CN103919542B - Based on the noncontact cerebrospinal fluid pulse pressure ripple monitoring device of magneticinduction - Google Patents
Based on the noncontact cerebrospinal fluid pulse pressure ripple monitoring device of magneticinduction Download PDFInfo
- Publication number
- CN103919542B CN103919542B CN201410177433.4A CN201410177433A CN103919542B CN 103919542 B CN103919542 B CN 103919542B CN 201410177433 A CN201410177433 A CN 201410177433A CN 103919542 B CN103919542 B CN 103919542B
- Authority
- CN
- China
- Prior art keywords
- signal
- pulse pressure
- unit
- cerebrospinal fluid
- pressure ripple
- 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.)
- Expired - Fee Related
Links
Landscapes
- Measuring And Recording Apparatus For Diagnosis (AREA)
Abstract
Based on a noncontact formula cerebrospinal fluid pulse pressure ripple monitoring device for magneticinduction, comprising: an ac signal which unit, it is used for producing an actuation signal to sensor unit and produces to encourage magnetic field and a reference signal to Signal acquiring and processing unit; The sensor unit being placed on oblongata Chi Chu below occipital bone, sensor unit comprise an annular drive coil and two lay respectively at detection coil coaxial with drive coil above and below drive coil, for launch actuation signal and detection induction signal; One differential amplifier, for the signal that two are detected coil is carried out differential amplification, offsets the mains field in detection signal; With a Signal acquiring and processing unit, obtain cerebrospinal fluid pulse pressure ripple for the signal gathered being carried out process.
Description
Technical field
The invention belongs to biomedical technical field of medical equipment, it is specifically related to the non-contact magnetic inductive cerebrospinal fluid pulse pressure ripple monitoring device in Neurological Surgery, health care and medical assessment field.
Background technology
Cerebrospinal fluid pulse pressure ripple is the fluctuation up and down occurred along with heart beat cycles on the basis of cranium pressure, in fact the change of cerebrospinal fluid pulse pressure ripple reflects in heartbeat process, due to the corresponding fluctuation change of intracranial pressure that Q volume of blood fluctuation change in cranium causes cranium internal volume to change and cause, i.e. intracranial compliance. Intracranial pressure conformability, all has important clinical value in the diagnosis of many Cerebral Injury, monitoring, state of an illness judgement etc. Monitoring cerebrospinal fluid pulse pressure ripple is as the direct reaction of cranium brain conformability, and its monitoring is significant equally. Currently, the monitoring of cerebrospinal fluid pulse pressure ripple has mainly relied on wound method, and such as pressure volumetric method, lumbar puncture method etc., easily cause infection, patient brings secondary damage, and measuring accuracy and the scope of application all have limitation.
At present, method without wound cerebrospinal fluid pulse pressure ripple monitoring mainly contains: transcranial Doppler is ultrasonic, retinal vein platen press, iridescent visual Evoked ptential method, ear drum membrane detection method, bioelectrical impedance analysis etc., all belong to indirect inspection, all directly do not pay close attention to motion and the change of cerebrospinal fluid, pressure conduction, path for transformation complexity, its accuracy and feasibility wait further research, although the iconography technology by representative of CT, MRI can have location and the feature such as accurate directly perceived, but it is expensive, lack behavioral characteristics, it is not suitable for bedside monitoring and personalized medicine. Along with the development of personalized medicine demand, a set of high precision, noncontact cerebrospinal fluid pulse pressure ripple Monitoring systems easy to operate, noninvasive have very important clinical value.
Intracranial tissue conductivity variations is mainly detected by magneticinduction phase-shifting technique, and the advantage of the method is: (1) magneticinduction phase shift has the theory clear and definite with cerebral tissue conductivity variations and experiment corresponding relation; (2) adopt magnetic excitation and the method for magnetic induction measurement, it does not have electrode and head contact, solve heavy head-brain injury, problem that serious burn, transmissible disease, tetter, the patient such as allergic are not easy to lay contact electrode at head; (3) adopting the method for magnetic excitation and magnetic induction measurement, avoid impact and the scalp shunting action of low conductivity skull, measurement sensistivity is higher, is applicable to clinical, family and the monitoring of outdoor environment vital sign.
For the existing deficiency without wound cerebrospinal fluid pulse pressure ripple monitoring method, and the needs of clinical Neurological Surgery diagnosis and treatment, personalized medicine health care and professional's medical assessment, proposing a kind of noncontact, high precision, miniaturization, easy to operate reliable monitoring method, to improving, the diagnosis of clinical Cerebral Injury, monitoring, Level of first-aid treatment and personalized medicine health care are significant.
Summary of the invention
Technical problem to be solved by this invention is to solve the shortcomings such as tradition cerebrospinal fluid pulse pressure ripple Monitoring systems has wound detection, tradition non-invasive monitoring method precision not high, it is proposed to a kind of noncontact cerebrospinal fluid pulse pressure ripple monitoring device based on magneticinduction.
The technical scheme solved the problems of the technologies described above is as follows:
A kind of non-contact magnetic inductive cerebrospinal fluid pulse pressure ripple monitoring device, an ac signal which unit, can produce 100KHz-100MHz and exchange signal, produces to encourage magnetic field and a reference signal to Signal acquiring and processing unit for generation of an actuation signal to sensor unit.
The sensor unit being placed on oblongata Chi Chu below occipital bone, sensor unit is for launching actuation signal and detection induction signal; One differential amplification unit, for sensor unit inspection gained two paths of signals is carried out differential amplification, offsets mains field and a Signal acquiring and processing unit, obtains cerebrospinal fluid pulse pressure ripple for the signal gathered carries out process.
Sensor unit comprises: an annular drive coil and two lay respectively at detection coil coaxial with drive coil above and below drive coil, and annular drive coil receives actuation signal, produces excitation magnetic field, and detection coil receives two-way magneticinduction signal.
Differential amplification unit comprises: one can produce the power supply of+5V ,-5V volts DS, for powering to differential amplifier; One low-pass filter, limiting frequency is 12MHz, for detection signal medium-high frequency interference is carried out filtering; One preposition differential amplifier, for the mains field part in signal being offset, carries out differential amplification to detection signal.
Signal acquiring and processing unit comprises: a phase detection unit, reference signal and differential amplification unit output signal are carried out phase-detection, and exports a d. c. voltage signal being directly proportional to the phase differential of described reference signal and the two paths of signals of differential output signal. One processing unit, carries out signal processing by the signal collected, and obtains cerebrospinal fluid pulse pressure wave frequency. Comprise a storage unit, by pulse pressure wave datum real-time storage in this storage unit. Draw together a display unit, pulse pressure waveform is shown on the display unit in real time.
The numerary signal that collects by pulse pressure ripple identification algorithm, is calculated real-time pulse pressure wave frequency by processing unit, and shows program by waveform and shown in real time by cerebrospinal fluid pulse pressure waveform.
The drive coil of the centre of sensor unit and the detection coil of both sides are printed on multilayer circuit board with coaxial form.
The advantage of the magnetic induction measurement device of the present invention is: 1, noncontact, without any pungency and uncomfortable sense (not needing and measured target skin contact). 2, accuracy height, has small displacement not affect measured result. 3, compact, low in energy consumption, conveniently monitor whenever and wherever possible.
The present invention one feature is to utilize double detection coil to carry out phase place signal detection in conjunction with differential amplification unit. Its form is one and detects coil near testee, and for signal detection, another detection coil deviates from detection coil, relatively away from testee, as with reference to signal. The induction signal caused due to actuation signal in single coil accounts for main component, the phase place information of target signal can partly be fallen into oblivion, therefore utilize double detection coil in conjunction with the form of difference unit, advantage is to utilize difference unit the mains field actuation signal in two detection coils to be offseted, and then the induction signal caused by eddy current in testee amplifies, thus system can be improved to the sensitivity of organism vortex induction signal phase place information. On the other hand, systems axiol-ogy environment is at 10MHz, and high frequency noise interference is relatively big, utilizes difference unit also can part random noise be offseted. According to this research team early stage work and practical experience, for identical physical model, detection system described in the invention compared to tradition list detect coil system in sensitivity, stability aspect is all significantly increased.
Accompanying drawing explanation
Fig. 1 is the block diagram of the non-contact magnetic inductive cerebrospinal fluid pulse pressure ripple monitoring device of the present invention;
Fig. 2 is sensor unit structure figure;
Fig. 3 is sensor multi-layer PCB schematic three dimensional views;
Fig. 4 human body non-contact magnetic inductive cerebrospinal fluid pulse pressure ripple monitoring schematic diagram;
Fig. 5 human body pulse pressure ripple monitor signal example;
Fig. 6 differential amplification unit schematic circuit diagram;
Fig. 7 process, display, storage unit circuit schematic diagram.
Embodiment
Technical problem to be solved by this invention is to solve the shortcomings such as tradition cerebrospinal fluid pulse pressure ripple Monitoring systems has wound detection, tradition non-invasive monitoring method precision not high, it is proposed to a kind of noncontact cerebrospinal fluid pulse pressure ripple monitoring device based on magneticinduction.
As shown in Figure 1, 2, 3, a kind of non-contact magnetic inductive cerebrospinal fluid pulse pressure ripple monitoring device, this sensor unit can directly be placed in oblongata Chi Chu below patient's occipital bone, it is also possible to is placed in pillow inside. Can be able to being produced on same piece of circuit card by ac signal which unit, differential amplification unit and Signal acquiring and processing unit, the unit volume that this circuit card is formed like this is small and exquisite, is convenient to be placed in bed side or carry with. Sensor not with skin contact, definitely safety again can freely activity. Retainer instrument can also be formed, sensor unit adopts the fixing mode of net cap be fixed on oblongata Chi Chu below patient's occipital bone, and ac signal which unit, differential amplification unit and Signal acquiring and processing unit and other display unit etc. form set of device and are placed on human body on one side. The object of Real-Time Monitoring can be realized. Fig. 4 is the schematic diagram that sensor unit is placed in oblongata Chi Chu below experimenter's occipital bone.
Fig. 1 is the block diagram of the non-contact magnetic inductive cerebrospinal fluid pulse pressure ripple monitoring device of the present invention, ac signal which unit generates a road actuation signal and a road reference signal, comprise the crystal oscillator that can produce 7MHz sine wave, a power divider and a power amplifier. The signal that crystal oscillator exports is connected to the input terminus of power divider, after power divider, exports the exchange signal that two-way is completely the same. One road signal is as the input terminus being connected to phase detection unit with reference to signal; Another road signal, by obtaining the actuation signal of 80mW after a power amplifier, the drive coil that actuation signal is connected on signal acquisition process plate by wire, produces excitation magnetic field.
As shown in Figure 2,3, sensor unit comprises one and is positioned at the annular drive coil in outside and is positioned at stacked at a certain distance between the upper and lower two the being parallel to each other detection coil of inner side, Fig. 2 is orthographic plan, it can be seen that annular drive coil and the position relation detecting coil, but is not limited to this. Fig. 3 illustrates the three-dimensional position relation of drive coil with detection coil, and two detection coils lay respectively at above and below the plane of drive coil place and coaxially arrange with drive coil, namely overlap apart from certain distance between the upper and lower. Annular drive coil receives actuation signal, produces excitation magnetic field, and detection coil receives two-way magneticinduction signal. This sensor unit can adopt circuit board making, and as shown in Figure 2,3, the drive coil in outside and the detection coil of inner side both up and down are printed on multilayer circuit board with coaxial form. The two ends of drive coil are connected on the positive-negative output end of an output terminal of ac signal which unit by two wires, and wherein a wire is not electrically connected with each turn coil when crossing over each coil. Altogether, the other end difference access differential amplifies two input ports of unit, and differential amplification unit is connected on an input terminus of signal processing unit by wire in two detection coil one end. Measured target cerebrospinal fluid beat cause inducedmagnetic field change can be detected, there is higher monitoring sensitivity.
Signal acquiring and processing unit comprises a phase detection unit, and reference signal and differential amplification unit output signal are carried out phase-detection, and exports a d. c. voltage signal being directly proportional to the phase differential of shown reference signal and differential amplification unit output signal; One processing unit, has AD acquisition function and data processing function, and the signal collected is carried out analog to digital conversion and process, obtains cerebrospinal fluid pulse pressure waveform and frequency information.
Described phase detection unit, it is possible to adopt mirror phase chip or other phase-detection chips. The input terminus of phase detection unit is connected with the output signal of described reference signal and differential amplification unit respectively; Phase detection unit exports a d. c. voltage signal being directly proportional to two-way input signal phase difference (MIPS), and this voltage signal reflects phase differential, and phase differential reflects the change of cerebrospinal fluid volume in oblongata pond. Mirror phase chip is adopted to have the feature of high precision and miniaturization, precision of phase discrimination 0.01 ��, mirror phase bandwidth 1��100MHz, and chip volume is small and exquisite, it may also be useful to convenient.
Processing unit, after being changed by A/D conversion unit by the d. c. voltage signal exported from phase detection unit, by cerebrospinal fluid pulse pressure ripple identification algorithm, calculates real-time pulse pressure wave frequency. This processing unit can adopt micro-chip, or other treaters. Micro-chip can select STM32F103RBT6 micro-chip, and this micro-chip carries AD acquisition function.
A storage unit can also be comprised, by pulse pressure wave datum real-time storage on a SD storage card. SD card can store the phase data of for some time.
A display unit can also be comprised, pulse pressure waveform is shown on the display unit in real time. Display unit can select 3.5 cun of display screens.
Comprise a 3.3V power supply, power for processing unit circuit card to whole device.
Have employed such scheme, during measurement, sensor unit is positioned over oblongata Chi Chu below tested object occipital bone, actuation signal connects drive coil and produces excitation magnetic field through the whole oblongata pond of experimenter, excitation field signal forms a superposition field signal relative to reference signal generation phase change together with secondary magnetic field Signal averaging, the detected coil of this superposition field signal receives, and output to differential amplification unit, to remove mains field impact, then export phase measurement cells again to and measure phase differential, this phase differential and oblongata pond cerebrospinal fluid whole conductivity are proportional relation, and global tissue specific conductivity is relevant to the volume of cerebrospinal fluid. this phase differential is by obtaining pulse pressure wave frequency after Single Chip Microcomputer (SCM) program acquisition process and outputs to and shows in real time on 3.5 cun of display screens. therefore, it is possible to by the change of the phase differential reflection pulse pressure ripple between detection superposition field signal and reference signal.
As shown in Figure 5, it is volunteer's cerebrospinal fluid pulse pressure ripple signal.
Fig. 6, Fig. 7 are embodiment circuit diagram, and Fig. 6 is differential amplifier circuit, Fig. 7 processing unit, storage unit, display unit circuit.
The advantage of the magnetic induction measurement device of the present invention is: 1, noncontact, without any pungency and uncomfortable sense (not needing directly to contact with measured target). 2, accuracy height, has small displacement not affect measured result. 3, compact, low in energy consumption, conveniently monitor whenever and wherever possible.
Claims (8)
1. a non-contact magnetic inductive cerebrospinal fluid pulse pressure ripple monitoring device, it is characterised in that, comprising:
One ac signal which unit, can produce 100KHz-100MHz and exchange signal, produces to encourage magnetic field and a reference signal to Signal acquiring and processing unit for generation of an actuation signal to sensor unit;
The sensor unit being placed under occipital bone;
One differential amplification unit, comprises the power supply that can produce volts DS, and for powering to differential amplification unit, described differential amplification unit is used for that sensor unit inspection gained two-way is detected signal and carries out differential amplification, offsets mains field;
One Signal acquiring and processing unit, obtains cerebrospinal fluid pulse pressure ripple signal for the signal gathered carries out process, comprising:
One phase detection unit, carries out phase-detection to reference signal and differential amplification unit output signal, and exports a d. c. voltage signal being directly proportional to the phase differential of described reference signal and described differential amplification unit output signal;
One processing unit, carries out signal processing by the signal collected, and obtains cerebrospinal fluid pulse pressure wave frequency;
Wherein, sensor unit comprises: an annular drive coil and two lay respectively at detection coil coaxial with drive coil above and below drive coil, annular drive coil receives actuation signal, produces excitation magnetic field, and detection coil receives two-way magneticinduction signal; And
Differential amplification unit comprises:
One low-pass filter, limiting frequency is 12MHz, for detection signal medium-high frequency interference is carried out filtering;
One preposition differential amplifier, for the mains field part in signal being offset, detects signal to two-way and carries out differential amplification.
2. non-contact magnetic inductive cerebrospinal fluid pulse pressure ripple monitoring device as claimed in claim 1, it is characterised in that, the input terminus of described phase detection unit is connected with the output signal of described reference signal and differential amplification unit.
3. non-contact magnetic inductive cerebrospinal fluid pulse pressure ripple monitoring device as claimed in claim 1, it is characterised in that, comprise a storage unit, by pulse pressure wave datum real-time storage in this storage unit.
4. non-contact magnetic inductive cerebrospinal fluid pulse pressure ripple monitoring device as claimed in claim 1, it is characterised in that, comprise a display unit, pulse pressure waveform is shown on the display unit in real time.
5. non-contact magnetic inductive cerebrospinal fluid pulse pressure ripple monitoring device as claimed in claim 4, it is characterised in that, described display unit comprises 3.5 cun of display screens.
6. non-contact magnetic inductive cerebrospinal fluid pulse pressure ripple monitoring device as claimed in claim 1, it is characterised in that, described ac signal which unit, comprises the crystal oscillator that can produce 7MHz sine wave, a power divider and a power amplifier.
7. non-contact magnetic inductive cerebrospinal fluid pulse pressure ripple monitoring device as claimed in claim 1, it is characterized in that, the numerary signal that collects by pulse pressure ripple identification algorithm, is calculated real-time pulse pressure ripple and beats frequency, and show program by waveform and shown in real time by pulse pressure waveform by processing unit.
8. non-contact magnetic inductive cerebrospinal fluid pulse pressure ripple monitoring device as claimed in claim 1, it is characterised in that, the drive coil in outside and the two of inner side detection coils are printed on multilayer circuit board with coaxial form.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201410177433.4A CN103919542B (en) | 2014-04-29 | 2014-04-29 | Based on the noncontact cerebrospinal fluid pulse pressure ripple monitoring device of magneticinduction |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201410177433.4A CN103919542B (en) | 2014-04-29 | 2014-04-29 | Based on the noncontact cerebrospinal fluid pulse pressure ripple monitoring device of magneticinduction |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CN103919542A CN103919542A (en) | 2014-07-16 |
| CN103919542B true CN103919542B (en) | 2016-06-01 |
Family
ID=51138120
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN201410177433.4A Expired - Fee Related CN103919542B (en) | 2014-04-29 | 2014-04-29 | Based on the noncontact cerebrospinal fluid pulse pressure ripple monitoring device of magneticinduction |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN103919542B (en) |
Family Cites Families (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| EP3571986A1 (en) * | 2012-01-19 | 2019-11-27 | Cerebrotech Medical Systems, Inc. | Diagnostic system for detection of fluid changes |
| CN203000923U (en) * | 2012-11-30 | 2013-06-19 | 中国人民解放军第三军医大学 | Non-contact magnetic induction-type intracranial pressure monitor |
| CN103598883B (en) * | 2013-12-03 | 2015-04-22 | 中国人民解放军第三军医大学 | Intracranial pressure monitoring method based on magnetic induction phase difference change |
-
2014
- 2014-04-29 CN CN201410177433.4A patent/CN103919542B/en not_active Expired - Fee Related
Also Published As
| Publication number | Publication date |
|---|---|
| CN103919542A (en) | 2014-07-16 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| CN102973260B (en) | Noncontact magnetic sensing-type intracranial pressure monitoring device | |
| CN203000923U (en) | Non-contact magnetic induction-type intracranial pressure monitor | |
| CN106937865B (en) | Temperature monitoring system and monitoring method capable of early warning breast lesions | |
| CN103598883B (en) | Intracranial pressure monitoring method based on magnetic induction phase difference change | |
| CN104039219A (en) | Devices and methods for monitoring cerebral hemodynamic characteristics | |
| US20130041271A1 (en) | Devices and methods for monitoring intracranial pressure and additional intracranial hemodynamic parameters | |
| US20110137189A1 (en) | Physiological signal sensing system without time and place contraint and its method | |
| JP2016519606A (en) | Measurement of physiological parameters of the brain using bioimpedance | |
| Wang et al. | A novel intracranial pressure readout circuit for passive wireless LC sensor | |
| JP2015512735A (en) | Measurement of physiological parameters of the brain using bioimpedance | |
| US11475987B2 (en) | Wearable inductive damping sensor | |
| CN113133753A (en) | Biological tissue blood flow real-time monitoring system and simulation monitoring system based on magnetic induction phase shift | |
| CN105832327B (en) | A kind of passive monitoring intracranial pressure system of implantation type wireless | |
| CA3113800A1 (en) | Model-based sensor technology for detection of cardiovascular status | |
| CN103860154B (en) | The wearable cardiopulmonary activity monitoring device of noncontact based on magnetic induction | |
| WO2022180306A2 (en) | Apparatus for and method of measuring intracranial dynamics | |
| CN102813513A (en) | Non-invasive intracranial pressure measurement method and measurement instrument | |
| CN103919542B (en) | Based on the noncontact cerebrospinal fluid pulse pressure ripple monitoring device of magneticinduction | |
| Al Younis et al. | Non-invasive technologies for heart failure, systolic and diastolic dysfunction modeling: A scoping review | |
| CN201683898U (en) | Hydrocephalus type examining device | |
| Jetzki et al. | A multisensor implant for continuous monitoring of intracranial pressure dynamics | |
| CN113288102B (en) | System for monitoring cerebral blood flow without wound | |
| Zeng et al. | A Wearable Device for Dynamic Monitoring of Cerebral Blood Flow Based on Electromagnetic Coupling Sensing | |
| CN101849818B (en) | Device for checking type of cerebral edema | |
| Yang et al. | BrainZ-BP: A Non-invasive Cuff-less Blood Pressure Estimation Approach Leveraging Brain Bio-impedance and Electrocardiogram |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| C06 | Publication | ||
| PB01 | Publication | ||
| C10 | Entry into substantive examination | ||
| SE01 | Entry into force of request for substantive examination | ||
| C14 | Grant of patent or utility model | ||
| GR01 | Patent grant | ||
| CF01 | Termination of patent right due to non-payment of annual fee |
Granted publication date: 20160601 Termination date: 20200429 |
|
| CF01 | Termination of patent right due to non-payment of annual fee |