CN102973260A - Noncontact magnetic sensing-type intracranial pressure monitoring device - Google Patents
Noncontact magnetic sensing-type intracranial pressure monitoring device Download PDFInfo
- Publication number
- CN102973260A CN102973260A CN2012105027497A CN201210502749A CN102973260A CN 102973260 A CN102973260 A CN 102973260A CN 2012105027497 A CN2012105027497 A CN 2012105027497A CN 201210502749 A CN201210502749 A CN 201210502749A CN 102973260 A CN102973260 A CN 102973260A
- Authority
- CN
- China
- Prior art keywords
- signal
- outfan
- frequency
- driving source
- phase
- 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.)
- Granted
Links
Images
Landscapes
- Measurement And Recording Of Electrical Phenomena And Electrical Characteristics Of The Living Body (AREA)
- Measuring And Recording Apparatus For Diagnosis (AREA)
Abstract
The invention relates to a noncontact magnetic sensing-type intracranial pressure monitoring device, which comprises an excitation source for generating an excitation signal and a reference signal, a magnetic sensing detection device surrounding a tested head and a phase discriminator, wherein the magnetic sensing detection device is connected to the output end of the excitation source, an alternating excitation magnetic field signal is generated according to an excitation signal provided by the excitation source, the excitation magnetic field signal runs through the entire tested head, the excitation magnetic field signal and a secondary magnetic field signal are superimposed together to form a superimposed magnetic field signal having phase change relative to the reference signal; the phase discriminator is used for detecting phase difference between the reference signal and the superimposed magnetic field signal, and the phase difference is used for reflecting the pressure variation of the wall of a cranial cavity caused by intracranial contents. Due to the adoption of the noncontact magnetic sensing-type intracranial pressure monitoring device, the defect that inductively coupled plasma (ICP) monitoring cannot sensitively reflect the variation of early lesion because the ICP is not increased greatly under the adjustment effect of cerebrospinal fluid and cerebral blood flow dynamics when the early lesion of the brain causes the increase of ICP can be overcome.
Description
Technical field
The invention belongs to biomedical armarium technical field, be specifically related to neural Medicine and Surgery non-contact magnetic inductive monitoring intracranial pressure device.
Background technology
The neural Medicine and Surgery common diseases such as all kinds of craniocerebral trauma, the cerebral tumor, apoplexy, cerebral infarction, cerebral ischemia, encephalitis disease, epilepsy, cephalophyma and high altitude cerebral adema, majority of cases breaks with tremendous force when falling ill, the state of an illness is critical, and mortality rate is high.These diseases are followed increasing of intracranial pressure (intracranial pressure, ICP) mostly, it be cause patient sb.'s illness took a turn for the worse, one of prognosis mala, secondary brain injury and dead common cause.Accurately, rapid, objective and easily ICP monitoring be observe that conditions of patients changes, carries out early diagnosis, determines therapeutic scheme, instructs clinical drug therapy, judgement and improve the important means of prognosis.
ICP refers to the tolerant pressure that the cranial cavity wall is produced of intracranial, take cerebrospinal fluid (cerebrospinal fluid, CSF) pressure as representative.Existing various ICP monitoring methods be the dependency that changes take tested physiological parameter and ICP as basic, have various limitation.Wound ICP monitoring method is arranged, such as in Intraventricular, the brain essence, under epidural or the cerebral dura mater, subarachnoid space, lumbar puncture method, nerve endoscope, wound brain electrical impedance monitoring etc. is arranged, existing has damage, patient's misery to cause greatly, easily the problems such as infection to human body; CT and MRI Imaging Method, existence check that price is more expensive, can't implement the problems such as bed side and the on-the-spot monitoring of first aid.Noinvasive ICP monitoring method, comprise based on ultrasonic vagina nervi optici diameter, retinal venous pressure or arterial pressure, flash visual evoked potential, tympanum displacement, bregma pressure measurement, noinvasive brain electrical impedance, Wicresoft's strain electrical measuring method, near infrared spectrum monitoring, transcranial doppler etc., because the brain early lesion causes when ICP raises, the regulating action that cerebrospinal fluid and cerebral hemodynamic are arranged, it is little that ICP is raise, and causes direct ICP monitoring can't reflect sensitively the change of early lesion.In addition, there is following point in the ICP monitoring method:
1. the patients such as heavy cranium brain injury, serious burn, infectious disease, dermatosis, skin allergy are not easy to use the contact method to guard; 2. the contact method can not be satisfying personalized and the aging crowd when personalized treatment to the demand of monitoring; 3. to lay electrode in patient head many for contact type measurement, and clinical use is inconvenient, and the activity of limiting patient increases discomfort; 4. for special populations such as special technical soldier, air force pilot, spacemans, in the time of need to monitoring under naturalness, the contact method more is not suitable for; 5. there is detection blind area in various degree in various noinvasive ICP monitorings.
For the deficiency of existing ICP monitoring method and the needs of clinical neural Medicine and Surgery disease treatment, propose a kind ofly have early lesion and Deep Lesions is highly sensitive, noncontact magnetically inductive, be convenient to the ICP monitoring method of bedside monitoring, significant to the Level of first-aid treatment that improves neural Medicine and Surgery patient.
Summary of the invention
Technical problem to be solved by this invention is to overcome the brain early lesion and causes when ICP raises, the regulating action that cerebrospinal fluid and cerebral hemodynamic are arranged, it is little that ICP is raise, cause direct ICP monitoring can't reflect sensitively the change of early lesion, and propose a kind of non-contact magnetic inductive monitoring intracranial pressure device.
The technical scheme that solves the problems of the technologies described above is as follows:
A kind of non-contact magnetic inductive monitoring intracranial pressure device comprises for the driving source that generates pumping signal and reference signal; And
A magnetic induction measurement device that is looped around around the tested head, this magnetic induction measurement device is connected in described driving source outfan, the pumping signal that the magnetic induction measurement device provides according to driving source produces the excitation field signal of alternation, the excitation field signal passes whole tested head, in tested head, produce eddy current, this eddy current produces again a secondary magnetic field signal, and excitation field signal and secondary magnetic field signal are superimposed and form the stack field signal with respect to reference signal generation phase change; And
Phase discriminator, the input of this phase discriminator is connected with the outfan of described driving source and the outfan of described magnetic induction measurement device respectively, phase discriminator detects the phase contrast of described reference signal and stack field signal, and this phase contrast is used for the tolerant pressure that the cranial cavity wall is produced of reflection intracranial to be changed.
Adopted such scheme, non-contact magnetic inductive monitoring intracranial pressure device of the present invention, the pumping signal of sending by a driving source, make the magnetic induction measurement device produce the excitation field signal of alternation, the excitation field signal passes whole tested head, in tested head, produce eddy current, eddy current produces again the another one field signal, be called the secondary magnetic field signal, former excitation field and the secondary magnetic field signal field signal that superposes that is superimposed, (phase place of this reference signal is identical with the phase place of pumping signal to the reference signal that this stack field signal sends with respect to driving source, so can replace pumping signal) phase generate change, detect this phase contrast with a multifrequency phase discriminator, the proportional relation of whole Conductivity of Brain of this phase contrast and tested head, and whole Conductivity of Brain and pathological changes, the volume of cerebrospinal fluid and blood is relevant, and intracranial volume directly affects the tolerant pressure that the cranial cavity wall is produced of ICP(intracranial).Therefore, can be by detecting the variation of the phase contrast reflection ICP between stack field signal and the reference signal.
Although for the brain early lesion, for example cerebral edema, cerebral hemorrhage hour, cerebrospinal fluid and cerebral blood flow can pass through the compensation regulating intracranial pressure, so that intracranial pressure raises not quite; But because cranial cavity is rigidity, when cranial cavity content volume increases to a critical point, cerebrospinal fluid and cerebral blood flow can't be regulated again, the at this moment increase of intracranial volume trace, intracranial pressure is increased severely, increase the weight of brain displacement and cerebral hernia, the depleted crisis of center of origin, this is breakneck, often has little time treatment this moment.Therefore intracranial pressure-PRESSURE-VOLUME RELATION is similar to an exponential curve, and adult's critical point scope is generally 20～25 mmHg, and child's critical point scope is lower.Can find out that detect the variation of the state of an illness when intracranial pressure does not reach critical point the state of an illness is judged to have higher-value, current ICP detection method can't detect the before variation of intracranial lesion of critical point, and can reflect more delicately early lesion by the present invention.Therefore, non-contact magnetic inductive monitoring intracranial pressure device of the present invention can reflect because the variation of the whole brain electrical conductivity that the regulating action of early lesion, cerebrospinal fluid and cerebral hemodynamic causes, thereby realizes the monitoring of early lesion.
In addition, during owing to Intracerebral lesion, the adjusting of cerebrospinal fluid and cerebral blood flow is the relationship change by approximate cube of Deep Lesions, and has synergistic effect with lesion volume, and current I CP detection method is insensitive to less Intracerebral lesion.Can reflect the variation of the whole brain electrical conductivity that is caused by less Deep Lesions by the present invention, improve the sensitivity to Intracerebral lesion.
Further, driving source is the multifrequency sine driving source, and this multifrequency sine driving source comprises the input equipment for user's setpoint frequency and power, and the single-chip microcomputer that is connected in described input equipment outfan, and the signal that provides according to input equipment sends control instruction; And the field programmable gate array that is connected in the single-chip microcomputer outfan, the control clock signal occurs after the control instruction of reception single-chip microcomputer; And the crystal oscillator that produces clock frequency; And the phaselocked loop that is connected with crystal oscillator, the clock frequency signal of crystal oscillator output is carried out frequency multiplication obtain reference clock; And be connected in Direct Digital Synthesizer with field programmable gate array and phaselocked loop outfan respectively, the control sequential that provides according to field programmable gate array, and according to the reference clock that phaselocked loop provides, generate frequency and power signal that the user sets; And the switch frequency-selecting filter that is connected in the Direct Digital Synthesizer outfan, frequency and power signal that Direct Digital Synthesizer is exported are converted to reference signal output; And the power amplification and the adapter that are connected in switch frequency-selecting filter outfan, the reference signal of switch frequency-selecting filter output amplified and mate as pumping signal export.This multifrequency sine driving source has used control and the synchronizing function of direct digital frequency synthesizer (DDS chip) and powerful field programmable gate array (fpga chip), so that the frequency stability of this driving source output signal can reach 10
-8, apparently higher than the signal of domestic other unit use.
Further, described multifrequency sine driving source is used for generating 200KHz, 1MHz, and 10.7MHz, 21.4MHz, 30.85MHz, 40.05MHz, 49.95MHz be the standard sine signal of totally 7 frequencies, and the output signal power range of accommodation is: 10mW-2W.This multifrequency sine driving source has the characteristics of multifrequency output and high-power adjusting, and this also is the characteristics that other unit driving source circuit is not had.Filter out by experiment 1MHz, 10.7MHz, a 21.4MHz3 sinusoidal excitation frequency, to adapt to the different requirements of clinical neural Medicine and Surgery disease surveillance, for example, dissimilar cerebral hemorrhages, cerebral edema, the cerebral tumor are distinguished.
Further, described driving source comprises the crystal oscillator that produces clock frequency; And the power divider that is connected in the crystal oscillator outfan, the clock frequency that crystal oscillator is generated is divided into first via clock frequency and the second tunnel clock frequency; And the first amplitude adjustor that is connected in the power divider outfan, the first via clock frequency of Modulating Power allotter output becomes reference signal; And the second amplitude adjustor that is connected in the power divider outfan, the second tunnel clock frequency of Modulating Power allotter output; And the power amplifier that is connected in the second amplitude adjustor outfan, the output signal that will come from the second amplitude adjustor is amplified and is become pumping signal.
Further, described magnetic induction measurement device is comprised of spaced apart excitation coil and magnetic test coil, and excitation coil and magnetic test coil are to be parallel to each other and at the coaxial outer surface that is fixed on the lucite sleeve.The induced field that any position pathological changes causes in the tested head changes and can be detected, and has higher monitoring sensitivity, can detect the rabbit intracranial and be changed by the hemorrhage ICP that causes of 0.8ml.The advantage of magnetic induction measurement device of the present invention is: 1, noncontact, and without wound (current I CP detection method need to be inserted sensor head in the cranium brain).2, highly sensitive, can detect the ICP variation that very little amount of bleeding causes, and the result and the ICP that detect are dependency.
Further, described phase discriminator comprises the first wave filter, and the reference signal of driving source output is carried out pre-filtering; And the first gain-programmed amplifier that is connected in the first filter output, nursed one's health in the input range of A/D converter to the reference signal after the pre-filtering by the digital programmable gain amplifier according to the gain that the user arranges; And second wave filter, the stack field signal of magnetic induction measurement device output is carried out pre-filtering; And the second gain-programmed amplifier that is connected in the second filter output, nursed one's health in the input range of A/D converter to the stack field signal after the pre-filtering by the digital programmable gain amplifier according to the gain that the user arranges; And respectively with the first gain-programmed amplifier be connected the A/D converter that gain-programmed amplifier is connected, will come from the first gain-programmed amplifier and the second gain-programmed amplifier is converted to digital signal; And the data acquisition unit that is connected with A/D converter, the two paths of signals that A/D converter is exported carries out synchronous acquisition; And the field programmable gate array that is connected with data acquisition unit, for the each several part circuit provides work schedule and as interface circuit; And the DSP that is connected with field programmable gate array, be used for finishing fast Fourier transform, calculate the phase contrast of input two paths of signals; And the synchronous DRAM that is connected with DSP, during the DSP deal with data data are read from SDRAM, carry out fast Fourier transform, obtain phase data; And the display that is connected with DSP, the phase data that DSP reentries is sent to display and shows in real time, and draws the phase contrast curve.Phase discriminator of the present invention adopts independently DSP and field programmable gate array (fpga chip) data acquisition and algorithm process, has reached the characteristics of high accuracy and miniaturization.Phase discriminator of the present invention can reach 0.02 ° precision of phase discrimination, meets or exceeds external instrument fully, has more low-cost and portable characteristics.
Further, described phase discriminator also comprises a clock module that is connected with field programmable gate array, and the synchronised clock that field programmable gate array provides by clock module for data acquisition unit provides sampling clock, and provides data transfer clock for DSP.Can guarantee in this way the synchronous processing of reference signal and stack field signal.
Further, described phase discriminator also comprises an external flash that is connected with DSP, and 12 hours phase data stores among the RAM or external flash of DSP inside.DSP can store the real time data that collects in the external flash into by dma bus, during the DSP deal with data data is read from external flash, carries out fast Fourier transform, thereby obtains phase data.
Description of drawings
Fig. 1 is the circuit block diagram of non-contact magnetic inductive monitoring intracranial pressure device of the present invention;
Fig. 2 is the circuit block diagram of the preferred embodiment of driving source among Fig. 1;
Fig. 3 is the circuit block diagram of another embodiment of driving source among Fig. 1;
Fig. 4 is the circuit block diagram of the another embodiment of driving source among Fig. 1;
Fig. 5 is the structural representation of the preferred embodiment of magnetic induction measurement device;
Fig. 6 is the circuit block diagram of the preferred embodiment that phase discriminator swashs among Fig. 1;
Fig. 7 is the intracranial pressure of zoopery acquisition and the corresponding relation of magnetic induction phase shift relation curve;
10 is driving source, 100 is the multifrequency sine driving source, 101 is input equipment, and 102 is single-chip microcomputer, and 103 is field programmable gate array, 104 is crystal oscillator, 105 is phaselocked loop, and 106 is Direct Digital Synthesizer, and 107 is the switch frequency-selecting filter, 108 are power amplification and adapter, and 109 is display; 110 is crystal oscillator, and 111 is power divider, and 112 is the first amplitude adjustor, and 113 is the second amplitude adjustor, and 114 is power amplifier;
20 is the magnetic induction measurement device, and 200 is excitation coil, and 201 is magnetic test coil;
300 is the first wave filter, 301 is the first gain-programmed amplifier, and 302 is the second wave filter, and 303 is the second gain-programmed amplifier, 304 is A/D converter, 305 is data acquisition unit, and 306 is field programmable gate array, and 307 is DSP, 308 is synchronous DRAM, 309 is display, and 310 is clock module, and 311 is external flash.
The specific embodiment
With reference to Fig. 1, non-contact magnetic inductive monitoring intracranial pressure device of the present invention is comprised of driving source 10, magnetic induction measurement device 20 and a phase discriminator 30 that is looped around around the tested head, and the below is elaborated to every part:
See figures.1.and.2, driving source 10 is used for generating pumping signal and reference signal.Driving source of the present invention is preferably multifrequency sine driving source 100, this multifrequency sine driving source is used for generating 200KHz, 1MHz, 10.7MHz, 21.4MHz, 30.85MHz, 40.05MHz, 49.95MHz the standard sine signal of totally 7 frequencies, the output signal power range of accommodation is: 10mW-2W, the frequency stability of signal reaches 10
-8Multifrequency sine driving source 100 comprises that input equipment 101 is keyboard or touch screen for the input equipment 101 of user's setpoint frequency and power, and the input equipment in the present embodiment is keyboard.And the single-chip microcomputer 102 that is connected in described input equipment outfan, single-chip microcomputer 102 sends control instruction according to the signal that input equipment provides, and single-chip microcomputer 102 usefulness things are controlled the work of whole multifrequency sine driving source.And the field programmable gate array (fpga chip among Fig. 2) 103 that is connected in the single-chip microcomputer outfan, the control clock signal occurs after the control instruction of field programmable gate array 103 reception single-chip microcomputers.And the crystal oscillator 104 that produces clock frequency.And the phaselocked loop that is connected with crystal oscillator (the PLL chip among Fig. 2) 105, the clock frequency signal that phaselocked loop 105 is exported crystal oscillator carries out frequency multiplication and obtains reference clock; Phaselocked loop 105 carries out frequency multiplication with the 100MHz clock frequency of crystal oscillator output, obtains the clock frequency signal of 800MHz as the reference clock of Direct Digital Synthesizer (the DDS chip among Fig. 2).And be connected in Direct Digital Synthesizer 106 with field-programmable gate array 103 row and phaselocked loop 105 outfans respectively, the control sequential that provides according to field programmable gate array, and according to the reference clock that phaselocked loop provides, generate frequency and power signal that the user sets.And the switch frequency-selecting filter 107 that is connected in the Direct Digital Synthesizer outfan, frequency and power signal that Direct Digital Synthesizer is exported are converted to reference signal output; And the power amplification and the adapter 108 that are connected in switch frequency-selecting filter outfan, the reference signal of switch frequency-selecting filter output amplified and mate as pumping signal export.Described multifrequency sine driving source also comprises a display (LCD among Fig. 2) 109 that is connected in the single-chip microcomputer outfan, is used for showing frequency and the power parameter that is used for Set For Current.
Above-mentioned multifrequency sine driving source circuit working process is: after single-chip microcomputer 102 received to do for oneself the order of input equipment 101, controlling field programmable gate array 103 provided various control sequential for Direct Digital Synthesizer 106 on the one hand.Frequency and power parameter with Set For Current outputs to display 109 demonstrations on the one hand.Direct Digital Synthesizer 106 generates frequency and power stage that the user sets under the 800MHz reference clock and field programmable gate array 103 control sequential effects that phaselocked loop 105 provides.The signal of Direct Digital Synthesizer 106 output carries out filtering through the switch frequency-selecting filter again and generates a LUSHEN and examine signal.Reference signal is exported as one tunnel pumping signal through three grades of power amplification circuits and power matching circuit.This driving source finally can be exported 200KHz, 1MHz, and 10.7MHz, 21.4MHz, 30.85MHz, 40.05MHz, 49.95MHz be the standard sine signal of totally 7 frequencies.The frequency stability of signal reaches 10
-8The pumping signal power regulating range of output is: 10mW-2W.The reference signal amplitude of every kind of frequency is fixed, and the phase contrast between reference signal and the pumping signal immobilizes.
With reference to Fig. 1 and Fig. 3, driving source of the present invention can also be the driving source of crystal oscillator device composition, and concrete structure is: described driving source comprises the crystal oscillator 110 that produces clock frequency; And the power divider 111 that is connected in the crystal oscillator outfan, the clock frequency that crystal oscillator is generated is divided into first via clock frequency and the second tunnel clock frequency; And the first amplitude adjustor 112 that is connected in the power divider outfan, the first via clock frequency of Modulating Power allotter output becomes reference signal; And the second amplitude adjustor 113 that is connected in the power divider outfan, the second tunnel clock frequency of Modulating Power allotter output; And the power amplifier 114 that is connected in the second amplitude adjustor outfan, the output signal that will come from the second amplitude adjustor is amplified and is become pumping signal.
With reference to Fig. 1 and Fig. 4, driving source of the present invention is not limited to above-described embodiment, can also adopt structure as shown in Figure 4, the clock frequency signal that crystal oscillator generates divides two-way output, one tunnel basis of adopting the Direct Digital Frequency Synthesizers mouth to produce as signal, the signal of output after buffer amplifier carries out impedance transformation, is failed reference signal again through filter filtering.The basis that another road adopts Direct Digital Frequency Synthesizers mouth to produce as signal, the signal of output be through filter filtering, carries out impedance transformation through buffer amplifier again and amplify by power amplifier and obtain pumping signal.
With reference to Fig. 1 and Fig. 5, the magnetic induction measurement device 20 among the present invention, magnetic induction measurement device are used for being looped around around the tested head.This magnetic induction measurement device 20 is connected in the outfan of described driving source 10, the pumping signal that the magnetic induction measurement device provides according to driving source produces the excitation field signal of alternation, the excitation field signal passes whole tested head, in tested head, produce eddy current, this eddy current produces again a secondary magnetic field signal, and excitation field signal and secondary magnetic field signal are superimposed and form the stack field signal with respect to reference signal generation phase change.Described magnetic induction measurement device is comprised of spaced apart excitation coil 200 and magnetic test coil 201, and excitation coil 200 and magnetic test coil 201 are to be parallel to each other and at the coaxial outer surface that is fixed on lucite sleeve (machine glass sleeve is not shown in the drawings).Excitation coil and magnetic test coil form by the coiling of copper enamel-covered wire, the diameter of excitation coil and magnetic test coil is 10-30cm, the diameter of two coils preferably is 25cm, excitation coil and magnetic test coil spacing distance are 6-9cm, excitation coil and magnetic test coil spacing distance are preferably 8.5 cm, and up and down the 5cm adjustable space are arranged respectively.Magnetic induction measurement device 20 of the present invention has higher monitoring sensitivity, tests with rabbit, can detect the rabbit intracranial and be changed by the hemorrhage ICP that causes of 0.8ml.
With reference to Fig. 1 and Fig. 6, phase discriminator 30 is the multifrequency phase discriminator, the input of phase discriminator 30 is connected with the outfan of described driving source 10 and the outfan of described magnetic induction measurement device 20 respectively, phase discriminator detects the phase contrast of described reference signal and stack field signal, and this phase contrast is used for the tolerant pressure that the cranial cavity wall is produced of reflection intracranial to be changed.Phase discriminator of the present invention preferably includes the first wave filter 300, and the reference signal of driving source output is carried out pre-filtering, and the first wave filter 300 is comprised of low pass filter and band filter.And the first gain-programmed amplifier 301 that is connected in the first filter output, the reference signal after the pre-filtering is nursed one's health in the input range of A/D converter by the digital programmable gain amplifier according to the gain that the user arranges.And second wave filter 302, the stack field signal of magnetic induction measurement device output is carried out pre-filtering, the second wave filter 302 also is comprised of low pass filter and band filter.And the second gain-programmed amplifier 303 that is connected in the second filter output, the stack field signal after the pre-filtering is nursed one's health in the input range of A/D converter by the digital programmable gain amplifier according to the gain that the user arranges.And respectively with the first gain-programmed amplifier 301 be connected the A/D converter 304 that gain-programmed amplifier 303 is connected, will come from the first gain-programmed amplifier and the second gain-programmed amplifier is converted to digital signal.And the data acquisition unit 305 that is connected with A/D converter, the two paths of signals that A/D converter is exported carries out synchronous acquisition; And the field programmable gate array 306 that is connected with data acquisition unit, for the each several part circuit provides work schedule and as interface circuit; And the DSP307 that is connected with field programmable gate array (fpga chip among Fig. 6), be used for finishing fast Fourier transform, calculate the phase contrast of input two paths of signals.And the synchronous DRAM 308 that is connected with DSP, during the DSP deal with data data are read from synchronous DRAM (the SDRAM chip Fig. 6) 308, carry out fast Fourier transform, obtain phase data.And the display 309 that is connected with DSP, the phase data that DSP reentries is sent to display (LCD among Fig. 6) and shows in real time, and draws the phase contrast curve.Described phase discriminator also comprises a clock module 310 that is connected with field programmable gate array 306, and the synchronised clock that field programmable gate array provides by clock module for data acquisition unit provides sampling clock, and provides data transfer clock for DSP.Described phase discriminator comprises that also 311,12 hours phase data of an external flash that is connected with DSP (the Flash chip among Fig. 6) stores among the RAM or external flash of DSP inside.In addition, DSP can also output to personal computer by the RS232 interface.The control that keyboard 312 is used for whole phase discriminator.
Reference signal and the stack field signal of two-way input same frequency carry out pre-filtering by each self-corresponding wave filter respectively.Signal after the pre-filtering is nursed one's health in the input range of A/D converter by the digital programmable gain amplifier according to the gain that the user arranges.By data acquisition unit two paths of signals is carried out synchronous acquisition, be sent to field programmable gate array.Field programmable gate array is by giving DSP with the SPORT interface logic of DSP with sampled digital signal, and DSP carries out fast Fourier transform, obtains phase data.DSP is sent to display with phase data again and shows in real time, and draws the phase contrast curve.
In addition, phase discriminator 30 is not limited to embodiment shown in Figure 6, can also adopt such as frequency reducing lock-in amplifier method, integrated phase demodulation chip and based on the software technology of phase discrimination of virtual instrument.The below is introduced these several phase demodulation methods:
The frequency reducing lock-in amplifier is the method for commonly using, the signal of magnetic test coil is amplified through differential amplifier, carry out mixing with the signal near driving frequency, by mixing the high frequency frequency is dropped to certain Frequency, be input to lock-in amplifier through low-pass filtering and Hyblid Buffer Amplifier; Reference signal from the excitation coil end obtains also by behind frequency reducing, low-pass filtering and the Hyblid Buffer Amplifier, is input to the reference edge of lock-in amplifier; Detection signal after the frequency reducing and reference signal are through lock-in amplifier, and the real part of output detection signal and imaginary part component perhaps deposit computer in through the A/D converter conversion, can calculate the information of representative amplitude and phase place.Phase drift was often larger when lock-in amplifier was operated in upper frequency, and its inside locks the measuring speed that has limited system with synchronizing process frequently, neither Complete Synchronization between the inner synthetic reference signal of lock-in amplifier and the external reference signal.In addition, the phase locking technique complex structure, system is huge, measures dumbly, is unfavorable for miniaturization.Present Domestic mainly adopts the lock-in amplifier instrument of external import to carry out phase demodulation, and representative products has the SR830 of research department, U.S. Stamford development, SR844 lock-in amplifier.
Current integrated phase demodulation chip has AD8302 and SYPD-1 etc., AD8302 phase contrast resolution rate only has 0.5 °, and SYPD-1 resolution is about 0.05 °, when the amplitude of variation of input signal, the output signal drift is very large, so the problem of phase demodulation chip maximum is that output signal is unstable.
Software technology of phase discrimination also is digital phase detection, is a kind of new development trend of current phase demodulation.Behind the amplification of detection signal process low noise narrow-band amplifier, crystal filter frequency-selecting and the high-gain narrow-band amplifier, after converting digital signal to by AD, re-use various processors digital signal is carried out correlation demodulation, obtain real part and the imaginary part of detection signal, obtain phase place and amplitude information.The software technology of phase discrimination method has higher precision and larger motility, increases but utilize computer and virtual instrument to carry out the software technology of phase discrimination cost, is unfavorable for equally miniaturization.
The preferred phase discriminator of the present invention (embodiment shown in Figure 6) is considered the pluses and minuses of above-mentioned phase detecting method, adopts independently DSP and fpga chip data acquisition and algorithm process, has reached the characteristics of high accuracy and miniaturization.This phase discriminator can reach 0.02 ° precision of phase discrimination, meets or exceeds external instrument fully, has more low-cost and portable characteristics.
System of the present invention passes through to measure the variation of the magnetic induction phase contrast (Magnetic Induction Phase Shift, MIPS) in 6 Cerebral Hemorrhage of Rabbit situations, and compares research with Intraventricular ICP monitoring.Mainly comprise: multifrequency sine driving source, magnetic induction measurement device, multifrequency phase discriminator, rabbit platform, physiological signal Acquisition Instrument and syringe pump etc.; The major parameter that gathers has MIPS, electrocardiosignal (ECG), Intraventricular ICP and arterial pressure (APP) etc.By rabbit internal capsule hemorrhage model, obtain the corresponding relation of Intraventricular ICP monitoring and non-contact magnetic inductive phase difference measurement, as shown in Figure 7.Noncontact magnetically inductive ICP monitoring method major advantage of the present invention is: the noncontact that realizes ICP is monitored without wound; The highly sensitive of early lesion monitored in traditional Intraventricular ICP; Solved the problem that serious brain trauma, dermatosis and skin allergy, the infectious victims can't be pasted contact electrode.
At last, (patent No. is: ZL200510042937.6) compare with non-contact magnetic inductive monitoring intracranial pressure device of the present invention and The Fourth Military Medical University's patent, different at aspects such as monitoring parameter, excitation detection mode, energisation mode, monitoring target, the scope of applications, be embodied in: 1. The Fourth Military Medical University's patent obtains the distribution of tested head electrical conductivity by area monitoring, and the present invention monitors the whole Conductivity of Brain of tested head; 2. The Fourth Military Medical University's patent adopts multiple activation magnetic test coil structure, and the present invention adopts single excitation magnetic test coil structure, and excitation magnetic test coil diameter is greater than tested head diameter; 3. The Fourth Military Medical University's patent adopts the single-frequency energisation mode, and the present invention adopts the multi-frequency excitation mode; 4. the distribution of conductivity that causes of The Fourth Military Medical University's patent monitor cerebral edema changes, and the present invention monitors the variation of whole cerebrospinal fluid and cerebral blood flow; 5. The Fourth Military Medical University's patent is limited to the cerebral edema monitoring, and the present invention is applicable to the ICP monitoring of various common neural Medicine and Surgery diseases.
Claims (10)
1. a non-contact magnetic inductive monitoring intracranial pressure device is characterized in that, comprises for the driving source that generates pumping signal and reference signal; And
A magnetic induction measurement device that is looped around around the tested head, this magnetic induction measurement device is connected in described driving source outfan, the pumping signal that the magnetic induction measurement device provides according to driving source produces the excitation field signal of alternation, the excitation field signal passes whole tested head, in tested head, produce eddy current, this eddy current produces again a secondary magnetic field signal, and excitation field signal and secondary magnetic field signal are superimposed and form the stack field signal with respect to reference signal generation phase change; And
Phase discriminator, the input of this phase discriminator is connected with the outfan of described driving source and the outfan of described magnetic induction measurement device respectively, phase discriminator detects the phase contrast of described reference signal and stack field signal, and this phase contrast is used for the tolerant pressure that the cranial cavity wall is produced of reflection intracranial to be changed.
2. noncontact magnetically inductive monitoring intracranial pressure device according to claim 1 is characterized in that, driving source is the multifrequency sine driving source, and this multifrequency sine driving source comprises the input equipment for user's setpoint frequency and power, and
Be connected in the single-chip microcomputer of described input equipment outfan, the signal that provides according to input equipment sends control instruction; And
Be connected in the field programmable gate array of single-chip microcomputer outfan, the control clock signal occurs after the control instruction of reception single-chip microcomputer; And
Produce the crystal oscillator of clock frequency; And
The phaselocked loop that is connected with crystal oscillator carries out frequency multiplication with the clock frequency signal of crystal oscillator output and obtains reference clock; And
Be connected in Direct Digital Synthesizer with field programmable gate array and phaselocked loop outfan respectively, the control sequential that provides according to field programmable gate array, and according to the reference clock that phaselocked loop provides, generate frequency and power signal that the user sets; And
Be connected in the switch frequency-selecting filter of Direct Digital Synthesizer outfan, frequency and power signal that Direct Digital Synthesizer is exported are converted to reference signal output; And
Be connected in power amplification and the adapter of switch frequency-selecting filter outfan, the reference signal of switch frequency-selecting filter output amplified and mated as pumping signal export.
3. noncontact magnetically inductive monitoring intracranial pressure device according to claim 2 is characterized in that, described multifrequency sine driving source also comprises a display that is connected in the single-chip microcomputer outfan, is used for showing frequency and the power parameter that is used for Set For Current.
4. noncontact magnetically inductive monitoring intracranial pressure device according to claim 2, it is characterized in that, described multifrequency sine driving source is used for generating 200KHz, 1MHz, 10.7MHz, 21.4MHz, 30.85MHz, 40.05MHz 49.95MHz is the standard sine signal of totally 7 frequencies, the output signal power range of accommodation is: 10mW-2W.
5. noncontact magnetically inductive monitoring intracranial pressure device according to claim 1 is characterized in that described driving source comprises the crystal oscillator that produces clock frequency; And
Be connected in the power divider of crystal oscillator outfan, the clock frequency that crystal oscillator is generated is divided into first via clock frequency and the second tunnel clock frequency; And
Be connected in the first amplitude adjustor of power divider outfan, the first via clock frequency of Modulating Power allotter output becomes reference signal; And
Be connected in the second amplitude adjustor of power divider outfan, the second tunnel clock frequency of Modulating Power allotter output; And
Be connected in the power amplifier of the second amplitude adjustor outfan, the output signal that will come from the second amplitude adjustor is amplified and is become pumping signal.
6. noncontact magnetically inductive monitoring intracranial pressure device according to claim 1, it is characterized in that, described magnetic induction measurement device is comprised of spaced apart excitation coil and magnetic test coil, and excitation coil and magnetic test coil are to be parallel to each other and at the coaxial outer surface that is fixed on the lucite sleeve.
7. noncontact magnetically inductive monitoring intracranial pressure device according to claim 5, it is characterized in that, excitation coil and magnetic test coil form by the coiling of copper enamel-covered wire, and the diameter of excitation coil and magnetic test coil is 10-30cm, and excitation coil and magnetic test coil spacing distance are 6-9cm.
8. noncontact magnetically inductive monitoring intracranial pressure device according to claim 1 is characterized in that described phase discriminator comprises the first wave filter, and the reference signal of driving source output is carried out pre-filtering; And
Be connected in the first gain-programmed amplifier of the first filter output, nursed one's health in the input range of A/D converter to the reference signal after the pre-filtering by the digital programmable gain amplifier according to the gain that the user arranges; And
The second wave filter, the stack field signal that the magnetic induction measurement device is exported carries out pre-filtering; And
Be connected in the second gain-programmed amplifier of the second filter output, nursed one's health in the input range of A/D converter to the stack field signal after the pre-filtering by the digital programmable gain amplifier according to the gain that the user arranges; And
Respectively with the first gain-programmed amplifier be connected the A/D converter that gain-programmed amplifier is connected, will come from the first gain-programmed amplifier and the second gain-programmed amplifier is converted to digital signal; And
The data acquisition unit that is connected with A/D converter, the two paths of signals that A/D converter is exported carries out synchronous acquisition; And
The field programmable gate array that is connected with data acquisition unit is for the each several part circuit provides work schedule and as interface circuit; And
The DSP that is connected with field programmable gate array is used for finishing fast Fourier transform, calculates the phase contrast of input two paths of signals; And
The synchronous DRAM that is connected with DSP is read data during the DSP deal with data from SDRAM, carry out fast Fourier transform, obtains phase data; And
The phase data that the display that is connected with DSP, DSP are reentried is sent to display and shows in real time, and draws the phase contrast curve.
9. noncontact magnetically inductive monitoring intracranial pressure device according to claim 8, it is characterized in that, described phase discriminator also comprises a clock module that is connected with field programmable gate array, the synchronised clock that field programmable gate array provides by clock module, for data acquisition unit provides sampling clock, and provide data transfer clock for DSP.
10. noncontact magnetically inductive monitoring intracranial pressure device according to claim 8 is characterized in that, described phase discriminator also comprises an external flash that is connected with DSP, and 12 hours phase data stores among the RAM or external flash of DSP inside.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201210502749.7A CN102973260B (en) | 2012-11-30 | 2012-11-30 | Noncontact magnetic sensing-type intracranial pressure monitoring device |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201210502749.7A CN102973260B (en) | 2012-11-30 | 2012-11-30 | Noncontact magnetic sensing-type intracranial pressure monitoring device |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CN102973260A true CN102973260A (en) | 2013-03-20 |
| CN102973260B CN102973260B (en) | 2014-09-10 |
Family
ID=47847816
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN201210502749.7A Expired - Fee Related CN102973260B (en) | 2012-11-30 | 2012-11-30 | Noncontact magnetic sensing-type intracranial pressure monitoring device |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN102973260B (en) |
Cited By (12)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| 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 |
| CN103344835A (en) * | 2013-07-02 | 2013-10-09 | 富勇 | Magnetic induction measuring method |
| CN103584858A (en) * | 2013-11-07 | 2014-02-19 | 金贵 | Contralateral-hemisphere-counteraction-based method for non-contact magnetic induction cerebral hemorrhage detection |
| CN103598883A (en) * | 2013-12-03 | 2014-02-26 | 中国人民解放军第三军医大学 | Intracranial pressure monitoring method based on magnetic induction phase difference change |
| CN103610452A (en) * | 2013-12-03 | 2014-03-05 | 中国人民解放军第三军医大学 | Non-contact magnetic induction type pulse detection method |
| CN103860154A (en) * | 2014-02-27 | 2014-06-18 | 中国人民解放军第三军医大学 | Non-contact type wearable type cardiorespiratory activity device based on magnetic induction |
| 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 |
| TWI509242B (en) * | 2014-12-15 | 2015-11-21 | Ind Tech Res Inst | Non-contact eddy-current detecting device and controlling method thereof |
| CN106361320A (en) * | 2016-09-26 | 2017-02-01 | 江苏爱思普医疗科技有限公司 | Minimally-invasive intracranial pressure and intracranial temperature monitoring system and probe zeroing method |
| 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 |
| CN113288102A (en) * | 2021-06-11 | 2021-08-24 | 中国人民解放军陆军军医大学 | System for monitoring cerebral blood flow without wound |
| TWI781897B (en) * | 2022-04-07 | 2022-10-21 | 國立臺灣科技大學 | Physiological signal detection system |
Citations (8)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US5388583A (en) * | 1993-09-01 | 1995-02-14 | Uab Vittamed | Method and apparatus for non-invasively deriving and indicating of dynamic characteristics of the human and animal intracranial media |
| US5617873A (en) * | 1994-08-25 | 1997-04-08 | The United States Of America As Represented By The Administrator, Of The National Aeronautics And Space Administration | Non-invasive method and apparatus for monitoring intracranial pressure and pressure volume index in humans |
| US6117089A (en) * | 1995-04-25 | 2000-09-12 | The Regents Of The University Of California | Method for noninvasive intracranial pressure measurement |
| WO2001054584A1 (en) * | 1999-01-27 | 2001-08-02 | The Government Of The United States As Represented By The Administrator Of The National Aeronautics And Space Administration | Ultrasonic apparatus and technique to measure changes in intracranial pressure |
| US20030191409A1 (en) * | 2002-04-04 | 2003-10-09 | National Aeronautics And Space Administration | Method and apparatus for determining changes in intracranial pressure utilizing measurement of the circumferential expansion or contraction of a patient's skull |
| WO2008005440A2 (en) * | 2006-06-30 | 2008-01-10 | University Of Illinois | Monitoring and controlling hydrocephalus |
| CN102670252A (en) * | 2012-05-31 | 2012-09-19 | 重庆朗普科技有限公司 | Intracranial pressure non-invasive measuring method and system |
| 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 |
-
2012
- 2012-11-30 CN CN201210502749.7A patent/CN102973260B/en not_active Expired - Fee Related
Patent Citations (8)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US5388583A (en) * | 1993-09-01 | 1995-02-14 | Uab Vittamed | Method and apparatus for non-invasively deriving and indicating of dynamic characteristics of the human and animal intracranial media |
| US5617873A (en) * | 1994-08-25 | 1997-04-08 | The United States Of America As Represented By The Administrator, Of The National Aeronautics And Space Administration | Non-invasive method and apparatus for monitoring intracranial pressure and pressure volume index in humans |
| US6117089A (en) * | 1995-04-25 | 2000-09-12 | The Regents Of The University Of California | Method for noninvasive intracranial pressure measurement |
| WO2001054584A1 (en) * | 1999-01-27 | 2001-08-02 | The Government Of The United States As Represented By The Administrator Of The National Aeronautics And Space Administration | Ultrasonic apparatus and technique to measure changes in intracranial pressure |
| US20030191409A1 (en) * | 2002-04-04 | 2003-10-09 | National Aeronautics And Space Administration | Method and apparatus for determining changes in intracranial pressure utilizing measurement of the circumferential expansion or contraction of a patient's skull |
| WO2008005440A2 (en) * | 2006-06-30 | 2008-01-10 | University Of Illinois | Monitoring and controlling hydrocephalus |
| CN102670252A (en) * | 2012-05-31 | 2012-09-19 | 重庆朗普科技有限公司 | Intracranial pressure non-invasive measuring method and system |
| 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 |
Non-Patent Citations (1)
| Title |
|---|
| 张欣等: "基于PC-MRI的无创测量颅内压方法", 《中国医学影像技术》, 31 December 2010 (2010-12-31) * |
Cited By (17)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN103126671B (en) * | 2013-03-27 | 2015-08-19 | 中国人民解放军第三军医大学 | A kind of non-contacting magnetic inductive cerebral hemorrhage detection system |
| 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 |
| CN103344835B (en) * | 2013-07-02 | 2015-04-22 | 富勇 | Magnetic induction measuring method |
| CN103344835A (en) * | 2013-07-02 | 2013-10-09 | 富勇 | Magnetic induction measuring method |
| CN103584858A (en) * | 2013-11-07 | 2014-02-19 | 金贵 | Contralateral-hemisphere-counteraction-based method for non-contact magnetic induction cerebral hemorrhage detection |
| CN103610452B (en) * | 2013-12-03 | 2015-06-10 | 中国人民解放军第三军医大学 | Non-contact magnetic induction type pulse detection method |
| CN103610452A (en) * | 2013-12-03 | 2014-03-05 | 中国人民解放军第三军医大学 | Non-contact magnetic induction type pulse detection method |
| CN103598883A (en) * | 2013-12-03 | 2014-02-26 | 中国人民解放军第三军医大学 | Intracranial pressure monitoring method based on magnetic induction phase difference change |
| CN103860154A (en) * | 2014-02-27 | 2014-06-18 | 中国人民解放军第三军医大学 | Non-contact type wearable type cardiorespiratory activity device based on magnetic induction |
| CN103860154B (en) * | 2014-02-27 | 2016-02-17 | 中国人民解放军第三军医大学 | The wearable cardiopulmonary activity monitoring device of noncontact based on magnetic induction |
| 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 |
| CN103932705B (en) * | 2014-04-29 | 2016-02-17 | 中国人民解放军第三军医大学 | A kind of non-contact magnetic inductive cerebral hemorrhage checkout gear of feature based frequency band |
| TWI509242B (en) * | 2014-12-15 | 2015-11-21 | Ind Tech Res Inst | Non-contact eddy-current detecting device and controlling method thereof |
| CN106361320A (en) * | 2016-09-26 | 2017-02-01 | 江苏爱思普医疗科技有限公司 | Minimally-invasive intracranial pressure and intracranial temperature monitoring system and probe zeroing method |
| 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 |
| CN113288102A (en) * | 2021-06-11 | 2021-08-24 | 中国人民解放军陆军军医大学 | System for monitoring cerebral blood flow without wound |
| TWI781897B (en) * | 2022-04-07 | 2022-10-21 | 國立臺灣科技大學 | Physiological signal detection system |
Also Published As
| Publication number | Publication date |
|---|---|
| CN102973260B (en) | 2014-09-10 |
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 | |
| CN103598883B (en) | Intracranial pressure monitoring method based on magnetic induction phase difference change | |
| US11612331B2 (en) | Headset device for detecting fluid in cranium via time varying magnetic field phase shifts and harmonics of fundamental frequencies | |
| CN103584847B (en) | Non-contact magnetic induction heart rate and respiration rate synchronous detection method and system | |
| Jin et al. | A new method for detecting cerebral hemorrhage in rabbits by magnetic inductive phase shift | |
| CN104039219A (en) | Devices and methods for monitoring cerebral hemodynamic characteristics | |
| JP2016519606A (en) | Measurement of physiological parameters of the brain using bioimpedance | |
| WO2012140510A2 (en) | Devices and methods for monitoring intracranial pressure and additional intracranial hemodynamic parameters | |
| CN113133753B (en) | Biological tissue blood flow real-time monitoring system and simulation monitoring system based on magnetic induction phase shift | |
| CN103126671A (en) | Non-contacting magnetic induction type detecting system of cerebral hemorrhage | |
| JP7123767B2 (en) | Magnetic resonance imaging device | |
| Li et al. | Design of a noninvasive bladder urinary volume monitoring system based on bio-impedance | |
| CN103860154B (en) | The wearable cardiopulmonary activity monitoring device of noncontact based on magnetic induction | |
| US20180317835A1 (en) | System and method for detecting contractions | |
| Sun et al. | The detection of chronic cerebral hemorrhage in rabbits with magnetic induction | |
| CN113288102B (en) | System for monitoring cerebral blood flow without wound | |
| CN202751392U (en) | Brain edema change measuring device based on minimum impedance frequency | |
| CN113768475B (en) | Noninvasive cerebral vascular autonomous regulation function monitoring system based on magnetic induction technology | |
| CN103919542B (en) | Based on the noncontact cerebrospinal fluid pulse pressure ripple monitoring device of magneticinduction | |
| WO2016042402A1 (en) | Systems and methods for diagnosing a brain injury | |
| Gong et al. | Dynamic cerebral blood flow assessment based on electromagnetic coupling sensing and image feature analysis | |
| Bouchaala et al. | Handheld bioimpedance spectrometer for the total frequency range of the e-dispersion | |
| Yu et al. | Inter-modal and intra-modal interference in a multi-modal sensor for non-contact monitoring of vital signs in patient beds | |
| Sun et al. | An experimental study of pulse wave measurements with magnetic induction phase shift method |
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: 20140910 Termination date: 20201130 |
|
| CF01 | Termination of patent right due to non-payment of annual fee |