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
- Publication number
- CN109091144A CN109091144A CN201810654838.0A CN201810654838A CN109091144A CN 109091144 A CN109091144 A CN 109091144A CN 201810654838 A CN201810654838 A CN 201810654838A CN 109091144 A CN109091144 A CN 109091144A
- Authority
- CN
- China
- Prior art keywords
- brain
- water content
- signal
- measured
- brain tissue
- 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
- XLYOFNOQVPJJNP-UHFFFAOYSA-N water Substances O XLYOFNOQVPJJNP-UHFFFAOYSA-N 0.000 title claims abstract description 85
- 206010048962 Brain oedema Diseases 0.000 title claims abstract description 34
- 208000006752 brain edema Diseases 0.000 title claims abstract description 33
- 238000012544 monitoring process Methods 0.000 title claims abstract description 24
- 238000011161 development Methods 0.000 title claims abstract description 15
- 210000005013 brain tissue Anatomy 0.000 claims abstract description 74
- 230000010363 phase shift Effects 0.000 claims abstract description 34
- 238000012545 processing Methods 0.000 claims abstract description 33
- 238000001514 detection method Methods 0.000 claims abstract description 29
- 230000006698 induction Effects 0.000 claims abstract description 28
- 238000005259 measurement Methods 0.000 claims abstract description 20
- 238000003384 imaging method Methods 0.000 claims abstract description 9
- 210000004556 brain Anatomy 0.000 claims description 76
- 238000005086 pumping Methods 0.000 claims description 13
- 238000007689 inspection Methods 0.000 claims description 3
- 230000005540 biological transmission Effects 0.000 claims description 2
- 238000000034 method Methods 0.000 abstract description 13
- 230000005284 excitation Effects 0.000 abstract 1
- 230000018109 developmental process Effects 0.000 description 8
- 206010008190 Cerebrovascular accident Diseases 0.000 description 4
- 208000006011 Stroke Diseases 0.000 description 4
- 238000007917 intracranial administration Methods 0.000 description 4
- 230000002490 cerebral effect Effects 0.000 description 3
- 238000009940 knitting Methods 0.000 description 3
- 206010030113 Oedema Diseases 0.000 description 2
- 230000000694 effects Effects 0.000 description 2
- 208000015181 infectious disease Diseases 0.000 description 2
- 241000208340 Araliaceae Species 0.000 description 1
- 208000022306 Cerebral injury Diseases 0.000 description 1
- 206010019909 Hernia Diseases 0.000 description 1
- 235000005035 Panax pseudoginseng ssp. pseudoginseng Nutrition 0.000 description 1
- 235000003140 Panax quinquefolius Nutrition 0.000 description 1
- 208000027418 Wounds and injury Diseases 0.000 description 1
- 230000002159 abnormal effect Effects 0.000 description 1
- 230000000740 bleeding effect Effects 0.000 description 1
- 230000006378 damage Effects 0.000 description 1
- 238000010586 diagram Methods 0.000 description 1
- 238000006073 displacement reaction Methods 0.000 description 1
- 235000008434 ginseng Nutrition 0.000 description 1
- 230000002008 hemorrhagic effect Effects 0.000 description 1
- 230000000302 ischemic effect Effects 0.000 description 1
- 230000003902 lesion Effects 0.000 description 1
- 231100000225 lethality Toxicity 0.000 description 1
- 238000000691 measurement method Methods 0.000 description 1
- 230000029052 metamorphosis Effects 0.000 description 1
- 210000005036 nerve Anatomy 0.000 description 1
- 230000001717 pathogenic effect Effects 0.000 description 1
- 230000036285 pathological change Effects 0.000 description 1
- 231100000915 pathological change Toxicity 0.000 description 1
- 230000035479 physiological effects, processes and functions Effects 0.000 description 1
- 238000004393 prognosis Methods 0.000 description 1
- 238000011002 quantification Methods 0.000 description 1
- 208000037921 secondary disease Diseases 0.000 description 1
- 230000000472 traumatic effect Effects 0.000 description 1
- 238000002604 ultrasonography Methods 0.000 description 1
- 230000002792 vascular Effects 0.000 description 1
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/05—Detecting, measuring or recording for diagnosis by means of electric currents or magnetic fields; Measuring using microwaves or radio waves
- A61B5/053—Measuring electrical impedance or conductance of a portion of the body
- A61B5/0537—Measuring body composition by impedance, e.g. tissue hydration or fat content
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/05—Detecting, measuring or recording for diagnosis by means of electric currents or magnetic fields; Measuring using microwaves or radio waves
- A61B5/055—Detecting, measuring or recording for diagnosis by means of electric currents or magnetic fields; Measuring using microwaves or radio waves involving electronic [EMR] or nuclear [NMR] magnetic resonance, e.g. magnetic resonance imaging
Landscapes
- Health & Medical Sciences (AREA)
- Life Sciences & Earth Sciences (AREA)
- Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
- Physics & Mathematics (AREA)
- Medical Informatics (AREA)
- Molecular Biology (AREA)
- Pathology (AREA)
- Engineering & Computer Science (AREA)
- Biomedical Technology (AREA)
- Heart & Thoracic Surgery (AREA)
- Radiology & Medical Imaging (AREA)
- Biophysics (AREA)
- Surgery (AREA)
- Animal Behavior & Ethology (AREA)
- General Health & Medical Sciences (AREA)
- Public Health (AREA)
- Veterinary Medicine (AREA)
- High Energy & Nuclear Physics (AREA)
- Measurement And Recording Of Electrical Phenomena And Electrical Characteristics Of The Living Body (AREA)
- Magnetic Resonance Imaging Apparatus (AREA)
Abstract
本发明公开了一种非接触的脑水肿中组织含水量发展的监测系统，主要包括MRI成像系统、待测脑组织、激励信号源、发射线圈、接收线圈、信号采集模块、信号处理模块和显示器。MRI成像系统测量待测脑组织的脑组织含水量。所述待测脑组织固定在所述发射线圈和所述接收线圈之间。所述信号处理模块对参考信号和检测信号进行处理，计算参考信号和检测信号的相位移θ。信号处理模块根据任意时刻t叠加磁场与主磁场之间的磁感应相位移θ、测量系数k和待测脑组织t0时刻的脑组织含水量W0实时计算待测脑组织的脑组织含水量W。本发明利用非接触的脑水肿中脑组织含水量发展的监测系统对脑组织含水量进行实时监测。The invention discloses a non-contact monitoring system for the development of tissue water content in cerebral edema, which mainly includes an MRI imaging system, brain tissue to be measured, an excitation signal source, a transmitting coil, a receiving coil, a signal acquisition module, a signal processing module and a display . The MRI imaging system measures the brain tissue water content of the brain tissue to be tested. The brain tissue to be measured is fixed between the transmitting coil and the receiving coil. The signal processing module processes the reference signal and the detection signal, and calculates the phase shift θ of the reference signal and the detection signal. The signal processing module calculates the brain tissue water content W of the brain tissue to be measured in real time according to the magnetic induction phase shift θ between the superimposed magnetic field and the main magnetic field at any time t, the measurement coefficient k, and the brain tissue water content W 0 of the brain tissue to be measured at time t 0 . The invention utilizes a non-contact monitoring system for the development of brain tissue water content in cerebral edema to monitor the brain tissue water content in real time.
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.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201810654838.0A CN109091144A (en) | 2018-06-22 | 2018-06-22 | A kind of monitoring system of non-contacting brain edema mesencephalic tissue water content development |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201810654838.0A CN109091144A (en) | 2018-06-22 | 2018-06-22 | A kind of monitoring system of non-contacting brain edema mesencephalic tissue water content development |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CN109091144A true CN109091144A (en) | 2018-12-28 |
Family
ID=64844926
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN201810654838.0A Pending CN109091144A (en) | 2018-06-22 | 2018-06-22 | A kind of monitoring system of non-contacting brain edema mesencephalic tissue water content development |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN109091144A (en) |
Cited By (4)
| 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 |
| 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 |
| 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 |
| CN115024708A (en) * | 2022-05-17 | 2022-09-09 | 重庆理工大学 | Detection method for evaluating CVAR based on MMNFC technology |
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 (4)
| 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 |
| CN115024708A (en) * | 2022-05-17 | 2022-09-09 | 重庆理工大学 | Detection method for evaluating CVAR based on MMNFC technology |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| Ward | Bioelectrical impedance analysis: proven utility in lymphedema risk assessment and therapeutic monitoring | |
| US10506943B2 (en) | Methods and systems for monitoring intrabody tissues | |
| Dueholm et al. | Accuracy of magnetic resonance imaging and transvaginal ultrasonography in the diagnosis, mapping, and measurement of uterine myomas | |
| CN109091144A (en) | A kind of monitoring system of non-contacting brain edema mesencephalic tissue water content development | |
| Baumer et al. | Thoracic outlet syndrome in 3T MR neurography—fibrous bands causing discernible lesions of the lower brachial plexus | |
| CN106937865B (en) | Temperature monitoring system and monitoring method capable of early warning breast lesions | |
| CN113133753B (en) | Real-time monitoring system and simulation monitoring system of biological tissue blood flow based on magnetic induction phase shift | |
| CN105147286A (en) | Cerebral hemorrhage and cerebral ischemia distinguishing system based on non-contact magnetic induction | |
| Ward | Is BIS ready for prime time as the gold standard measure | |
| US20200082926A1 (en) | Wearable Inductive Damping Sensor | |
| CN103767688A (en) | Implantable extracorporeal monitoring device of intracranial environment | |
| CN103932705B (en) | A kind of non-contact magnetic inductive cerebral hemorrhage checkout gear of feature based frequency band | |
| US20230277079A1 (en) | Methods and systems for monitoring intrabody tissues | |
| CN102727199B (en) | Brain edema change measuring method based on minimum impedance frequency | |
| CN201683898U (en) | Hydrocephalus type examining device | |
| CN202751392U (en) | Brain edema change measuring device based on minimum impedance frequency | |
| CN105769190A (en) | Device for detecting cephalophyma and encephaledema | |
| Oue et al. | Accuracy of the measurement of uterine leiomyoma by transabdominal ultrasonography | |
| Belgrado et al. | Lymphoedema: What can be measured and how... overview | |
| Takpor et al. | Advances in current techniques for monitoring the progress of child delivery | |
| RU2579617C1 (en) | Method for prediction of clinical narrow pelvis | |
| Kumar et al. | Development of a non-invasive point of care diagnostic tool for fetal monitoring using electrical impedance based approach | |
| US20240285251A1 (en) | Systems and Methods for Non-Invasive Measurement of Intracranial Pressure | |
| CN101849818B (en) | Device for checking type of cerebral edema | |
| Ali Mohammed Teniteen et al. | COMPARATIVE STUDY BETWEEN TRANSCEREBELLAR DIAMETER WITH BIPARIETAL DIAMETER AND FEMUR LENGTH OF ULTRASOUND FOR GESTATIONAL AGE MEASUREMENT IN SECOND TRIMESTER OF PREGNANCY |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| PB01 | Publication | ||
| PB01 | Publication | ||
| SE01 | Entry into force of request for substantive examination | ||
| SE01 | Entry into force of request for substantive examination | ||
| TA01 | Transfer of patent application right |
Effective date of registration: 20210106 Address after: Chongqing city Shapingba street 400038 gaotanyan No. 30 Applicant after: ARMY MEDICAL University Address before: No. 209, Zhuyuan Road, high tech Zone, Suzhou, Jiangsu, 215010 Applicant before: SUZHOU MAICIRUI MEDICAL TECHNOLOGY Co.,Ltd. |
|
| TA01 | Transfer of patent application right | ||
| WD01 | Invention patent application deemed withdrawn after publication |
Application publication date: 20181228 |
|
| WD01 | Invention patent application deemed withdrawn after publication |