CN100536783C - Method and system for measuring intracranial pressure - Google Patents
Method and system for measuring intracranial pressure Download PDFInfo
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- CN100536783C CN100536783C CN 200510003877 CN200510003877A CN100536783C CN 100536783 C CN100536783 C CN 100536783C CN 200510003877 CN200510003877 CN 200510003877 CN 200510003877 A CN200510003877 A CN 200510003877A CN 100536783 C CN100536783 C CN 100536783C
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- 238000007917 intracranial administration Methods 0.000 title claims abstract description 29
- 238000000034 method Methods 0.000 title abstract description 21
- 239000002872 contrast media Substances 0.000 claims abstract description 24
- 210000003625 skull Anatomy 0.000 claims abstract description 18
- 238000010183 spectrum analysis Methods 0.000 claims abstract description 7
- 238000004364 calculation method Methods 0.000 claims description 18
- 238000009530 blood pressure measurement Methods 0.000 claims description 11
- 239000002961 echo contrast media Substances 0.000 claims description 8
- 238000010606 normalization Methods 0.000 claims 4
- 238000000605 extraction Methods 0.000 claims 2
- 230000005540 biological transmission Effects 0.000 abstract description 4
- 238000002604 ultrasonography Methods 0.000 description 30
- 238000005259 measurement Methods 0.000 description 7
- 238000001514 detection method Methods 0.000 description 5
- 238000005516 engineering process Methods 0.000 description 5
- 210000004204 blood vessel Anatomy 0.000 description 4
- 210000004556 brain Anatomy 0.000 description 4
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- 206010022773 Intracranial pressure increased Diseases 0.000 description 3
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- 238000002347 injection Methods 0.000 description 3
- 239000007924 injection Substances 0.000 description 3
- 201000009941 intracranial hypertension Diseases 0.000 description 3
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- 206010010356 Congenital anomaly Diseases 0.000 description 1
- 201000009906 Meningitis Diseases 0.000 description 1
- 206010028980 Neoplasm Diseases 0.000 description 1
- 201000010183 Papilledema Diseases 0.000 description 1
- 206010033712 Papilloedema Diseases 0.000 description 1
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- 230000009286 beneficial effect Effects 0.000 description 1
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- 210000001175 cerebrospinal fluid Anatomy 0.000 description 1
- 238000010586 diagram Methods 0.000 description 1
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- 238000010255 intramuscular injection Methods 0.000 description 1
- 239000007927 intramuscular injection Substances 0.000 description 1
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
- A61B8/08—Clinical applications
- A61B8/0808—Clinical applications for diagnosis of the brain
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Abstract
一种颅内压量测方法，可对于一注射有对比剂并形成多数微气泡的颅骨内部区域进行量测，包含以下步骤：(1)对颅骨内部区域发射一带状频宽的超音波发射信号；(2)探测得一来自微气泡的回波信号；(3)回波信号进行频谱分析，得到接近直流部分的低频响应，其频宽与发射信号近似；(4)以低频响应的频宽、强度等表现特性作为参数计算微气泡的共振频率；(5)依据共振频率，配合对比剂的性质，求出微气泡的尺寸；(6)换算颅内压力值。
A method for measuring intracranial pressure can be used to measure an area inside a skull where a contrast agent is injected and a plurality of microbubbles are formed, and comprises the following steps: (1) transmitting an ultrasonic transmission signal with a band-shaped bandwidth to the area inside the skull; (2) detecting an echo signal from the microbubbles; (3) performing spectrum analysis on the echo signal to obtain a low-frequency response close to the DC part, whose bandwidth is similar to that of the transmission signal; (4) calculating the resonance frequency of the microbubbles using the bandwidth, intensity and other performance characteristics of the low-frequency response as parameters; (5) calculating the size of the microbubbles based on the resonance frequency and the properties of the contrast agent; and (6) converting the intracranial pressure value.
Description
Technical field
The present invention relates to a kind of method of intracranial pressure measuring, particularly relate to a kind of non-intrusion type, and with the ultrasound contrast medium and use the intracranial pressure method for measurement of distinctive signal treatment technology.
Background technology
About traumatic intracranial hematoma, intracranial tumor, hemorrhagic apoplexy, meningitis, or disease such as congenital cranium portion deformity, often produce the phenomenon of intracranial hypertension during generation, and because meninges, blood vessel or nerve are squeezed, involve, cause the aggravation of patient's unrelenting headache, paroxysmal, vomiting, in addition because of papilloedema cause optic atrophy, cause expendable blind.Therefore, the early discovery intracranial hypertension, and handle very important timely.
The general detection mode that whether increases for intracranial pressure, except with have a headache clinically, symptom such as vomiting as a reference, mainly still need utilize accurate measurement mode to confirm, comparatively widely used as (1) must get cerebrospinal fluid analysis, (2) shooting X-ray sheet with the examination by centesis of waist awl, inspect projects such as impressions for cerebral gyri, sutura separation, inner table of skull attenuation, sella turcica expansion, reach modes such as (3) brain ultrasound detection.
Wherein, (1) kind intrusive mood measures, and has the problem of the infection and the sufferer suitability; (2) though kind belongs to the non-intrusion type measurement, and is not necessarily effective for the intracranial hypertension early diagnosis.Detect as for (3) the brain ultrasound of planting, because the relation that its outside is coated by skull, the ultrasound signal of launching in the brain is transmitted can a large amount of decay through skull, cause that the echo-signal surveyed is faint, quality is not good.
In recent years, problem for ultrasound signal quality, develop and the householder method that in blood or lymph fluid, adds contrast medium (contrast agent), being based on wherein, microbubble (microbubble) has good echoing characteristics to sound wave, can reach the purpose that promotes signal quality, help measuring of relevant parameter.
See also Fig. 1, the ultrasound echo-signal of relevant contrast medium, carry out spectrum analysis and can find a known fundamental frequency response (fundamental response) 11,1 second resonance response (secondharmonic response) 12, and a resonance response (subharmonic) 13.The latter two all belong to the nonlinearity response of bubble, and need higher acoustic pressure in transmission that microbubble is produced, and wherein the required acoustic pressure of resonance response 13 is the highest in proper order again.
Wherein, fundamental frequency response all can be found in blood flow and surrounding tissue, therefore can't lose value in order to comparison and identification.
With regard to second resonance response, because it belongs to high frequency, showing especially on the one hand through the degree that decays behind the skull; Then owing in the mammal tissue, also can find second resonance response, make the ability of utilizing second resonance response to distinguish blood, lymph fluid and surrounding tissue greatly reduce on the other hand.
With regard to inferior resonance response, in the 6th, 302, No. 845 patents of the U.S., disclose a kind of traditional ultrasound system that uses, be auxiliary with contrast medium, in order to infer the method for heart or pylic pressure.Its technical characterstic is: applying under the situation of different pressures at microbubble, and the difference of time resonance response that produces, and then infer force value.Yet, when significantly time resonance response is ejected by required high pressure, often follow microbubble to begin disruptive phenomenon.If the method is used in the measurement of intracranial pressure, the microbubbles rupture phenomenon probably threatens to brain safety.
Summary of the invention
Therefore, the intracranial pressure measuring method and the system that the purpose of this invention is to provide a kind of non-intrusion type.
Another object of the present invention provides a kind of method for measurement and the system that can in time try to achieve intracranial pressure.
A further object of the present invention provides a kind of accurate and safe intracranial pressure measuring method and system.
Intracranial pressure measuring method of the present invention and system, can measure for the skull interior zone that an injection has contrast medium and forms most microbubbles, this system comprises a ultrasound scanner head (transducer), a transmitter module that links to each other with ultrasound scanner head and a receiver module, and a signal processing module that is connected with receiver module.
This method then comprises following steps:
(1) transmitter module produces and drives signal, and the ultrasound that makes ultrasound scanner head that the skull interior zone is launched a banded frequency range transmits, that is short pulse signal (short-pulse).Because the signal of the present invention's acquisition in order to analyze, the degree small (being described in more detail in hereinafter) that decayed by skull, so this ultrasound scanner head can select to measure from cranium portion optional position makes ultrasound penetrate medium such as skull and enters cranium portion blood vessel.
(2) ultrasound scanner head detects an echo-signal from microbubble, and is sent to receiver module.
(3) receiver module is passed to signal processing module with echo-signal, to carry out further calculation process work.
(4) signal processing module carries out spectrum analysis with echo-signal, obtains a fundamental frequency response, one second resonance response, a resonance response, and a uncared-for in the past LF-response (low-frequency response).The generation of LF-response can be supported jointly-stimulate simultaneously when microbubble is subjected to the bifrequency acoustic signals in the theoretical and experiment that the present invention derived, and this double frequency enough near the time (suitably launching frequency range), the difference of this double frequency part near direct current in frequency spectrum is excited, just LF-response.Therefore it should be noted that one of LF-response characteristic is: do not need the required high sound pressure of as follows resonance response, the generation that can be excited does not have the phenomenon of microbubbles rupture, and is obviously safer and be applicable to intracranial pressure measuring compared to known technology.
(5) signal processing module utilize LF-response performance characteristics such as frequency range, intensity as parameter, with the formula that extends by the bifrequency analytic solutions, calculate the resonant frequency of this microbubble.
(6) signal processing module cooperates the character of contrast medium according to this resonant frequency, obtains the size of this microbubble.Wherein, based on the difference of contrast medium, the relation of its microbubble resonant frequency and size is also different.
(7) last, because the microbubble size can be subjected to the ambient value influence at its place, signal processing module can converse the force value of skull interior zone according to the size of microbubble.
Intracranial pressure measuring of the present invention system, the skull interior zone that contrast medium is arranged and form most microbubbles for an injection measures; This system comprises: a transmitter module transmits in order to the ultrasound of this zone being launched a banded frequency range; One receiver module is in order to detect one from the echo-signal of a microbubble wherein; An and signal processing module, be connected with this receiver module, and comprise a low frequency acquisition unit, a resonant frequency computing unit and a calculation of pressure unit: this low frequency acquisition unit carries out spectrum analysis and separates obtaining a LF-response at this echo-signal, and the frequency range of this LF-response is similar to this frequency range that transmits; The performance characteristic that this resonant frequency calculates this LF-response of unit by using calculate the resonant frequency of this microbubble; Reach this calculation of pressure unit and obtain the size of this microbubble, and further calculate the force value that this is regional according to the character of this resonant frequency and this contrast medium.
The amount of pressure examining system of application ultrasound contrast medium of the present invention, the target area that contrast medium is arranged and form most microbubbles for an injection measures, this system comprises: a transmitter module transmits in order to the ultrasound of this target area being launched a banded frequency range; One receiver module is in order to detect one from the echo-signal of a microbubble wherein; An and signal processing module, be connected with this receiver module, and comprise a low frequency acquisition unit, a resonant frequency computing unit and a calculation of pressure unit: this low frequency acquisition unit carries out spectrum analysis and separates obtaining a LF-response at this echo-signal, and the frequency range of this LF-response is similar to this frequency range that transmits; The performance characteristic that this resonant frequency calculates this LF-response of unit by using calculate the resonant frequency of this microbubble; Reach this calculation of pressure unit and obtain the size of this microbubble, and further calculate the force value of this target area according to the character of this resonant frequency and this contrast medium.
Because the present invention adopts the LF-response of ultrasound echo-signal to carry out computing, and that the LF-response signal penetrates the attenuation degree of skull is little compared to high frequency, therefore the signal quality that is received by ultrasound scanner head is preferable, can obtain force value according to its characteristic quickly and accurately.In addition, aforementioned contrast medium is not limited to inject blood vessel, can see through intramuscular injection and enter lymph fluid, therefore can use the inventive method equally the pressure measurement is carried out in the lymph fluid region.
What deserves to be mentioned is, just because of the present invention separates the LF-response of employing, need not bestow high pressure can produce, and speciality with the influence of fading that is not subjected to high attenuation rate medium, therefore can be applied in other organ of mammal such as heart safer and effectively, or pylic pressure detection, even being used for surveying arbitrary different medium, for example building be full of cracks, finedraw are surveyed, the ocean Mesichthyes is surveyed etc.
Description of drawings
Fig. 1 is the spectrogram of a ultrasound echo-signal, and the fundamental frequency, second resonance that disclose at the known technology document are described, and time resonance response;
Fig. 2 is the system block diagrams of intracranial pressure measuring of the present invention system one preferred embodiment;
Fig. 3 is the flow chart of intracranial pressure measuring method one preferred embodiment of the present invention;
Fig. 4 is the spectrogram of a ultrasound echo-signal, illustrates that application the inventive method and system isolate a LF-response; And
Fig. 5 is the resonant frequency of a microbubble and frequency range, the strength relationship figure of echo-signal.
The reference numeral explanation
11 fundamental frequency response
12 second resonance responses
13 resonance responses
20 signal processing modules
21 ultrasound scanner heads
22 transmitter modules
23 receiver modules
24 filter units
25 low frequency acquisition units
26 resonant frequencies calculate the unit
27 calculation of pressure unit
31～38 steps
41 fundamental frequency response
42 LF-response
The specific embodiment
About aforementioned and other technology contents, characteristics and effect of the present invention, in detailed description, can clearly present below in conjunction with a preferred embodiment of accompanying drawing.
As shown in Figure 2, the preferred embodiment of intracranial pressure measuring of the present invention system be with the pressure of a skull interior zone as measuring target, and in general intravenous mode contrast medium is injected in advance, make in this zone blood to have most microbubbles.The intracranial pressure measuring system comprises a ultrasound scanner head 21, a transmitter module 22 that links to each other with ultrasound scanner head 21 and a receiver module 23, and a signal processing module 20 that is connected with receiver module 23.Signal processing module 20 inside comprise a filter unit 24, a low frequency acquisition unit 25, a resonant frequency computing unit 26 that links to each other in regular turn again, and a calculation of pressure unit 27.
See also Fig. 3, intracranial pressure measuring method of the present invention then comprises following steps:
Step 31-transmitter module 22 produces one and drives signal, is passed to ultrasound scanner head 21.This ultrasound scanner head 21 should be posted by cranium portion appearance any place in advance.
Step 32-ultrasound scanner head 21 drives signal according to this, and the ultrasound of launching a banded frequency range transmits, and making transmits penetrates the blood vessel that skull arrives the intracranial zone.This transmits and need not be high sound pressure, the 2-10MHz that mid frequency can adopt general instrument to send, and the signal frequency range can roughly be chosen as the 10-40% of mid frequency.Is that 20% of mid frequency explains for example at present embodiment with 3.25MHz and frequency range.
Step 33-ultrasound scanner head 21 detects an echo-signal from microbubble, and is sent to receiver module 23.
Step 34-receiver module 23 is passed to the filter unit 24 of signal processing module 20 with echo-signal, carries out the echo-signal quality that Filtering Processing obtains this detection and promotes.
Step 35-see also Fig. 4,25 receptions of low frequency acquisition unit are from the echo-signal of filter unit 24, the line frequency analysis of spectrum of going forward side by side.According to the frequency distribution of this echo-signal, can obtain one with the mid frequency and the suitable fundamental frequency response 41 of frequency range of tranmitting frequency, an and LF-response 42 near the part of direct current, and utilize band filter to capture a LF-response 42.These LF-response 42 frequency ranges are similar to the frequency range of fundamental frequency response 41.
The resonant frequency of step 36-signal processing module 20 calculates unit 26, with performance characteristics such as the frequency range of LF-response, intensity as parameter, utilization is by the bifrequency analytic solutions, and (formula 1) that cooperates the vibrated nonlinear characteristic to be extended calculates the resonant frequency of this microbubble.
P
2∝ p
2X '
12 2B
e 4... ... ... ... .. (formula 1)
Wherein, P=p
L/ p
F, (p
L: LF-response intensity, p
F: the fundamental frequency response intensity peak), just through the LF-response intensity of standardization.
P: acoustic pressure in transmission
(f
0: resonant frequency, Δ f: frequency range)
B
e=Δ f/f
c(f
c: the mid frequency of fundamental frequency), just through the LF-response frequency range of standardization.
Relevant following formula can be made into resonant frequency-frequency range graph of a relation as shown in Figure 5, and transverse axis is represented resonant frequency f
0, the MHz of unit; The longitudinal axis is represented standardization frequency range B
eThe equal pitch contour that seals among the figure is represented standardization intensity P, and with depth representing intensity.
As shown in Figure 5, be set at frequency range under 20% situation of mid frequency, look the intensity of the LF-response 42 of measured echo, can learn the resonant frequency of microbubble.
The calculation of pressure unit 27 of step 37-signal processing module 20 according to the resonant frequency that step 36 is obtained, utilizes (formula 2) can obtain the size of this microbubble.
f
0.R
0≈ 3.2.................................... (formula 2)
Wherein, f
0Represent resonant frequency, the MHz of unit;
R
0Represent the diameter of microbubble, the μ m of unit.
(formula 2) comes from the character of contrast medium own, and at the contrast medium that present embodiment adopted, the diameter of its microbubble and the product value of resonant frequency are constantly equal to 3.2.This product value is difference to some extent according to the kind of contrast medium.
Step 38-last, because the microbubble size can be subjected to the ambient value influence at its place, the microbubble size that try to achieve according to step 37 the calculation of pressure unit 27 of signal processing module 20 converses the force value of skull interior zone.
Conclude above-mentionedly, intracranial pressure measuring method of the present invention and system have following characteristics:
(1) non-intrusion type method for measurement, no wound is looked after and infection problems, and is fit to patient's use of the various patient's condition.
(2) do not need other auxiliary facilities, can cooperate general existing ultrasound system to measure timely, reduce expending of extra cost.
(3) because the echo that receives is only got LF-response, it more is not subjected to the skull influence of fading, can say so influenced by one-way attenuation, therefore can select arbitrarily in the position of ultrasound scanner head 21 emission ultrasound signals of the present invention and detection, is not limited to positions such as known eye socket, temple.
(4) because the LF-response of echo can excite with low transmitting of acoustic pressure, therefore do not have the problem of microbubbles rupture, safer for the measurement of cranium portion pressure.
(5) adopt the LF-response of echo-signal to carry out computing, compared to the fundamental frequency or second resonance response, for the identification separating capacity height of blood flow and surrounding tissue, and owing to its low frequency characteristic and the visual degree of depth is darker; Compared to inferior resonance response, then the microbubble holding time long, safety and be beneficial to observation.
Therefore can reach really safety of the present invention, in time, economical and accurately measure the purpose of intracranial pressure.
The above is preferred embodiment of the present invention only, and can not limit scope of the invention process with this, and therefore the simple equivalent of being done according to claim of the present invention and invention book content changes and modifies, and all belongs to the scope that patent of the present invention contains.
Claims (12)
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| CN 200510003877 CN100536783C (en) | 2005-01-19 | 2005-01-19 | Method and system for measuring intracranial pressure |
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Families Citing this family (5)
| Publication number | Priority date | Publication date | Assignee | Title |
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| US8211031B2 (en) * | 2002-01-15 | 2012-07-03 | Orsan Medical Technologies Ltd. | Non-invasive intracranial monitor |
| CN102048530B (en) * | 2010-12-22 | 2012-05-23 | 重庆大学 | Modification algorithm-based method for extracting simplex-wave feature points of intracranial pressure signals |
| US20120203121A1 (en) | 2011-02-09 | 2012-08-09 | Opher Kinrot | Devices and methods for monitoring cerebral hemodynamic characteristics |
| CN103190930B (en) * | 2013-04-19 | 2014-10-29 | 重庆大学 | Intracranial pressure monitoring instrument based on ultrasonic wave acoustoelastic effect |
| EP3645118B1 (en) * | 2017-06-29 | 2023-11-29 | Insightec Ltd. | Simulation-based drug treatment planning |
Citations (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US5749364A (en) * | 1996-06-21 | 1998-05-12 | Acuson Corporation | Method and apparatus for mapping pressure and tissue properties |
| WO1999047045A1 (en) * | 1998-03-20 | 1999-09-23 | Thomas Jefferson University | Microbubble-based ultrasonic contrast agents for pressure measurements |
| CN1251028A (en) * | 1997-01-22 | 2000-04-19 | 廓德伦特健康护理(英国)有限公司 | Ultrasound contrast imaging |
| US20040129082A1 (en) * | 2001-04-06 | 2004-07-08 | Frinking Peter J A | Method for improved measurement of local physical parameters in a fluid-filled cavity |
-
2005
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Patent Citations (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US5749364A (en) * | 1996-06-21 | 1998-05-12 | Acuson Corporation | Method and apparatus for mapping pressure and tissue properties |
| CN1251028A (en) * | 1997-01-22 | 2000-04-19 | 廓德伦特健康护理(英国)有限公司 | Ultrasound contrast imaging |
| WO1999047045A1 (en) * | 1998-03-20 | 1999-09-23 | Thomas Jefferson University | Microbubble-based ultrasonic contrast agents for pressure measurements |
| US20010021808A1 (en) * | 1998-03-20 | 2001-09-13 | William Tao Shi | Method and system for pressure estimation using subharmonic signals from microbubble-based ultrasound contrast agents |
| US20040129082A1 (en) * | 2001-04-06 | 2004-07-08 | Frinking Peter J A | Method for improved measurement of local physical parameters in a fluid-filled cavity |
Non-Patent Citations (1)
| Title |
|---|
| Intracranial pressure monitoring: application of spectralanalysis to the classification of B-waves. Pasley, R.L., Connolly, M.J.L., Bada, H.S., et al.Proceedings of the First Joint BMES/EMBS Conference. 1999 IEEE Engineering in Medicine and Biology 21st Annual Conference and the 1999 Annual Fall Meeting of the Biomedical Engineering Society,Vol.1 . 1999 * |
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