, LF, and all the other are precordial electrode C
n, n=1 ..., N-6; Wherein reference electrode M is one among L, R, the LF; Use N-3 buffer and N-4 difference amplifier;
A. the output signal with N-3 above-mentioned body electrode is passed to respectively in the above-mentioned N-3 buffer;
B. be passed to one of above-mentioned N-4 amplifier input respectively by each signal except that reference electrode M in described N-3 the buffer output signal; The buffer output signal of reference electrode M is passed to another input of each amplifier, constitutes each electrode channel except that reference electrode M, and respectively this channel amplifier amplifies back output with signal;
C. will be converted to digital signal through each amplifier amplifying signal by having, and calculate by listed formula in the following d point with the corresponding A/D converter of described difference amplifier number, thus the electrocardiogram of acquisition standard lead number;
D. computational methods are:
If the unipolar lead of each electrode is V
L, V
R, V
LF, V
1... V
n, the unipolar lead V of reference electrode
M, they are these electrode corresponding output signal respectively,
Definition " reference power station D " is
((V
L+V
R+V
LF)÷3)-V
M，
Standard electrocardiographic lead:
I is the output of first non-benchmark limb electrode to bipolar lead=first non-benchmark limb electrode channel amplifier of benchmark limb electrode;
II is the output of second non-benchmark limb electrode to bipolar lead=second a non-benchmark limb electrode channel amplifier of benchmark limb electrode;
III is the bipolar lead=II-I between first and second non-benchmark limb electrode;
V
M=-D; Its pressurization unipolar lead is 15 * (D);
First non-benchmark limb electrode unipolar lead=I-D; Its unipolar lead 15 * (I-D) that pressurizes;
Second non-benchmark limb electrode unipolar lead=II-D; Its unipolar lead 15 * (II-D) that pressurizes;
Each front unipolar lead V
n,
V
n＝(V
n-V
M)-D
(V
n-V
M) be amplifier output corresponding to n precordial electrode passage, n=1 ..., N-6.
The derivation of each calculating formula will be described in detail below.
The advantage of the standard electrocardiographic lead method of no Wilson network of the present invention is the no Wilson resistor networks of whole electrocardio inputs, and amplifier can be designed to theoretic symmetric mode; When electrocardiogram was led in measurement more, used amplifier channel number lacked than traditional approach; Found the computational methods that realize this cardiac diagnosis lead measuring technique, set up by " reference power station " and realized the new approach that usefulness " central station " is in the past measured, and a kind of amplifier pattern of the present invention that is fit to is provided.
All in the present invention electrocardio output contents all are ambipolar, and no Wilson resistor network, thereby amplifier can be designed to theoretic symmetry makes the design of amplifier circuit more can satisfy the requirement of high cmrr.Can use than the tradition mode amplifier channel number still less that leads, computational methods proposed by the invention, the N lead electrocardiogram that is needed N road amplifier just can obtain in the past.Though electrocardiogram content of the present invention all is ambipolar, through method provided by the present invention, not only can obtain required bipolar lead electrocardiogram, more can obtain the one pole electrocardiogram that must just can finish with the Wilson network over.All unipolar lead electrocardios that the present invention obtained are all realized by " reference power station " this new way, yet it meets Einthoven fully on principle, the theory that Wilson and Goldberger proposed, thereby its complete and existing ECG Technique compatibility, need not to set up new theoretical standard.
Description of drawings
Cardiac diagnosis lead amplification mode sketch map in Fig. 1 prior art.
Fig. 2 is the composition diagram of N lead electrocardiogram measuring system of the present invention.
Fig. 3 is the system diagram that example electrocardiogram that 12 (N=12) lead writes down simultaneously.
Fig. 4 is the present invention 12 connecting mode between the buffer stage and ecg amplifier in the example that leads.
The specific embodiment
As shown in Figure 1, in prior art, carry out the electrocardio measurement that N leads, in the cardiac diagnosis lead amplification mode, use the Wilson network, and use N amplifier and N buffer, like this, not only the parts of Shi Yonging are many, and because the existence of Wilson network resistor, electrocardio amplifying circuit CMRR produces considerable restraint; To obtain the N electrocardiographic recording that leads simultaneously, just must use to be no less than N amplifier.
And in N lead electrocardiogram measuring system of the present invention shown in Figure 2, as long as use N-3 buffer and N-4 difference amplifier, and no longer need the Wilson network, and make the mode of leading more easy like this, also saved many parts, in the standard lead example electrocardiogram while recording system when N equals 12 shown in Figure 3, use 9 body electrodes, 9 road buffer stages, 8 road ECG difference amplifiers, by computer acquisition, calculate output 12 lead electrocardiogram through A/D converter then.This example is established one in addition with reference to the body electrode, without buffer, connects whole common points of each amplifier, constitutes the symmetry input mode of amplifier, and this can clearly see from Fig. 4.
The sketch map of connecting mode between N-3 road buffer stage when in Fig. 4, having represented N=12 and the N-4 road ecg amplifier.
Below in conjunction with Fig. 3,4, be that example is introduced computational methods of the present invention with N=12.
12 lead measure in totally 12 of standard leads.
If employed body electrode has limb electrode L, R, LF, precordial electrode C
1C
6, with C
nExpression, wherein n=1 ... 6, nine altogether, other establishes a reference electrode RF.Wherein nine electrodes insert nine (being N-3) individual buffers respectively, reference electrode is M, this example is a benchmark with limb electrode R, M=R, the output of buffer connects each negative terminal of eight (being N-4) difference amplifiers, the output of the buffer of each electrode of other except that R connects the anode of these eight amplifiers respectively, and the output of each amplifier will be electrocardio measurement result or the content that is used for calculating, and their meaning illustrates during below in conjunction with the narration computational methods.RF electrode in this example directly connects the common port of each amplifier.
Above L, R, LF can be located at the electrode on left and right upper limb and a left side or the right lower extremity respectively, and RF can be provided in a side of the electrode on the right side or the left lower extremity.C
1C
6Be six precordial electrodes.
Reference electrode M as mentioned above, is chosen for R in this example, M=R, and situation shown in Figure 4 that Here it is, in fact, also can get L or LF is reference electrode, M=L or LF at that time, it is self-evident.
Under this routine situation, 12 standard leads are counted
I.I be first non-benchmark limb electrode L to the R electrode, i.e. reference electrode in this example, bipolar lead=V
L-V
R,
Ii.II is the bipolar lead=V of second non-benchmark limb electrode LF to the R electrode
LF-V
R,
Iii.III is first, the bipolar lead=V between second non-benchmark limb electrode
LF-V
L=
II-I，
Iv. the R electrode that pressurizes is the benchmark limb electrode in this example, unipolar lead α V
R, press the Godberger principle, α=1.5,
V. the L electrode that pressurizes is first non-benchmark limb electrode in this example, unipolar lead α V
L,
Vi. the LF electrode that pressurizes is second non-benchmark limb electrode in this example, unipolar lead α V
LF, V wherein
R, V
L, V
LFBe unipolar lead corresponding to R, L, LF electrode.With V
MBe the unipolar lead of reference electrode M,
Six precordial electrode unipolar leads of vii-xii V
1V
6
At first set " reference power station D ",
When getting R and be reference electrode, V
M=V
R, then
Nature, when L or LF are reference electrode, M=L or LF, this moment, all above parameters that relate to benchmark in various were replaced by the associated arguments of L or LF.
From (1) formula of reference power station D as seen, with the central station of Wilson network many " a V
R".
Thus, I=V
L-V
R=first non-benchmark limb electrode is to the amplifier output of bipolar lead=first non-benchmark limb electrode passage of benchmark limb electrode ... (2)
II=V
LF-V
R=the second non-benchmark limb electrode exported the amplifier of bipolar lead=second a non-benchmark limb electrode passage of benchmark limb electrode ... (3)
III=V
L-V
L=II-I ... (4) calculate by (2) (1).
Because press the definition of Einthoven triangle
Should be zero, so
V
RCan take from D, V
R=-D.
Can calculate by I and D.
Can calculate by II and D.
Augmented unipolar limb lead is thus
αV
R＝1.5V
R ……(8)
αV
L＝1.5V
L ……(9)
αV
F＝1.5V
F ……(10)
The precordial electrode unipolar lead
＝(V
n-V
M)-D ……(11)
N=1 ... 6 can be by C
1C
6Amplifier output (the V of each passage
n-V
R) and D calculating.
So far, with (2)-(4), (8)-(11) just can obtain whole 12 and lead.
When M=L or LF, the calculating principle of each standard electrocardiographic lead is consistent with the calculating principle of above-mentioned expression.
Thus, it all is ambipolar using the resulting whole cardiac electrical results of standard electrocardiographic lead measuring method of no Wilson network of the present invention, no Wilson resistor network, thereby amplifier can be designed to symmetric mode in theory, makes the design of amplifier circuit more can satisfy the requirement of high cmrr; The number of amplifier that lacks than traditional approach can be used,, the N lead electrocardiogram that needs N road amplifier to obtain can be obtained over by computational methods proposed by the invention; And, though the electrocardio output content that the present invention obtains all is ambipolar,, can obtain required unipolar lead electrocardiogram through computational methods of the present invention; Using the present invention can make all unipolar lead electrocardios of acquisition all is to realize by " reference power station " this approach, in theory with Einthoven, the theory that Wilson and Goldberger proposed meets fully, thereby fully can with existing ECG Technique compatibility, need not to set up new theory and standard.Certainly should be noted that the buffer stage that between amplifier of the present invention and human body, needs to insert number of amplifier many 1, to guarantee the effect of ecg amplifier CMRR value in the practical work process.
More than just schematically the present invention will be described, and those skilled in the art can make various improvement on the basis of the above description, and do not deviate from theme of the present invention.
Claims (3)
1. standard electrocardiographic lead measuring method of not having the inferior network of Weir, it is characterized in that: in a standard N lead electrocardiogram measuring system, comprise N-3 body electrode, wherein 3 is limb electrode L, R, LF, and all the other are precordial electrode C
n, n=1 ..., N-6; Wherein reference electrode M is one among L, R, the LF; Use N-3 buffer and N-4 difference amplifier;
A. the output signal with N-3 above-mentioned body electrode is passed to respectively in the above-mentioned N-3 buffer;
B. be passed to one of above-mentioned N-4 amplifier input respectively by each signal except that reference electrode M in described N-3 the buffer output signal; The buffer output signal of reference electrode M is passed to another input of each amplifier, constitutes each electrode channel except that reference electrode M, and respectively this channel amplifier amplifies back output with signal;
C. will be converted to digital signal through each amplifier amplifying signal by having, and calculate by listed formula in the following d point with the corresponding A/D converter of described difference amplifier number, thus the electrocardiogram of acquisition standard lead number;
D. computational methods are:
If the unipolar lead of each electrode is V
L, V
R, V
LF, V
1... V
n, the unipolar lead V of reference electrode
M, they are these electrode corresponding output signal respectively,
Definition " reference power station D " is
((V
L+V
R+V
LF)÷3)-V
M，
Standard electrocardiographic lead:
I is the output of first non-benchmark limb electrode to bipolar lead=first non-benchmark limb electrode channel amplifier of benchmark limb electrode;
II is the output of second non-benchmark limb electrode to bipolar lead=second a non-benchmark limb electrode channel amplifier of benchmark limb electrode;
III is the bipolar lead=II-I between first and second non-benchmark limb electrode;
V
M=-D; Its pressurization unipolar lead is 15 * (D);
First non-benchmark limb electrode unipolar lead=I-D; Its unipolar lead 15 * (I-D) that pressurizes;
Second non-benchmark limb electrode unipolar lead=II-D; Its unipolar lead 15 * (II-D) that pressurizes;
Each front unipolar lead V
n,
V
n＝(V
n-V
M)-D
(V
n-V
M) be amplifier output corresponding to n precordial electrode passage, n=1 ..., N-6.
2. measuring method according to claim 1 is characterized in that: also be provided with the RF with reference to the body electrode, directly be connected on the common point of whole amplifiers.
3. measuring method according to claim 2 is characterized in that: described limb electrode L, R, LF are provided in a side of the electrode of left and right upper limb and a left side or right lower extremity, and described is the electrode that correspondingly is located at the right side or left lower extremity with reference to body electrode RF.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN 95108186 CN1124823C (en) | 1995-07-28 | 1995-07-28 | Standard cardioelectric lead meauring method without wilson network |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN 95108186 CN1124823C (en) | 1995-07-28 | 1995-07-28 | Standard cardioelectric lead meauring method without wilson network |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CN1141763A CN1141763A (en) | 1997-02-05 |
| CN1124823C true CN1124823C (en) | 2003-10-22 |
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ID=5076664
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| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN 95108186 Expired - Fee Related CN1124823C (en) | 1995-07-28 | 1995-07-28 | Standard cardioelectric lead meauring method without wilson network |
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| Country | Link |
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Families Citing this family (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| WO2012160550A1 (en) * | 2011-05-23 | 2012-11-29 | Shl Telemedicine International Ltd. | An electrocardiographic monitoring system and method |
| US9167981B2 (en) * | 2013-10-08 | 2015-10-27 | Mediatek Inc. | ECG device, ECG lead signal generating circuit, and related method |
| CN106388808B (en) * | 2015-06-26 | 2021-05-25 | 席剑 | Novel multichannel electrocardiogram acquisition scheme |
| CN106691432B (en) * | 2016-10-19 | 2023-04-21 | 深圳市杰纳瑞医疗仪器股份有限公司 | Induction type electrocardio measuring method and device |
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1995
- 1995-07-28 CN CN 95108186 patent/CN1124823C/en not_active Expired - Fee Related
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| Publication number | Publication date |
|---|---|
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