CN109091144A - A kind of monitoring system of non-contacting brain edema mesencephalic tissue water content development - Google Patents
A kind of monitoring system of non-contacting brain edema mesencephalic tissue water content development Download PDFInfo
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Abstract
The invention discloses the monitoring systems that tissue water content in a kind of non-contacting brain edema develops, and mainly include MRI imaging system, brain tissue to be measured, exciting signal source, transmitting coil, receiving coil, signal acquisition module, signal processing module and display.MRI imaging system measures the brain water content of brain tissue to be measured.The brain tissue to be measured is fixed between the transmitting coil and the receiving coil.The signal processing module handles reference signal and detection signal, calculates reference signal and detects the phase shift θ of signal.Signal processing module is superimposed magnetic induction phase shift θ, measurement coefficient k and brain tissue t to be measured between magnetic field and main field according to any time t0The brain water content W at moment0The brain water content W of brain tissue to be measured is calculated in real time.The present invention carries out real-time monitoring to brain water content using the monitoring system that non-contacting brain edema mesencephalic tissue water content develops.
Description
Technical field
The present invention relates to the tolerant method of real-time of the intracerebral of biomedical engineering field, specifically a kind of non-contacting brain
The monitoring system of oedema mesencephalic tissue water content development.
Background technique
The brain edema secondary disease extremely common as cerebral apoplexy (hemorrhagic and ischemic) is that patient is caused to generate forever
The main reason for long property cerebral injury and death.A variety of pathogenic factor collective effects promote intracerebral moisture abnormal increase to cause brain
Oedema generates.With the generation of brain edema, brain parenchym volume expands, and causes and aggravate intracranial pressure (ICP) to increase, when developing to one
Determine severity and cannot timely and effectively be controlled, intracranial pressure will be increased persistently, cause irreversibility nerve function to patient
It can damage, or even cause brain displacement, hernia cerebri, eventually lead to patient and lose life.Therefore, brain edema state of development is grasped in time,
It helps to improve the treatment condition of patients with cerebral apoplexy, improve its prognosis.
Currently, the clinical examination means of brain edema mainly include invasive monitoring intracranial pressure, transcranial Doppler (TCD) ultrasound,
Iconography etc..Intracranial pressure is one of most important physiology indication of field of neurosurgery.Can at present clinic ICP monitor generallyd use
The mode of wound can cause secondary pain to patient, and easily lead to bleeding, infection and other complication.TCD inspection technique belongs to noninvasive
Brain edema detection method, but the inspection of big vascular flow amount can only be carried out, detection depth is limited, is also not suitable for as real-time monitoring
The means of brain edema.The iconographies such as CT, MRI equipment can obtain the encephalic image of high-resolution, can determine that edema volume and
Position.But since brain edema metamorphosis takes a long time, so that the iconographies equipment such as CT, MRI is difficult at the first time
Detect the generation of brain edema, such equipment volume is huge, complicated for operation in addition, can not carry out to apoplexy patient real-time continuous
Bedside monitoring, detection time resolution ratio is low, is easy delay brain edema optimal diagnosing and treating opportunity.Therefore, still do not have so far
There is safe and efficient method that can carry out real-time continuous bedside monitoring to brain edema, developing a kind of easy to operate, safety has
The real-time continuous monitoring method of the brain edema of effect reduces its lethality, disability rate has for improving the treatment condition of patients with cerebral apoplexy
Important meaning.
There is an important index parameter in brain edema ----brain water content, after traumatic brain edema occurs, brain
The increase of tissue water content is the immediate cause that brain parenchym volume increases.Brain water content is reflection brain parenchym water content variation
Direct quantizating index, in the clinic of brain edema and experimental study, be widely used in assess brain edema severity.
The measurement method of current brain water content mainly includes direct method and indirect method.The common direct method of measurement is dry
Wet weight method, collecting part brain parenchym sample, first weighs weight in wet base, then weighs dry weight after being baked to, by calculate dry weight with it is wet
The ratio of weight obtains brain water content.The direct method of measurement can accurately obtain the absolute value of brain water content, but
Brain parenchym entity sample must be extracted, thus routine clinical detection method can not be become.Indirect method is MRI mensuration.Just
In normal situation, brain water content is by height adjustment, once lesion occurs, its pathological change is easy to by MRI fast quantification
Identification.However, MRI detection device volume is excessively huge, and generally fixed placement, brain edema patient can not be connected in real time
Continuous bedside monitoring.
Summary of the invention
Present invention aim to address problems of the prior art.
To realize the present invention purpose and the technical solution adopted is that such, a kind of non-contacting brain edema mesencephalic tissue contains
The monitoring system of water development mainly includes MRI imaging system, brain tissue to be measured, exciting signal source, transmitting coil, receives line
Circle, signal acquisition module, signal processing module and display.
The MRI imaging system measures the brain tissue t to be measured respectively0The brain water content W at moment0And t1Moment
Brain water content W1, and by brain water content W0With brain water content W1Pass to the signal processing module.
The brain tissue to be measured is fixed between the transmitting coil and the receiving coil.
Further, the brain tissue to be measured is head.
The spacing of the brain tissue to be measured and transmitting coil is less than 10mm.The spacing of the brain tissue to be measured and receiving coil
Less than 10mm.
The transmitting coil and the receiving coil are coaxial parallel coil.The transmitting coil and the receiving coil
Size and spacing are mainly adjusted according to the shapes and sizes of the head.
The exciting signal source is binary channels alternating message source.Frequency by the pumping signal of the transmitting coil is
1MHz~10MHz.
The exciting signal source sends the identical signal of two-way to the transmitting coil and the signal acquisition module respectively.
Wherein, the signal that the transmitting coil receives is denoted as pumping signal, and the signal that the signal acquisition module receives is denoted as ginseng
Examine signal.
After the transmitting coil receives pumping signal, main field is generated.The main field is passing through the brain group to be measured
Disturbed magnetic field is generated after knitting.After the receiving coil receives the superposition magnetic field of main field and disturbed magnetic field, detection signal is generated.
The signal acquisition module receives the detection signal of receiving coil transmission.
Reference signal and detection signal are passed to signal processing module by the signal acquisition module.
The signal processing module to reference signal and detection signal handle, calculate any time t reference signal and
Detect the magnetic induction phase shift θ between the phase shift θ namely any time t superposition magnetic field and main field of signal.Wherein, remember t1
The magnetic induction phase shift being superimposed between magnetic field and main field that moment is calculated is θ1。
The signal processing module is according to t1Moment is superimposed the magnetic induction phase shift θ between magnetic field and main field1, brain to be measured
Organize t1The brain water content W at moment1With brain tissue t to be measured0The brain water content W at moment0Measurement coefficient k is calculated.
Measurement coefficient k is as follows:
In formula, θ1For t1Moment is superimposed the magnetic induction phase shift between magnetic field and main field.W1For brain tissue t to be measured1Moment
Brain water content.W0For brain tissue t to be measured0The brain water content at moment.
The signal processing module is according to the magnetic induction phase shift θ between the superposition magnetic field any time t and main field, measurement
Coefficient k and brain tissue t to be measured0The brain water content W at moment0The brain tissue for calculating any time t brain tissue to be measured in real time is aqueous
Measure W.The brain water content W of any time t brain tissue to be measured is passed to the display by the signal processing module.
The brain water content W of the brain tissue any time t to be measured is as follows:
W=k θ+W0。 (2)
In formula, W0For brain tissue t to be measured0The brain water content at moment.K is measurement coefficient.θ is that any time t is superimposed magnetic
Magnetic induction phase shift between field and main field.
The display shows the numerical value of the brain water content W of any time t brain tissue to be measured.
The solution have the advantages that unquestionable.The present invention proposes to use non-contacting magnetic-inductive device, and passes through
Measurement magnetic induction phase shift reflects the conductivity variations of cranium brain, thus set up magnetic induction phase shift and brain water content it
Between relationship.The system has great importance for the real-time monitoring of brain edema.The present invention is non-contact, and hurtless measure does not need
It is directly contacted with measured object, avoids infection.Meanwhile the present invention measurement it is simple and convenient, system cost is very low, be expected into
The integrated miniaturization of row, so as to real-time on-site monitoring.The present invention utilizes the development of non-contacting brain edema mesencephalic tissue water content
Monitoring system carries out real-time monitoring to brain water content.
Detailed description of the invention
Fig. 1 is system principle diagram；
In figure: MRI imaging system 0, brain tissue to be measured 1, exciting signal source 2, transmitting coil 3, receiving coil 4, signal are adopted
Collect module 5, signal processing module 6 and display 7.
Specific embodiment
Below with reference to embodiment, the invention will be further described, but should not be construed the above-mentioned subject area of the present invention only
It is limited to following embodiments.Without departing from the idea case in the present invention described above, according to ordinary skill knowledge and used
With means, various replacements and change are made, should all include within the scope of the present invention.
Embodiment 1:
The monitoring system of tissue water content development in a kind of non-contacting brain edema, mainly include MRI imaging system 0, to
Survey brain tissue 1, exciting signal source 2, transmitting coil 3, receiving coil 4, signal acquisition module 5, signal processing module 6 and display
7。
The MRI imaging system 0 measures the brain tissue 1t to be measured respectively0The brain water content W at moment0And t1Moment
Brain water content W1, and by brain water content W0With brain water content W1Pass to the signal processing module 6.
The brain tissue to be measured 1 is fixed between the transmitting coil 2 and the receiving coil 3.
Further, the brain tissue to be measured is head.
The spacing of the brain tissue to be measured 1 and transmitting coil 2 is less than 10mm.The brain tissue to be measured 1 and receiving coil 3
Spacing is less than 10mm.
The exciting signal source 2 sends identical signal to the transmitting coil 3 and the signal acquisition module 5 respectively.
Wherein, the signal that the transmitting coil 3 receives is denoted as pumping signal, and the signal that the signal acquisition module 5 receives is denoted as
Reference signal.
Exciting signal source 2 be used for generate frequency 1MHz-10MHz range two-way with frequency in-phase signal.Exciting signal source
As long as binary channels alternating message source, band are wider than 10MHz.
After the transmitting coil 3 receives pumping signal, main field is generated.If magnetic field strength is lower, can motivate
Add a power amplifier to amplify magnetic field strength between signal source and transmitting coil, enhances collected physiological signal.It is described
Main field generates disturbed magnetic field after through the brain tissue to be measured.The receiving coil 4 receives main field and disturbed magnetic field
After being superimposed magnetic field, detection signal is generated.
The signal acquisition module 5 receives detection signal.
Signal acquisition module 5 can use twin-channel data collecting card, also can use lock-in amplifier, can also adopt
Data acquisition is carried out with single-chip microcontroller and A/D converter.The emitted coil of pumping signal and the acquisition of receiving coil arriving signal all the way
Module 5, another way reference signal is directly sent to signal acquisition module 5, and converts the signal into digital signal with A/D converter.
Reference signal and detection signal are passed to signal processing module by the signal acquisition module 5.
The signal processing module 6 to reference signal and detection signal handle, calculate any time t reference signal and
Detect the magnetic induction phase shift θ between the phase shift θ namely any time t superposition magnetic field and main field of signal.At the signal
Calculated magnetic induction phase shift θ can be carried out using ready-made fft algorithm by managing module 6.Wherein, remember t1The superposition that moment is calculated
Magnetic induction phase shift between magnetic field and main field is θ1。
The signal processing module 6 is according to t1Moment is superimposed the magnetic induction phase shift θ between magnetic field and main field1, brain to be measured
Organize 1t1The brain water content W at moment1With brain tissue 1t to be measured0The brain water content W at moment0Measurement coefficient is calculated
k.Measurement coefficient k is as follows:
In formula, θ1For t1Moment is superimposed the magnetic induction phase shift between magnetic field and main field.W1For brain tissue 1t to be measured1When
The brain water content at quarter.W0For brain tissue 1t to be measured0The brain water content at moment.
The signal processing module 6 is according to the magnetic induction phase shift θ between the superposition magnetic field any time t and main field, survey
Coefficient of discharge k and brain tissue 1t to be measured0The brain water content W at moment0The brain tissue of any time t brain tissue 1 to be measured is calculated in real time
Water content W.The brain water content W of any time t brain tissue 1 to be measured is passed to the display by the signal processing module 6
Device 7.
The brain water content W of 1 any time of the brain tissue to be measured t is as follows:
W=k θ+W0。 (2)
In formula, W0For brain tissue 1t to be measured0The brain water content at moment.K is measurement coefficient.θ is any time t superposition
Magnetic induction phase shift between magnetic field and main field.
The display 7 shows the numerical value of the brain water content W of any time t brain tissue 1 to be measured.Display can be
Arbitrarily it is capable of the device of the brain water content W value of real-time display brain tissue 1 to be measured, such as PC machine.
Embodiment 2:
The application method of the monitoring system of tissue water content development in a kind of non-contacting brain edema, mainly including following step
It is rapid:
1) the monitoring system of tissue water content development in non-contacting brain edema is set up.
2) by brain tissue 1 to be measured, i.e., the head with brain edema is fixed in MRI imaging system, at the beginning of measuring brain edema
Brain water content W under beginning state0And t1The brain water content W at moment1, and by brain water content W0Contain with brain tissue
Water W1Pass to the signal processing module 6.
3) in t1Moment, the exciting signal source 2 are sent to the transmitting coil 3 and the signal acquisition module 5 respectively
Identical signal.Wherein, the signal that the transmitting coil 3 receives is denoted as pumping signal, and the signal acquisition module 5 receives
Signal be denoted as reference signal.
After the transmitting coil 3 receives pumping signal, main field is generated.The main field is passing through the brain group to be measured
Disturbed magnetic field is generated after knitting.After the receiving coil 4 receives the superposition magnetic field of main field and disturbed magnetic field, detection signal is generated.
4) signal acquisition module 5 receives detection signal.
Reference signal and detection signal are passed to signal processing module by the signal acquisition module 5.
5) signal processing module 6 handles reference signal and detection signal, calculates any time t reference signal
With the phase shift θ of detection signal1Namely the magnetic induction phase shift θ between any time t superposition magnetic field and main field1。
6) signal processing module 6 is according to t1Moment is superimposed the magnetic induction phase shift θ between magnetic field and main field1, it is to be measured
Brain tissue 1t1The brain water content W at moment1With brain tissue 1t to be measured0The brain water content W at moment0Measurement system is calculated
Number k.Measurement coefficient k is as follows:
In formula, θ1For t1Moment is superimposed the magnetic induction phase shift between magnetic field and main field.W1For brain tissue 1t to be measured1When
The brain water content at quarter.W0For brain tissue 1t to be measured0The brain water content at moment.
7) t, the exciting signal source 2 are sent out to the transmitting coil 3 and the signal acquisition module 5 respectively at any time
Send identical signal.Wherein, the signal that the transmitting coil 3 receives is denoted as pumping signal, and the signal acquisition module 5 receives
To signal be denoted as reference signal.
After the transmitting coil 3 receives pumping signal, main field is generated.The main field is passing through the brain group to be measured
Disturbed magnetic field is generated after knitting.After the receiving coil 4 receives the superposition magnetic field of main field and disturbed magnetic field, detection signal is generated.
8) signal acquisition module 5 receives detection signal.
Reference signal and detection signal are passed to signal processing module by the signal acquisition module 5.
9) signal processing module 6 handles reference signal and detection signal, calculates any time t reference signal
Magnetic induction phase shift θ between the phase shift θ namely any time t superposition magnetic field and main field of detection signal.
10) signal processing module 6 according to any time t be superimposed magnetic induction phase shift θ between magnetic field and main field,
Measurement coefficient k and brain tissue 1t to be measured0The brain water content W at moment0The brain group of any time t brain tissue 1 to be measured is calculated in real time
Knit water content W.The signal processing module 6 passes to the brain water content W of any time t brain tissue 1 to be measured described aobvious
Show device 7.
The brain water content W of 1 any time of the brain tissue to be measured t is as follows:
W=k θ+W0。 (2)
In formula, W0For brain tissue 1t to be measured0The brain water content at moment.K is measurement coefficient.θ is any time t superposition
Magnetic induction phase shift between magnetic field and main field.
The display 7 shows the numerical value of the brain water content W of any time t brain tissue 1 to be measured.
Claims (5)
1. a kind of monitoring system of non-contacting brain edema mesencephalic tissue water content development, it is characterised in that: mainly include MRI at
As system (0), brain tissue to be measured (1), exciting signal source (2), transmitting coil (3), receiving coil (4), signal acquisition module (5)
With signal processing module (6) and display (7)；
The MRI imaging system (0) measures brain tissue to be measured (1) t respectively0The brain water content W at moment0And t1Moment
Brain water content W1, and by brain water content W0With brain water content W1Pass to the signal processing module (6)；
The brain tissue to be measured (1) is fixed between the transmitting coil (2) and the receiving coil (3)；
It is identical that the exciting signal source (2) sends two-way to the transmitting coil (3) and the signal acquisition module (5) respectively
Signal；Wherein, the signal that the transmitting coil (3) receives is denoted as pumping signal, what the signal acquisition module (5) received
Signal is denoted as reference signal；
After the transmitting coil (3) receives pumping signal, main field is generated；The main field is passing through the brain tissue to be measured
After generate disturbed magnetic field；After the receiving coil (4) receives the superposition magnetic field of main field and disturbed magnetic field, detection signal is generated；
The signal acquisition module (5) receives the detection signal of receiving coil transmission；
Reference signal and detection signal are passed to signal processing module by the signal acquisition module (5)；
The signal processing module (6) handles reference signal and detection signal, calculates any time t reference signal and inspection
Survey the magnetic induction phase shift θ between the phase shift θ namely any time t superposition magnetic field and main field of signal；Wherein, remember t1When
Carving the magnetic induction phase shift between the superposition magnetic field being calculated and main field is θ1；
The signal processing module (6) is according to t1Moment is superimposed the magnetic induction phase shift θ between magnetic field and main field1, brain group to be measured
Knit (1) t1The brain water content W at moment1With brain tissue to be measured (1) t0The brain water content W at moment0Measurement system is calculated
Number k；Measurement coefficient k is as follows:
In formula, θ1For t1Moment is superimposed the magnetic induction phase shift between magnetic field and main field；W1For brain tissue to be measured (1) t1Moment
Brain water content；W0For brain tissue to be measured (1) t0The brain water content at moment；
The signal processing module (6) is according to the magnetic induction phase shift θ between the superposition magnetic field any time t and main field, measurement
Coefficient k and brain tissue to be measured (1) t0The brain water content W at moment0The brain group of any time t brain tissue to be measured (1) is calculated in real time
Knit water content W；The brain water content W of any time t brain tissue to be measured (1) is passed to institute by the signal processing module (6)
State display (7)；
The brain water content W of brain tissue to be measured (1) any time t is as follows:
W=k θ+W0； (1)
In formula, W0For brain tissue to be measured (1) t0The brain water content at moment；K is measurement coefficient；θ is that any time t is superimposed magnetic
Magnetic induction phase shift between field and main field；
The display (7) shows the numerical value of the brain water content W of any time t brain tissue to be measured (1).
2. a kind of monitoring system of non-contacting brain edema mesencephalic tissue water content development according to claim 1, special
Sign is: the transmitting coil and the receiving coil are coaxial parallel coil；The transmitting coil and the receiving coil
Size and spacing are mainly adjusted according to the shapes and sizes of the brain tissue to be measured.
3. a kind of monitoring system of non-contacting brain edema mesencephalic tissue water content development according to claim 1, special
Sign is: the exciting signal source is binary channels alternating message source；Frequency by the pumping signal of the transmitting coil is
1MHz~10MHz.
4. a kind of monitoring system of non-contacting brain edema mesencephalic tissue water content development according to claim 1, special
Sign is: the brain tissue to be measured is head.
5. the monitoring system that tissue water content develops in a kind of non-contacting brain edema according to claim 1, feature
Be: the spacing of the brain tissue (1) to be measured and transmitting coil (2) is less than 10mm；The brain tissue to be measured (1) and receiving coil
(3) spacing is less than 10mm.
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Cited By (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN112656394A (en) * | 2020-12-01 | 2021-04-16 | 重庆理工大学 | Edema real-time monitoring device and method based on near-field coupling phase shift sensing technology |
| CN113133754A (en) * | 2021-04-21 | 2021-07-20 | 天津工业大学 | Non-contact magnetic induction electrical impedance scanning imaging device and imaging method |
| CN113133753A (en) * | 2021-05-21 | 2021-07-20 | 重庆理工大学 | Biological tissue blood flow real-time monitoring system and simulation monitoring system based on magnetic induction phase shift |
Citations (6)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US5995863A (en) * | 1996-12-27 | 1999-11-30 | Instituto Trentino Di Cultura | Method and an automatic system for obtaining water content and electric-permittivity maps from magnetic resonance images |
| WO2007029138A2 (en) * | 2005-09-07 | 2007-03-15 | Philips Intellectual Property & Standards Gmbh | System and method for inductively measuring the bio-impedance of a conductive tissue |
| US20100097081A1 (en) * | 2005-06-09 | 2010-04-22 | The Regents Of The University Of Califonia | Volumetric Induction Phase Shift Detection System for Determining Tissue Water Content Properties |
| CN103126671A (en) * | 2013-03-27 | 2013-06-05 | 中国人民解放军第三军医大学 | Non-contacting magnetic induction type detecting system of cerebral hemorrhage |
| CN103584858A (en) * | 2013-11-07 | 2014-02-19 | 金贵 | Contralateral-hemisphere-counteraction-based method for non-contact magnetic induction cerebral hemorrhage detection |
| CN103932705A (en) * | 2014-04-29 | 2014-07-23 | 中国人民解放军第三军医大学 | Non-contact magnetic induction cerebral hemorrhage detecting device based on feature band |
-
2018
- 2018-06-22 CN CN201810654838.0A patent/CN109091144A/en active Pending
Patent Citations (6)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US5995863A (en) * | 1996-12-27 | 1999-11-30 | Instituto Trentino Di Cultura | Method and an automatic system for obtaining water content and electric-permittivity maps from magnetic resonance images |
| US20100097081A1 (en) * | 2005-06-09 | 2010-04-22 | The Regents Of The University Of Califonia | Volumetric Induction Phase Shift Detection System for Determining Tissue Water Content Properties |
| WO2007029138A2 (en) * | 2005-09-07 | 2007-03-15 | Philips Intellectual Property & Standards Gmbh | System and method for inductively measuring the bio-impedance of a conductive tissue |
| CN103126671A (en) * | 2013-03-27 | 2013-06-05 | 中国人民解放军第三军医大学 | Non-contacting magnetic induction type detecting system of cerebral hemorrhage |
| CN103584858A (en) * | 2013-11-07 | 2014-02-19 | 金贵 | Contralateral-hemisphere-counteraction-based method for non-contact magnetic induction cerebral hemorrhage detection |
| CN103932705A (en) * | 2014-04-29 | 2014-07-23 | 中国人民解放军第三军医大学 | Non-contact magnetic induction cerebral hemorrhage detecting device based on feature band |
Cited By (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN112656394A (en) * | 2020-12-01 | 2021-04-16 | 重庆理工大学 | Edema real-time monitoring device and method based on near-field coupling phase shift sensing technology |
| CN113133754A (en) * | 2021-04-21 | 2021-07-20 | 天津工业大学 | Non-contact magnetic induction electrical impedance scanning imaging device and imaging method |
| CN113133753A (en) * | 2021-05-21 | 2021-07-20 | 重庆理工大学 | Biological tissue blood flow real-time monitoring system and simulation monitoring system based on magnetic induction phase shift |
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