CN1034665A - Automatic and woundless cardiac-function measuring instrument - Google Patents
Automatic and woundless cardiac-function measuring instrument Download PDFInfo
- Publication number
- CN1034665A CN1034665A CN 88100018 CN88100018A CN1034665A CN 1034665 A CN1034665 A CN 1034665A CN 88100018 CN88100018 CN 88100018 CN 88100018 A CN88100018 A CN 88100018A CN 1034665 A CN1034665 A CN 1034665A
- Authority
- CN
- China
- Prior art keywords
- signal
- key
- cardiac
- woundless
- display
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Pending
Links
- 230000004217 heart function Effects 0.000 title claims abstract description 30
- 230000000747 cardiac effect Effects 0.000 claims abstract description 23
- 238000006243 chemical reaction Methods 0.000 claims abstract description 4
- 238000000034 method Methods 0.000 claims description 13
- 230000006870 function Effects 0.000 claims description 8
- 238000005259 measurement Methods 0.000 claims description 8
- 238000004458 analytical method Methods 0.000 claims description 5
- 238000012545 processing Methods 0.000 claims description 4
- 230000003321 amplification Effects 0.000 claims description 3
- 238000003199 nucleic acid amplification method Methods 0.000 claims description 3
- 230000008569 process Effects 0.000 claims description 2
- 238000004364 calculation method Methods 0.000 claims 1
- 238000004088 simulation Methods 0.000 claims 1
- 238000005070 sampling Methods 0.000 abstract description 2
- 238000007689 inspection Methods 0.000 description 10
- 230000036541 health Effects 0.000 description 6
- 230000002861 ventricular Effects 0.000 description 6
- 239000008280 blood Substances 0.000 description 5
- 210000004369 blood Anatomy 0.000 description 5
- 210000004204 blood vessel Anatomy 0.000 description 5
- 238000010586 diagram Methods 0.000 description 5
- 210000002417 xiphoid bone Anatomy 0.000 description 5
- 238000001514 detection method Methods 0.000 description 4
- 230000036581 peripheral resistance Effects 0.000 description 3
- 101000649996 Homo sapiens Postacrosomal sheath WW domain-binding protein Proteins 0.000 description 2
- 102100028278 Postacrosomal sheath WW domain-binding protein Human genes 0.000 description 2
- 238000010521 absorption reaction Methods 0.000 description 2
- 238000010009 beating Methods 0.000 description 2
- 210000000038 chest Anatomy 0.000 description 2
- 230000035487 diastolic blood pressure Effects 0.000 description 2
- 238000005516 engineering process Methods 0.000 description 2
- 238000002489 impedance cardiography Methods 0.000 description 2
- 210000003141 lower extremity Anatomy 0.000 description 2
- 238000012544 monitoring process Methods 0.000 description 2
- 0 CC1**(C)CC1 Chemical compound CC1**(C)CC1 0.000 description 1
- 208000032843 Hemorrhage Diseases 0.000 description 1
- 210000000709 aorta Anatomy 0.000 description 1
- 230000004872 arterial blood pressure Effects 0.000 description 1
- 230000006399 behavior Effects 0.000 description 1
- 230000008901 benefit Effects 0.000 description 1
- 230000017531 blood circulation Effects 0.000 description 1
- 230000037396 body weight Effects 0.000 description 1
- 230000008859 change Effects 0.000 description 1
- 239000003795 chemical substances by application Substances 0.000 description 1
- 229940079593 drug Drugs 0.000 description 1
- 239000003814 drug Substances 0.000 description 1
- 230000002526 effect on cardiovascular system Effects 0.000 description 1
- 230000005611 electricity Effects 0.000 description 1
- 238000001125 extrusion Methods 0.000 description 1
- 238000005534 hematocrit Methods 0.000 description 1
- 230000000004 hemodynamic effect Effects 0.000 description 1
- 238000002847 impedance measurement Methods 0.000 description 1
- 230000008676 import Effects 0.000 description 1
- 208000015181 infectious disease Diseases 0.000 description 1
- 210000005240 left ventricle Anatomy 0.000 description 1
- 239000002184 metal Substances 0.000 description 1
- 238000012806 monitoring device Methods 0.000 description 1
- 230000002107 myocardial effect Effects 0.000 description 1
- 230000036284 oxygen consumption Effects 0.000 description 1
- 230000010412 perfusion Effects 0.000 description 1
- 239000004033 plastic Substances 0.000 description 1
- 229920003023 plastic Polymers 0.000 description 1
- 230000002685 pulmonary effect Effects 0.000 description 1
- 238000011160 research Methods 0.000 description 1
- 230000035488 systolic blood pressure Effects 0.000 description 1
Images
Landscapes
- Measurement And Recording Of Electrical Phenomena And Electrical Characteristics Of The Living Body (AREA)
Abstract
A kind of automatic and woundless cardiac-function measuring instrument by signals collecting amplifier section and conversion of signals, is handled and is calculated and the input composition.Utilize microcomputer that electrocardiosignal, cardiechema signals and the cardiac impedance signal of human body are detected automatically and handle, this system's capacity of resisting disturbance by force, is not subjected to breathe to be influenced, the time fixed point is accurate, operating rate is fast, good reproducibility, with about two minutes times just can finish auto-scaling, decide baseline, sampling, calculate and print core signal ECG, three curves such as cardiechema signals PCG and cardiac impedance signal IRG and print the report that portion has 32 heart function parameters.Native system is simple to operate, can be used for units such as hospital, institute, factory.
Description
Native system is one and utilizes microcomputer technology to realize the instrument that cardiac function noninvasive detects automatically.This system can be used for the cardiac function of cardiovascular patient, normal person (as normal person's health check-up, select athletes and spaceman detection etc.) is carried out complete detection, also can change according to the cardiac function before and after patient's medication, with the research pharmaceutical properties.So native system can be used for units such as hospital, medical college, biological study institute, institute of materia medica, sports departments and school, office, army.
The cardiac function detector of present domestic use is divided into two kinds, and a kind of is that the wound method is arranged, and another kind is the noinvasive method.The wound method is arranged: as the float catheter method many shortcomings are arranged, its complicated operation, expense costliness are brought a lot of miseries to patient, the more important thing is may cause that venous blood is fastened, infection, hemorrhage or complication etc.The employed cardiac function detector of noinvasive method generally adopts impedance cardiography method, but all parameter is by manual measurement and calculating, speed is very slow, a person under inspection is made a examining report list need spend 1 to 2 hour time, and accuracy and repeated relatively poor, thereby be difficult to clinical practice." noinvasive hemodynamic cardiac monitoring instrument " that precious beautiful (BOMed) company of the U.S. produces also is to adopt impedance cardiography method, but this device only shows 6 cardiac functional parameters, and only as monitoring usefulness, 1.3 ten thousand dollars of prices cost an arm and a leg.The domestic like product of not seeing as yet.
Problem in view of prior art exists the present invention seeks to develop a kind of automatic non-invasive cardiac function detector.Adopt microcomputer that signal is detected automatically and handles, not being subjected to breathe influences, operating rate is fast, only just can finish calibration to signal automatically, decides baseline, sampling, calculates and print that portion has three figures (electrocardiogram ECG, cardiac impedance signal IRG and cardiechema signals figure PCG) and report, doctor and the patient of 32 cardiac function detected parameters can see the result at that time with about two minutes time.
Provided by the present invention is a kind of microcomputer impedance method cardiac function detector.This system is made up of hardware and software.Hardware has two parts as shown in Figure 1, and first is the collection amplifier section of signal; Second portion is conversion of signals, handles and calculate and input and output.First comprises high-frequency current signal source (1), the measurement of human body basal impedance, display (2), IRG(cardiac impedance signal) amplifier (3), PCG(cardiechema signals) amplifier (5).Second portion comprises A/D converter (6), running LED (7), microcomputer main frame (8), keyboard (9), mode selection switch (10), display (11), printer (12) etc., all hardware all pack into be made of metal or the cabinet (13) of plastics extrusion modling in, printer (12) is installed on the top panel of cabinet (13) as shown in Figure 2, stop opening pass (19), stop beating display lamp (20), on and off switch (21), on and off switch display lamp (22), keyboard (9), display (11), running LED (7) etc.The measurement of human body basal impedance, display (1), ZO knob (18), PCG jack (15), ECG jack (14), IRG socket (16), GAIN knob (17) and mode selection switch (10) are installed on the front panel of cabinet (13).
It is core signal ECG, cardiechema signals PCG and cardiac impedance signal IRG that native system will detect three kinds of signals.Detection method is as follows: first, thought-read signal of telecommunication ECG, three electrodes of electrocardioelectrode cable one end are adsorbed on chest, right arm and the left lower extremity of human body respectively, and record core signal ECG from chest, right arm and left lower extremity electrode, the other end of cable is inserted in the front panel ECG jack (14) of cabinet (13), connection circuit ECG amplifier in parallel (4).Second, thought-read tone signal PCG, cardiac sound transducer with hear sounds electrode cable one end, be adsorbed between third and fourth rib of presternum left border of human body and by recording cardiechema signals PCG on this electrode, the other end of cable is inserted in the front panel PCG jack (15) of cabinet (13), connection circuit PCG amplifier in parallel (5).The 3rd, the method of thought-read impedance signal IRG and basal impedance ZO value is to have an end of the cable of 4 electrodes, wherein two electrodes are bundled in the neck root of human body respectively, two electrodes in addition, be bundled in the xiphoid-process lower edge position of human body respectively, (seeing Fig. 3 for details) is added to the top electrode of person under inspection's neck root top electrode and xiphoid-process lower edge by the constant current signal of high-frequency constant current source (1) generation 50KHZ, measure basal impedance ZO value, with cardiac impedance signal IRG, the other end of cable is inserted in the front panel I RG socket (16) of cabinet (13), and connects circuit high-frequency current signal source (1) respectively by socket (16), the human body basal impedance is measured, display (2) and IRG amplifier (3).When person under inspection (X) is adsorbed each electrode on one's body on request, after tying up, can switch on this moment, by the health check-up parameter of keying in person under inspection (X) on this system's keyboard, key entry finishes, system enters and decides baseline automatically, the simultaneously corresponding display lamp of calibration is lighted automatically, to core signal ECG, cardiechema signals PCG and cardiac impedance signal IRG gather automatically, gathering the signal that comes is analogue signal further amplification of the amplifier on Fig. 5 (26) more respectively, deliver in the A/D converter (6), aanalogvoltage is converted to digital quantity, delivers to then in Fig. 6 microcomputer main frame (8).Trigger among Fig. 5 (27) 74LS76 becomes the clock pulses of 500KHZ to be used for A/D converter (6) in order to the clock with 2MHZ.Introduce to satisfying the selected chip that requires of native system speed, precision and memory size in conjunction with Fig. 6.CPU Xuan Strew 80CPU, native system require read-only memory ROM(32) capacity be 16KB so select 27128 for use, the capacity that requires random memory ram (31) is 8KB so select 6264 for use.But in order to adapt to function expansion from now on,, diffused into the 32KB that only drawn among 64KB(Fig. 6) so internal memory leaves expansion leeway.The sheet choosing of memory relies on Y0, Y1 etc., by decoder (29) 74LS138(1) produce.In order to reach the requirement of input and output, use 3/8 decoder (30) 74LS138(2 again) and Fig. 5 in decoder (28) 74LS138(3) two chip blocks.By decoder (30) 74LS138(2) produce the PS1 signal as CTC(34) chip selection signal, the PS6 signal that produces is added to decoder (28) 74LS138(3 among Fig. 5) the C end through deciphering after, produce the 98H chip selection signal in order to gating running LED driver (37) 74LS374, and then driving running LED (7) by the Y0 end.System's pairing status indicator lamp in running is lighted.
Introduce keyboard (9) and realize the circuit of its function in conjunction with Fig. 2 and Fig. 7.What native system was selected for use is the keyboard with 32 keys, reality 25 keys.10 0-9 of numeral keys are wherein arranged.Have 9 command keys to have: restart key (START), down key (NEXT), go up key (LAST), C key (removings), from the beginning check key, measure key, beat again the chart key, beat again and show key, reset key etc.2 sex key A keys (woman), B key (man) are arranged.There are 4 spare keys to be provided with the new function of back expansion.Keyboard circuit is one group of row, column Closing Switch circuit shown in Figure 7, and 6 row 5 row are arranged, and the signal of being sent here by data/address bus D5-D0 is delivered to the line scanning of respectively advancing after word bit latch (36) 74LS273 and not gate are anti-phase.Article 5, the alignment resistance that respectively is connected in series 100K connects+5V, is not having line scanning or line scanning is being arranged but when not having key and pressing; Article 5, alignment is high potential.Simultaneously have key to press on this row as line scanning when electronegative potential (be the behavior), then the alignment at place also becomes electronegative potential.Column signal is delivered to microcomputer main frame (8) by triple gate (38) 74LS244.Which key what just can determine to press according to row signal and column signal is, and is shown by display (11) and to export.Display (11) is made up of six common cathode seven segment numerical display tubes.The font code that he shows is through data/address bus D6-D0, by font latch (35) 74LS273, latch after audion FS9012 amplifies, be sent on seven sections of each charactron, meanwhile the word bit code is through D5-D0, through word bit latch (36) 74LS273.Latch, be sent to after anti-phase the negative electrode of six charactrons, the control charactron shows.
The software that the present invention uses is write as with the Z80 assembler language.It is among the ROM27128 at the read-only memory (33) of 16K that program is finished after fixing.Below in conjunction with software flow pattern Fig. 8 software used in the present invention is once described: after the energising of this automatic and woundless cardiac-function measuring instrument, system automatically performs initialize routine and removes automatically, resets.Enter display routine then, when key is pressed, system enters the keyboard analysis programme, key assignments is carried out discriminatory analysis, after key entry finishes, system automatically performs the handling procedure section and carries out deciding automatically baseline, calibration and control corresponding Status Flag, carries out data acquisition, processing, analysis, calculating etc. automatically.After this section program executed, system automatically performed the printout program, printout ECG, PCG, three curve waveform figure of IRG and 32 heart function parameters.System carries out automatic display routine and carries out keyboard scan simultaneously behind the end of output, and system is recycled to corresponding block again when key is pressed.
Cardiac function institute detected parameters is described further to utilizing microcomputer technology below in conjunction with Fig. 4: number in the figure is: electrocardiogram ECG curve (23), cardiac impedance differential map IRG curve (24), sound figure PCG curve (25).The cardiac impedance signal is taken out through amplifying circuit amplification and peaker differential by human body and forms heart impedance differential signal, heart impedance differential signal can reflect that the variation of blood vessel instantaneous delivery is a velocity of blood flow, and after one's own heart impedance differential map (24) C point is that on behalf of blood vessel maximum instantaneous flow, A2, dz/dt|max represent the maximum retraction rate of blood vessel, O point to represent the maximum further expansion speed of blood vessel, S point to represent blood vessel retraction rate again.Therefore go up the amplitude and the interval of certain characteristics point according to cardiac flow cardiac impedance differential map (24), just can reflect heart blood hydromechanics state, also can judge cardiac function simultaneously.Utilize electrocardiogram ECG curve (23) and sound figure PCG curve (25) on cardiac impedance differential map IRG curve, to carry out the correct time fixed point to each characteristic point.For example C point, A2 point and O each interval of ordering is respectively Q-BO(or B15), BO(or B15)-A2(or X), A2(or X)-O and R-R.Above data all can be measured automatically by native system.Then can calculate other heart function parameter again according to input person under inspection's experience parameter.Below native system can be calculated 32 heart function parameters and the numeral expression formula thereof that print is listed as follows:
1.AMP C: impedance differential map amplitude, IRG maximum (expansion wave amplitude).
2.AMP O: O wave amplitude (further expansion wave amplitude).
3.AMP A: A wave amplitude (retraction wave amplitude).
4.Q-B。The Q ripple starting point of (or B15): ECG is to BO(or B15) blanking time, be left pre-ejection period.
5.Q-Z: the left chamber function index.Be that Q ripple starting point arrives the blanking time that impedance differential map maximum C is ordered.
6.B0(or B15)-and A2(or X): be the left ventricular ejection phase.
7.A2(or X)-0: be the left ventricle isovolumic relaxation phase.
8.R-R: be cardiac cycle the blanking time that is adjacent two R ripples.
9.HR: heart rate
Mathematical formulae: HR=60000/(R-R) inferior/min
10.MAP: mean arterial pressure.
Mathematical formulae: MAP=DP+SP mmHg
11.BSA: body surface area.
Mathematical formulae: BSA=0.0128Wkg+0.0061Hcm-0.153M
2
12.rho: blood resistivity.
13.SV: the heart stroke volume
Mathematical formulae: SV=ρ (1/z) dz/dt|maxT mL/B
In the formula: ρ: the resistivity of blood is about 135 Ω-cm;
L: the distance between measurement electrode (absorption human body neck root bottom electrode and xiphoid-process lower edge top electrode) is about 25cm;
ZO: measure the impedance between electricity level (absorption human body neck root bottom electrode and xiphoid-process top electrode), normal value is 22-35 Ω;
Dz/dt|max: the maximum of painstaking effort stream differential impedance figure;
T: be left ventricular ejection time promptly by B0 or B15 blanking time to A2,
Normal value is about 280 to 300ms.
14.CO: minute output of heart
Mathematical formulae: CO=SVHR L/min
15.SVI: the index of fighting
Mathematical formulae: SVI=SV/BSA L/min/M
2
16.CI: cardiac index
Mathematical formulae: CI=CO/BSA mL/B/M
2
17.HI: the cardiac systolic function index
Mathematical formulae: HI=dz/dt|man ÷ (Q-Z) Ω/S
2
18.PEP/LVET: left pre-ejection period/left ventricular ejection phase
Mathematical formulae: PEP/LVET=(Q-B15)/(B15-A2)
19.EF: ejection fraction
Mathematical formulae: EF=1.125-1.25(PEP/LVET)
20.O/C: further expansion wave amplitude/expansion wave amplitude.
21.A/C: retraction wave amplitude/expansion wave amplitude.
22.Q-A2(or X): left pre-ejection period with penetrate blood phase sum.
23.TPR: total peripheral resistance
Mathematical formulae: TPR=MAP ÷ CO * 80dyneseccm
-5
24.AC: the aorta compliance
Mathematical formulae: AC=SV ÷ (SP-DP) mL/mmHg
25.PAWP: pulmonary capillary wedge pressure
Mathematical formulae: PAWP=18.8(Q-B15)/(A2-O)+1.8 mmHg
26.LVEDP: ventricular end diastolic pressure
Mathematical formulae: LVEDP=21.6(Q-B15)/(A2-O)+1.1 mmHg
27.SW: the left ventricular work of whenever fighting
Mathematical formulae: SW=SV * MAP * 13.6 * 1000 kgm/B
28.CW: the per minute left ventricular work
Mathematical formulae: CW=CO * MAP kgm/min
29.SWI: stroke work index
Mathematical formulae: SWI=SW ÷ BSA kgm/B/M
2
30.CWI: core power index
Mathematical formulae: CWI=CW ÷ BSA kgm/min/M
2
31.HS: myocardial oxygen consumption
Mathematical formulae: HS=HRSBP
32.CAPP: coronary perfusion pressure
Mathematical formulae: CAPP=DBP-PAWP mmHg
The advantage of this automatic and woundless cardiac-function measuring instrument be reliable operation, stable performance, automaticity height, speed fast, can accurately react heart function state, not be subjected to breathe and influence, its good reproducibility especially.And easy to operate, be easy to learn and use, volume is little, cost is low, be convenient to clinical expansion uses, not only can use at large hospital, and in can be generalized to, infirmary uses.Have only large hospital just to have the ability to purchase expensive import cardiac monitoring device at present, and most of parameter is by artificial calculating.Native system is carried out the cardiac function detection for extensive popularization and is had bigger impetus.
The present invention has following accompanying drawing
Fig. 1. functional-block diagram
Fig. 2. the automatic and woundless cardiac-function measuring instrument outline drawing
Fig. 3. person under inspection's instrumentation plan
Fig. 4 .ECG, IRG, three curve charts of PCG
Fig. 5. circuit diagram
Fig. 6. circuit diagram
Fig. 7. circuit diagram
Fig. 8. program flow diagram.
Number in the figure is as follows:
1. high-frequency current signal source
2. human body basal impedance measurement, display
3.IRG amplifier
4.ECG amplifier
5.PCG amplifier
6.A/D transducer (ADC 0809)
7. running LED
8. microcomputer main frame (Z8CPU)
9. keyboard
10. mode selection switch
11. display (charactron)
12. printer
13. cabinet
14.ECG jack
15.PCG jack
16.IEG socket
17.GAIN knob
18.Zo knob
19. stop opening the pass
20. stop beating display lamp
21. on and off switch
22. power supply indicator
23.ECG(electrocardiosignal) curve
24.IRG(curve cardiac impedance)
25.PCG(curve cardiechema signals)
26. amplifier
27. trigger (74LS76)
28. decoder (74LS138(3))
29. decoder (74LS138(1))
30. decoder (74LS138(2))
31. random memory ram (6264)
32. read-only memory ROM(2764)
33. read-only memory ROM(27128)
34.CTC
35. font latch (74LS273)
36. word bit latch (74LS273)
37. running LED driver (74LS374)
38. triple gate (74LS244)
X. person under inspection
Work process of the present invention and concrete enforcement are described below in conjunction with the accompanying drawings:
After the energized, show IRCg, illustrate that native system is working properly, be ready.Click " following key " (NEXT),, key in content corresponding and promptly key in person under inspection's health check-up parameter (requiring the content english abbreviation letter representation of key entry) according to prompting character.
SE: sex.The man keys in A; The woman keys in B.
AG: at the age, key in 1 to 3 figure place.
Ht: height (cm), key in 3 figure places.
Ut: body weight (kg), key in 2 figure places.
Hp: systolic pressure (mmHg), key in 2 to 3 figure places.
Lp: diastolic pressure (mmHg), key in 2 to 3 figure places.
Zo: working control switch is placed " calibration " position, transferring basal impedance is 30, will go up switch again and put " measurement " position, just can obtain examinee's human body basal impedance Zo value.Key in three figure places.
Lo: tie up distance (cm) value between the top electrode of health neck root bottom electrode and xiphoid-process lower edge.Key in three figure places.
Hc: hematocrit, key in 359.
The health check-up parameter is keyed in and is finished, and clicks " measurement " key, and system enters automatically and decides baseline, calibration, measurement and processing, prints curve chart and examining report list with 32 heart function parameters of ECG, IRG, PCG at last.
The hardware of realizing above-mentioned functions has the high frequency electric of high-frequency current signal source (1) generation 50KHZ to be added on person under inspection's relevant electrode on one's body, by the electrocardioelectrode ECG that is checked on one's body, obtain ECG, IRG, PCG signal on hear sounds electrode PCG and the cardiac impedance electrode IRG, and obtained signal is amplified to certain amplitude by IRG amplifier (3), ECG amplifier (4), PCG amplifier (5).These three amplifier amplifying signals are aanalogvoltage.Analogue signal ECG, IRG, PCG deliver to amplifier shown in Figure 5 (26) respectively, further amplify the back is sent into A/D converter (6) respectively by outfan IN0, IN1, IN2 input again, A/D converter (6) is converted into digital quantity with analog quantity, sends into microcomputer main frame (8) among Fig. 6 by D0-D7 output by data/address bus.Trigger (27) 74LS76 is that the clock pulses of 500KHZ is used for A/D converter (6) with the clock division of 2MHZ.
The data/address bus D0-D7 of microcomputer main frame (8) connects random memory ram (31), read-only memory ROM(32 respectively among Fig. 6) (33).CTC(34), printer (12) font latch (35), word bit latch (36) etc.Address wire A0-A12 connects random memory ram (31), read-only memory ROM(32 respectively) (33), decoder (30).The chip selection signal of memory is by generations such as decoder (29) Y0, Y1.Decoder (30) produces the chip selection signal of PS1 signal as CTC, be added to the C end of the decoder (28) among Fig. 5 by the PS6 signal of decoder (30) generation, after deciphering, produce the 98H signal by outfan Y0, with gating running LED driver (37), remove to drive running LED (7).
Be the keyboard circuit of input person under inspection health check-up parameter among Fig. 7, keyboard is the ranks switch of one group of closure, and 6 row, 5 row are arranged, and 5 row alignments are gone here and there respectively and connect+the positive source of 5V behind the 100K resistance.Column signal is sent into microcomputer main frame (8) by triple gate (38).The D0-D5 of word bit latch (36) receives on the 6 every trade lines after anti-phase, and then connects the negative electrode of display (11).The D0-D6 of font latch (35) is on 7 sections of audion output back connection display (11).
The IOR, the IOW that are produced by microcomputer main frame (8) are connected printer with the signals such as PS7 that decoder (30) produces.
Claims (7)
1, automatic and woundless cardiac-function measuring instrument, after being made up of two large divisions's hardware, this system packs in the cabinet (13), first is collection amplification and high-frequency current signal source (1) of signal, the human body basal impedance is measured, display hardware such as (2) is formed, second portion is made up of hardware such as signal conversion processes calculating and input and output, it is characterized in that: realize conversion of signals, handle, calculate, the hardware of input and output has A/D converter (6), running LED (7), microcomputer main frame (8), keyboard (9), mode selection switch (10), display (11), printer (12) etc. and the used software of system's operation.
2, automatic and woundless cardiac-function measuring instrument according to claim 1 is characterized in that: the top panel at cabinet (13) is equipped with printer (12), on and off switch display lamp (22), keyboard (9), display (11), running LED (7) etc.The measurement of human body basal impedance, display (2), ZO knob (18), PCG jack (15), ECG jack (14), IRG jack (16), GAIN knob (17) and mode selection switch (10) are installed on the front panel of cabinet (13).
3, automatic and woundless cardiac-function measuring instrument according to claim 1 and 2, it is characterized in that: adopt the core signal ECG, cardiechema signals PCG and the cardiac impedance signal IRG that come by human body and be the simulation signal, after amplifier (26) further amplifies, deliver in the A/D converter (6) analog quantity is converted to digital quantity, send into then and carry out date processing calculating in the microcomputer main frame (8); The signal IOW IOR that is sent by microcomputer main frame (8) sends the P57 signal with decoder (30) and data/address bus D0-D9 signal is connected printer (12).The clock pulses of the employed 500KHZ of A/D converter (6) is by forming behind the clock division of trigger (27) with 2MHZ.
4, automatic and woundless cardiac-function measuring instrument according to claim 3 is characterized in that: random memory ram (31) capacity is that 8KB, read-only memory ROM are 16KB, for ease of the function expansion, expands to 64KB altogether.The employed chip selection signal Y0 of memory, Y1 are produced by decoder (29).Produce the PS1 signal as CTC(34 by decoder (30)) chip selection signal, the P56 signal that produces send the C end of decoder (28), the decoding back produces the 98H chip selection signal, goes gating running LED driver (37), removes to drive running LED (7) then.Be that system's pairing status indicator lamp in running is lighted.
5, according to claim 1 or 2 or 4 described automatic and woundless cardiac-function measuring instruments, it is characterized in that: what this system used is the keyboard with 32 keys, and reality has been used 25 keys, wherein 0-9, be 10 numeral keys.9 command keys are arranged, and command key has: restart key (START), down key (NEXT), go up key (LAST), C key (removings), from the beginning check key, measure key, beat again the chart key, beat again and show key, reset key etc.Two sex keys are arranged, and A key (woman), B key (man) have 4 spare keys.
6, automatic and woundless cardiac-function measuring instrument according to claim 5 is characterized in that: the circuit of realizing keypad function is the row, column switch of one group of closure, and 6 row, 5 row are arranged.The signal of sending here by data/address bus D5-P0, through word bit latch (36) latch, and 8/3 anti-phase after deliver to each row, also deliver to display (11) simultaneously.Article 5, alignment respectively is connected in series 100K resistance and connects+5V, and column signal send microcomputer main frame (8) by triple gate (38).Have key to press as line scanning and on this row, that then can determine to press according to the row, column signal is He Jian, and shows output by display (11).Display is made up of six common cathode seven segment digital tubes.The font code that shows is sent by data/address bus D6-D0, latch by font latch (35), after amplifying, triode delivers on seven sections of each charactron, the word bit code is sent by the D5-D0 data/address bus, latchs, is sent to after anti-phase the negative electrode of six charactrons by word bit latch (36).
7, according to claim 1 or 2 or 4 described automatic and woundless cardiac-function measuring instruments, it is characterized in that: the software that native system uses is write as with the Z80 assembler language.After program is finished, be solidificated in the read-only memory ROM(33 of 16KB) in.Wherein software program comprises initialize routine, the keyboard analysis programme; Data acquisition, processing, analysis, calculation procedure section and input/output routine.Output program can be printed 32 cardiac functional parameters and three curves.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN 88100018 CN1034665A (en) | 1988-01-08 | 1988-01-08 | Automatic and woundless cardiac-function measuring instrument |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN 88100018 CN1034665A (en) | 1988-01-08 | 1988-01-08 | Automatic and woundless cardiac-function measuring instrument |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CN1034665A true CN1034665A (en) | 1989-08-16 |
Family
ID=4831125
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN 88100018 Pending CN1034665A (en) | 1988-01-08 | 1988-01-08 | Automatic and woundless cardiac-function measuring instrument |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN1034665A (en) |
Cited By (16)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN102657525A (en) * | 2012-05-11 | 2012-09-12 | 季忠 | Nondestructive detection system and method of cardiac function |
| CN102772223A (en) * | 2011-05-10 | 2012-11-14 | 财团法人工业技术研究院 | System and method for discriminating heart sound/heart disease risk |
| EP2814385A4 (en) * | 2012-02-13 | 2015-10-07 | Cardio Scale Ltd | METHOD AND SYSTEM FOR ESTIMATING MOMENTANEOUS CARDIOVASCULAR PERFORMANCE RESERVE |
| CN105163652A (en) * | 2013-02-08 | 2015-12-16 | 株式会社K海奥斯威尔 | Apparatus for continuously and automatically measuring pulse wave and method for measuring blood pressure |
| US9595123B2 (en) | 2014-03-06 | 2017-03-14 | Respiratory Motion, Inc. | Methods and devices for displaying trend and variability in a physiological dataset |
| EP2603138B1 (en) * | 2010-08-13 | 2017-11-01 | Respiratory Motion, Inc. | Devices and methods for respiratory variation monitoring by measurement of respiratory volumes, motion and variability |
| CN109846464A (en) * | 2018-12-29 | 2019-06-07 | 曹乃钊 | The system for non-invasive measurement and data processing system of blood flow mechanics parameter |
| CN109984742A (en) * | 2019-04-22 | 2019-07-09 | 深圳大学 | Cardiac impedance signal processing system and method |
| US10441186B2 (en) | 2012-09-07 | 2019-10-15 | Respiratory Motion, Inc. | Electrode padset |
| US10702166B1 (en) | 2010-08-13 | 2020-07-07 | Respiratory Motion, Inc. | Devices and methods for respiratory variation monitoring by measurement of respiratory volumes, motion and variability |
| US11272889B2 (en) | 2015-12-15 | 2022-03-15 | Respiratory Motion, Inc. | Evaluation of respiratory volume monitoring (RVM) to detect respiratory compromise in advance of pulse oximetry and eliminate false desaturation alarms |
| CN116098629A (en) * | 2022-11-30 | 2023-05-12 | 深圳市杰纳瑞医疗仪器股份有限公司 | A method and device for simulating human body electrocardiogram signal generation |
| US11654234B2 (en) | 2014-11-04 | 2023-05-23 | Respiratory Motion, Inc. | Respiratory parameter guided automated IV administration and IV tube clamp activation |
| CN116413057A (en) * | 2023-04-07 | 2023-07-11 | 广东省医疗器械质量监督检验所 | Performance test method for impedance method noninvasive hemodynamic cardiac function detector |
| US11723542B2 (en) | 2010-08-13 | 2023-08-15 | Respiratory Motion, Inc. | Advanced respiratory monitor and system |
| US12343130B2 (en) | 2012-09-07 | 2025-07-01 | Respiratory Motion, Inc. | Spacing of electrodes for bioimpedance measurements |
-
1988
- 1988-01-08 CN CN 88100018 patent/CN1034665A/en active Pending
Cited By (21)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US10702166B1 (en) | 2010-08-13 | 2020-07-07 | Respiratory Motion, Inc. | Devices and methods for respiratory variation monitoring by measurement of respiratory volumes, motion and variability |
| US11723542B2 (en) | 2010-08-13 | 2023-08-15 | Respiratory Motion, Inc. | Advanced respiratory monitor and system |
| US12121334B2 (en) | 2010-08-13 | 2024-10-22 | Respiratory Motion, Inc. | Advanced respiratory monitor and system |
| EP2603138B1 (en) * | 2010-08-13 | 2017-11-01 | Respiratory Motion, Inc. | Devices and methods for respiratory variation monitoring by measurement of respiratory volumes, motion and variability |
| US11129536B2 (en) | 2010-08-13 | 2021-09-28 | Respiratory Motion, Inc. | Respiratory early warning scoring systems and methods |
| CN102772223A (en) * | 2011-05-10 | 2012-11-14 | 财团法人工业技术研究院 | System and method for discriminating heart sound/heart disease risk |
| EP2814385A4 (en) * | 2012-02-13 | 2015-10-07 | Cardio Scale Ltd | METHOD AND SYSTEM FOR ESTIMATING MOMENTANEOUS CARDIOVASCULAR PERFORMANCE RESERVE |
| US9603534B2 (en) | 2012-02-13 | 2017-03-28 | Cardio Scale Ltd. | Method and system for estimating momentary cardiovascular performance reserve |
| CN102657525B (en) * | 2012-05-11 | 2014-03-26 | 季忠 | Nondestructive detection system and method of cardiac function |
| CN102657525A (en) * | 2012-05-11 | 2012-09-12 | 季忠 | Nondestructive detection system and method of cardiac function |
| US12343130B2 (en) | 2012-09-07 | 2025-07-01 | Respiratory Motion, Inc. | Spacing of electrodes for bioimpedance measurements |
| US10441186B2 (en) | 2012-09-07 | 2019-10-15 | Respiratory Motion, Inc. | Electrode padset |
| CN105163652A (en) * | 2013-02-08 | 2015-12-16 | 株式会社K海奥斯威尔 | Apparatus for continuously and automatically measuring pulse wave and method for measuring blood pressure |
| US10347020B2 (en) | 2014-03-06 | 2019-07-09 | Respiratory Motion, Inc. | Methods and devices for displaying trend and variability in a physiological dataset |
| US9595123B2 (en) | 2014-03-06 | 2017-03-14 | Respiratory Motion, Inc. | Methods and devices for displaying trend and variability in a physiological dataset |
| US11654234B2 (en) | 2014-11-04 | 2023-05-23 | Respiratory Motion, Inc. | Respiratory parameter guided automated IV administration and IV tube clamp activation |
| US11272889B2 (en) | 2015-12-15 | 2022-03-15 | Respiratory Motion, Inc. | Evaluation of respiratory volume monitoring (RVM) to detect respiratory compromise in advance of pulse oximetry and eliminate false desaturation alarms |
| CN109846464A (en) * | 2018-12-29 | 2019-06-07 | 曹乃钊 | The system for non-invasive measurement and data processing system of blood flow mechanics parameter |
| CN109984742A (en) * | 2019-04-22 | 2019-07-09 | 深圳大学 | Cardiac impedance signal processing system and method |
| CN116098629A (en) * | 2022-11-30 | 2023-05-12 | 深圳市杰纳瑞医疗仪器股份有限公司 | A method and device for simulating human body electrocardiogram signal generation |
| CN116413057A (en) * | 2023-04-07 | 2023-07-11 | 广东省医疗器械质量监督检验所 | Performance test method for impedance method noninvasive hemodynamic cardiac function detector |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| CN1034665A (en) | Automatic and woundless cardiac-function measuring instrument | |
| US7536220B2 (en) | Methods for obtaining quick, repeatable and non-invasive bioelectrical signals in living organisms | |
| CN1736326A (en) | Multi-electrode module, measurement method and device using same, and lead search method | |
| CN1221325A (en) | Non-invasive monitoring of hemodynamic parameters using chest bioimpedance and electrocardiography | |
| CN101375178A (en) | Automated ultrasonic Doppler measurement | |
| CN1832703A (en) | System, method and apparatus for measuring blood flow and blood volume | |
| CN1572239A (en) | Electrocardiograph and display method for electrocardiograph | |
| JP2022552987A (en) | Method and apparatus for medical examination of animals | |
| CN109222934B (en) | System and method for bio-electrical impedance coherence measurement | |
| CN1739447A (en) | Portable electrocardiograph and processing method | |
| CN86102378A (en) | Measure the method and apparatus of circulatory function | |
| CN1073392C (en) | Multiple parameter monitor and its detecting method | |
| CN1526358A (en) | An electrical impedance tomography method and device for bedside image monitoring | |
| US20050010121A1 (en) | System and method for detecting and analyzing electrocardiological signals of a laboratory animal | |
| CN200970234Y (en) | Endocardium three dimension navigation system | |
| EP1745741A1 (en) | Ruler for evaluation of signals | |
| CN1661617A (en) | Automatic diagnosis method and device for autonomic nerve | |
| JP2019088643A (en) | Electrocardiogram analysis apparatus and control method thereof | |
| WO2015051621A1 (en) | Holter monitor | |
| JPH10262935A (en) | Method and apparatus for measuring pressure deformation characteristics of tissue around arterial blood vessels and pulse diagnostic device | |
| CN201091580Y (en) | Front guide-joint sucker pole for cardiogram | |
| CN1163091A (en) | Diagnosting and monitoring electrocardiograph designed based on hemodynamics | |
| CN205683079U (en) | A kind of electrocardiogram lead reversal connection alarm device | |
| CN210904427U (en) | Low-intermediate frequency feedback type injector | |
| CN207561894U (en) | Local anaesthesia detection device |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| C10 | Entry into substantive examination | ||
| SE01 | Entry into force of request for substantive examination | ||
| C06 | Publication | ||
| PB01 | Publication | ||
| C01 | Deemed withdrawal of patent application (patent law 1993) | ||
| WD01 | Invention patent application deemed withdrawn after publication |