CN105232004A - Opto-acoustic-ultrasonic united imaging device and imaging method for precisely measuring thickness of melanoma - Google Patents
Opto-acoustic-ultrasonic united imaging device and imaging method for precisely measuring thickness of melanoma Download PDFInfo
- Publication number
- CN105232004A CN105232004A CN201510788892.0A CN201510788892A CN105232004A CN 105232004 A CN105232004 A CN 105232004A CN 201510788892 A CN201510788892 A CN 201510788892A CN 105232004 A CN105232004 A CN 105232004A
- Authority
- CN
- China
- Prior art keywords
- signal
- imaging
- ultrasonic
- photoacoustic
- melanoma
- 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
Landscapes
- Ultra Sonic Daignosis Equipment (AREA)
- Investigating Or Analyzing Materials By The Use Of Ultrasonic Waves (AREA)
Abstract
The invention relates to an opto-acoustic-ultrasonic united imaging device for precisely measuring the thickness of melanoma. The opto-acoustic-ultrasonic united imaging device comprises a computer control and imaging system, a laser emitting system, a time delay module, an FPGA control and signal processing system, a digital-analog converter, an ultrasonic receiving/emitting unit and a handheld dual-mode integrated detector, wherein pulse triggering of the laser emitting system is divided into two paths; one path is directly contacted with the FPGA control and signal processing system to acquire an opto-acoustic signal; the other path is contacted with the FPGA control and signal processing system through the time delay module to acquire an ultrasonic signal; the thickness of melanoma can be precisely measured by using generated opto-acoustic images and ultrasonic images. The invention further relates to an opto-acoustic-ultrasonic united imaging method for precisely measuring thickness of melanoma. By using the imaging device and the imaging method, the thickness of melanoma at different stages can be precisely measured in a non-destructive mode, the imaging device is small in size, possibility of rapid clinical detection is provided, and the imaging device and the imaging method belong to the technical field of opto-acoustic-ultrasonic imaging measurement.
Description
Technical field
The present invention relates to the technology being measured melanoma thickness by optoacoustic and ultra sonic imaging, specifically, relate to a kind of the photoacoustic ultrasound joint imaging device and the formation method that accurately measure melanoma thickness.
Background technology
Melanoma thickness is the major criterion judging postoperative five-year survival rate.The increase that melanoma infiltrates thickness (Clark grade) is relevant with poor prognosis.Histology judges that treatment and prognosis determine mainly through the intramural invasion in microscopic Melanoma Tissue.Histological grade needs to carry out sufficient biopsy.But biopsy can bring painful also scar to patient, and the excision damaged likely brings further cancerates.Present stage, the main method of nondestructive measurement melanoma thickness is ultra sonic imaging, be usually used in the high frequency ultrasound that melanoma is measured at present, dominant frequency is generally 15-20Mhz, the ultra sonic imaging degree of depth comparatively dark (cm) of this pattern, but be less than 1.5mm to thickness, be especially less than the melanoma of 0.75mm, thickness statistical error is larger.
Photoacoustic imaging is a kind of harmless medical imaging techniques, it is based on optoacoustic effect, use short-pulse laser (optical signal) the irradiating biological tissue of nanosecond order, after biological tissue absorbs short-pulse laser, cause thermal-elastic expansion fast to produce mechanical wave, produce ultrasound wave (photoacoustic signal) thus.Ultrasonic detector receives the ultrasound wave of generation and carries out back projection by certain algorithm, namely obtains the light absorption distribution in tissue.Photoacoustic imaging is the imaging based on tissue resorption, although stage melanoma acoustic impedance and surrounding tissue are more or less the same, containing a large amount of melanin in it, can obtain high to the high-resolution optoacoustic result of comparison.But photoacoustic imaging is limited to melanomatous imaging depth, therefore, by in conjunction with optoacoustic and ultra sonic imaging, difference melanoma thickness by stages can be obtained, simultaneously, the acoustic impedance of epidermis and couplant differs greatly, and can be presented clearly by ultra sonic imaging, thus improves the accuracy of melanoma intramural invasion detection.
Summary of the invention
For the technical problem existed in prior art, the object of the invention is: a kind of the photoacoustic ultrasound joint imaging device and the formation method that accurately measure melanoma thickness are provided, can real-time, accurately measure difference melanomatous thickness by stages.
In order to achieve the above object, the present invention adopts following technical scheme:
Accurately measure a photoacoustic ultrasound joint imaging device for melanoma thickness, comprising: computer controls and imaging system, laser transmitting system, time delay module, FPGA control and signal processing system, digital to analog converter, ultrasonic reception/transmitter unit, the double-mode integrated detector of hand-held; Computer controls and imaging system connects with laser transmitting system; The pulse-triggered of laser transmitting system is divided into two-way, a road directly controls with FPGA and signal processing system contacts luminous acoustical signal collection, triggering ultrasonic signal acquisition that time delay module of separately leading up to controls with FPGA and signal processing system connects; Along the flow direction of signal, FPGA controls and signal processing system, ultrasonic reception/transmitter unit, the double-mode integrated detector of hand-held, ultrasonic reception/transmitter unit, digital to analog converter, FPGA control and signal processing system, computer control and imaging system set gradually.
Computer control and imaging system control the operation of laser transmitting system, control the keying of time delay module, receive optoacoustic/ultrasonic signal, realize realtime imaging; Laser transmitting system Emission Lasers; Laser postpones to be used for ultrasound imaging mode by time delay module; FPGA controls and signal processing system controls ultrasonic reception/transmitter unit and launches and Received signal strength will return computer after optoacoustic/ultrasonic signal processing and control and imaging system; Ultrasonic reception/transmitter unit only Received signal strength under photoacoustic imaging pattern, launches and Received signal strength under ultrasound imaging mode; The double-mode integrated detector of hand-held and contact skin, transmit to skin and receive the signal of skin reflex.
The double-mode integrated detector of hand-held comprises: shell and the fibre bundle, line collimating lens, line focus lens, the ultrasonic detector array that are successively set in shell; Ultrasonic reception/transmitter unit connects with fibre bundle; The signal of ultrasonic detector array received skin reflex, transmits signals to ultrasonic reception/transmitter unit.
Fibre bundle comprises n bar optical fiber, and ultrasonic detector array comprises n group array element sheet, and ultrasonic reception/transmitter unit comprises n group reception/radiating circuit, an optical fiber and one group of array element sheet correspondence access, one group of reception/radiating circuit; The access FPGA of n group reception/radiating circuit parallel connection controls and signal processing system; Wherein n gets positive integer.
Fibre bundle is the multimode fibre of multifiber linearly arrangement architecture.
The quantity of array element sheet is many groups; The quantity often organizing array element sheet is two, the symmetrical both sides being arranged on the signal irradiating skin; Multiple array element sheets of the same side form a line.
Each array element sheet is all 5 degree to 10 degree angles with skin surface; Two array element sheets with group become splayed, and splay big uncork is towards skin.
The shape of line focus lens is strip, and convex surface is downward, and burnt length is 22-30 millimeter.
Accurately measure a photoacoustic ultrasound joint imaging method for melanoma thickness, use a kind of photoacoustic ultrasound joint imaging device accurately measuring melanoma thickness, comprise the steps:
A. computer control and imaging system control the operation of laser transmitting system, laser transmitting system Emission Lasers, simultaneously for photoacoustic imaging and ultra sonic imaging provide triggering signal, one tunnel triggering signal directly triggers photoacoustic signal collection, i.e. step b, another road triggering signal is through time delay module Triggered ultrasound signals collecting, i.e. step c, realizes photoacoustic imaging and the substep of ultra sonic imaging at same collection position triggers;
B. laser controls and signal processing system through FPGA, signal through ultrasonic reception/transmitter unit amplifies, skin is irradiated again by the double-mode integrated detector of hand-held, the photoacoustic signal of the ultrasonic detector array received skin reflex of the double-mode integrated detector of hand-held, photoacoustic signal is returned ultrasonic reception/transmitter unit and become the signal of telecommunication, the signal of telecommunication controls and arrives computer after signal processing system to control and imaging system through digital to analog converter, FPGA; Wherein FPGA control and signal processing system are under photoacoustic imaging pattern, and gather photoacoustic signal by ultrasonic reception/transmitter unit, be used for carrying out photoacoustic imaging restructuring, ultrasonic reception/transmitter unit only works in receiving mode;
C. laser to control and signal processing system excitation ultrasound reception/transmitter unit transmits through time delay module and FPGA, the double-mode integrated detector of signal excitation hand-held produces ultrasonic signal and irradiates skin, the ultrasonic signal of the ultrasonic detector array received skin reflex of the double-mode integrated detector of hand-held, ultrasonic signal is returned ultrasonic reception/transmitter unit and become the signal of telecommunication, the signal of telecommunication controls and arrives computer after signal processing system to control and imaging system through digital to analog converter, FPGA; Wherein, when FPGA control and signal processing system gauge tap select ultrasound imaging mode time, FPGA controls and signal processing system controls ultrasonic reception/transmitter unit transmitting ultrasonic signal and gathers ultrasonic signal, be used for carrying out ultra sonic imaging restructuring, ultrasonic reception/transmitter unit works in reception/emission mode;
D. computer control and imaging system comprise the double-mode imaging pattern containing photoacoustic imaging and ultra sonic imaging, generate photoacoustic image and ultrasonoscopy, are provided the test result of melanoma thickness by two width images.
In steps d, epidermis position is indicated by ultrasonoscopy, melanoma upper surface position is indicated: measure melanoma lower surface signal distance upper surface signal when photoacoustic signal and be greater than 1.5mm by photoacoustic image, or photoacoustic signal lower surface Signal-to-Noise is when being less than 6db, melanoma lower surface position is indicated by ultrasonoscopy, otherwise, then melanoma lower surface position is indicated by photoacoustic image.
Generally speaking, tool of the present invention has the following advantages:
1. can measure different melanoma thickness by stages accurately by harmless mode.
2. adopt the double-mode integrated detector of hand-held, compact, for clinical quick detection provides probability.
3. optoacoustic, ultrasonic double-mode imaging pattern, obtains the optical characteristics harmony impedance information of tissue simultaneously.
4. adopt line focus lens line focus hot spot and ultrasonic detector array, more single focal beam spot and single array element detector, speed is faster, can carry out double-mode imaging real-time.
5. array element sheet and skin tilt, and are focused on by physics, improve detectivity.
Accompanying drawing explanation
Fig. 1 is a kind of theory diagram accurately measuring the photoacoustic ultrasound joint imaging device of melanoma thickness.
Fig. 2 is the structural representation of the double-mode integrated detector of hand-held.
Fig. 3 is light, the sound transmission schematic diagram of the double-mode integrated detector of hand-held.
Fig. 4 a is the ultra sonic imaging image of embodiment one.
Fig. 4 b is the photoacoustic imaging image of embodiment one.
1 is computer control and imaging system, and 2 is laser transmitting system, and 3 is time delay module, and 4 is that FPGA controls and signal processing system, and 5 is ultrasonic reception/transmitter unit, and 6 is the double-mode integrated detector of hand-held, and 7 is digital to analog converter.5-1,5-2 ..., 5-64 is reception/radiating circuit.6-1,6-2 ..., 6-64 is each group of array element sheet.
61 is fibre bundle, and 62 is line collimating lens, and 63 is line focus lens, and 64 is focused beam, and 65 is ultrasonic detector array.
11 instruction simulation skin surfaces, 12 instruction simulation melanoma upper surfaces, 13 instruction thickness are less than the melanomatous mark lower surface of simulation of 1.5mm, and 14 instruction thickness are greater than the melanomatous mark lower surface of simulation of 1.5mm.
Detailed description of the invention
Come that the present invention will be further described in detail below.
Accurately measure a photoacoustic ultrasound joint imaging device for melanoma thickness, comprising: computer controls and imaging system, laser transmitting system, time delay module, FPGA control and signal processing system, digital to analog converter, ultrasonic reception/transmitter unit, the double-mode integrated detector of hand-held.A kind of photoacoustic ultrasound joint imaging device accurately measuring melanoma thickness adopts existing system or module again to arrange and is formed by connecting, and connected mode is: computer controls and imaging system connects with laser transmitting system; Laser transmitting system is divided into two-way, a road directly controls with FPGA and signal processing system contacts luminous acoustical signal collection, triggering ultrasonic signal acquisition that time delay module of separately leading up to controls with FPGA and signal processing system connects; Along the flow direction of signal, FPGA controls and signal processing system, ultrasonic reception/transmitter unit, the double-mode integrated detector of hand-held, ultrasonic reception/transmitter unit, digital to analog converter, FPGA control and signal processing system, computer control and imaging system set gradually.The double-mode integrated detector of hand-held adopts existing parts again to arrange and is formed by connecting.
Computer control and imaging system control the operation of laser transmitting system, control the keying of time delay module, receive optoacoustic/ultrasonic signal, realize realtime imaging.Computer control and imaging system comprise the double-mode imaging pattern containing photoacoustic imaging and ultra sonic imaging, generate photoacoustic image and ultrasonoscopy, are provided the test result of melanoma thickness by two width images.
Laser transmitting system, for generation of laser, comprises laser instrument, laser shaping filter element and fiber coupling device.Wherein laser instrument exports pulse laser, through laser shaping filter element, is coupled into fiber array by fiber coupling device.Described fiber array comprises the fibre bundle of rectangular array arrangement.
The delay circuit that time delay module is formed based on 555 chips, for the external trigger that time delay is produced by laser instrument, external trigger passes through time delay, the transmitting of Triggered ultrasound signal and collection.
FPGA controls and signal processing system comprises signal condition and acquisition module, dynamic RAM, Flash (flash memory), PXIe controller and FPGA controller.Wherein FPGA controller controls ultrasonic reception/transmitter unit transmitting and receives ultrasonic signal, fifo module is input to by bus after signal condition and acquisition module convert the analogue signal of input the digital signal of serial to, fifo module transfers signals to main control unit, result is stored in inside internal RAM.FPGA controls and signal processing system is existing equipment, and it is a kind of development board, and above, program writing can realize the function needed, and the function that the FPGA in the present invention controls and signal processing system reaches is existing.
Digital to analog converter is used for the conversion of signal, is convenient to computer and controls and imaging system Received signal strength.
Ultrasonic reception/transmitter unit, comprises the access FPGA control of 64 tunnel parallel connections and the reception/radiating circuit of signal processing system.Under photoacoustic imaging pattern, reception/radiating circuit is Received signal strength only, and the circuit as amplifying circuit signal uses.Under ultrasound imaging mode, the 64 tunnel double-mode integrated detectors of reception/radiating circuit excitation hand-held produce and receive ultrasonic signal.
The double-mode integrated detector of hand-held comprises fibre bundle, line collimating lens, line focus lens, ultrasonic detector array, shell.In shell, fibre bundle, line collimating lens, line focus lens, ultrasonic detector array set gradually.Wherein, fibre bundle comprises 64 optical fiber, and ultrasonic detector array comprises 64 groups of array element sheets, an optical fiber and one group of array element sheet correspondence access, one group of reception/radiating circuit.Fibre bundle is the multimode fibre of 64 rectangular arrayed structures of optical fiber.Line collimating lens is used for the laser of collimating optical fibre bundle outgoing.Line focus lens are used for the linear light source of laser beam focus after by collimation, and the shape of line focus lens is strip, and convex surface is downward, and burnt length is 22-30 millimeter.The quantity of array element sheet is 64 groups; The quantity often organizing array element sheet is two, the symmetrical both sides being arranged on the signal irradiating skin; Multiple array element sheets of the same side form a line.Each array element sheet is all 5 degree to 10 degree angles with skin surface; Two array element sheets with group become symmetrically arranged splayed, and the signal of skin reflex towards skin, thus can be gathered collection by splay big uncork.Work process is as follows: laser imports through fibre bundle, the laser of fibre bundle outgoing, after line collimating lens collimation, light beam is that line source irradiates tissue surface by line focus lens focus, produce ultrasonic signal, via ultrasonic detector array received, the signal now received is for the restructuring of photoacoustic image; After time delay after a while, ultrasonic detector array emitter is ultrasonic and receive, and the signal now received is for the restructuring of ultrasonic signal.As shown in Figure 3, focused light beam tissue surface, wherein optical focus and detector area for sound,focal are at grade to improve the sensitivity that photoacoustic signal detects.Ultrasonic detector array is the symmetrical two row array element sheets placed, and every two array element sheets of symmetric position are respectively one group, and each group array element sheet transmits and receives signal simultaneously.
A kind of photoacoustic ultrasound joint imaging method accurately measuring melanoma thickness, computer control and imaging system control the folding of laser transmitting system, the external trigger (by the automatic selection path of sequencing contro) of laser transmitting system is divided into two-way, as shown in the dotted line frame on the right side of Fig. 1, by gauge tap selection path, the collection of photoacoustic signal or ultrasonic signal is triggered.Wherein, external trigger directly triggers FPGA and controls and signal processing system, and namely path below selected by switch shown in figure, then for triggering photoacoustic signal collection; External trigger by time delay module, namely figure breaker in middle select above path time, triggering FPGA and control and signal processing system, is then Triggered ultrasound signals collecting.FPGA controls and signal processing system controls 64 tunnel reception/radiating circuits, and under photoacoustic mode, reception/radiating circuit only receives photoacoustic signal, and the circuit as amplifying circuit signal uses; Under ultrasound mode, FPGA control and signal processing system control 64 tunnel reception/radiating circuits excitation ultrasonic detector arrays and produce and receive ultrasonic signal.In both modes, the signal of telecommunication transformed after ultrasonic detector array received to acoustical signal all by digital to analog converter, receive enter FPGA control and signal processing system carry out signal processing after transmission enter computer control and imaging system.Computer controls and imaging system receives optoacoustic/ultrasonic signal, and carries out image reorganization, indicates epidermis position by ultrasonoscopy, indicates melanoma upper surface position by photoacoustic image; The instruction of melanoma lower surface position is divided into following two kinds of situations: measure melanoma lower surface signal distance upper surface signal when photoacoustic signal and be greater than 1.5mm, or photoacoustic signal lower surface Signal-to-Noise is when being less than 6db, melanoma lower surface position is indicated by ultrasonoscopy, otherwise, then melanoma lower surface position is indicated by photoacoustic image.
As shown in figures 4 a and 4b, ultrasonoscopy indicates the position of epidermis to testing result, the position of photoacoustic image instruction melanoma upper surface, and the instruction of melanoma lower surface position take 1.5mm as index; When system judgement melanoma thickness is less than 1.5mm (photoacoustic signal is measured melanoma lower surface signal distance upper surface signal and is less than 1.5mm), provide melanoma lower surface position by photoacoustic imaging; When system judges that melanoma thickness is greater than 1.5mm, or when photoacoustic signal lower surface Signal-to-Noise is less than 6db, indicate melanoma lower surface position by ultra sonic imaging.
Above-described embodiment is the present invention's preferably embodiment; but embodiments of the present invention are not restricted to the described embodiments; change, the modification done under other any does not deviate from spirit of the present invention and principle, substitute, combine, simplify; all should be the substitute mode of equivalence, be included within protection scope of the present invention.
Claims (10)
1. accurately measure a photoacoustic ultrasound joint imaging device for melanoma thickness, it is characterized in that: comprising: computer controls and imaging system, laser transmitting system, time delay module, FPGA control and signal processing system, digital to analog converter, ultrasonic reception/transmitter unit, the double-mode integrated detector of hand-held; Computer controls and imaging system connects with laser transmitting system; The pulse-triggered of laser transmitting system is divided into two-way, a road directly controls with FPGA and signal processing system contacts luminous acoustical signal collection, triggering ultrasonic signal acquisition that time delay module of separately leading up to controls with FPGA and signal processing system connects; Along the flow direction of signal, FPGA controls and signal processing system, ultrasonic reception/transmitter unit, the double-mode integrated detector of hand-held, ultrasonic reception/transmitter unit, digital to analog converter, FPGA control and signal processing system, computer control and imaging system set gradually.
2., according to a kind of photoacoustic ultrasound joint imaging device accurately measuring melanoma thickness according to claim 1, it is characterized in that: described in
Computer control and imaging system control the operation of laser transmitting system, control the keying of time delay module, receive optoacoustic/ultrasonic signal, realize realtime imaging;
Laser transmitting system Emission Lasers;
Laser postpones to be used for ultrasound imaging mode by time delay module;
FPGA controls and signal processing system controls ultrasonic reception/transmitter unit and launches and Received signal strength will return computer after optoacoustic/ultrasonic signal processing and control and imaging system;
Ultrasonic reception/transmitter unit only Received signal strength under photoacoustic imaging pattern, launches and Received signal strength under ultrasound imaging mode;
The double-mode integrated detector of hand-held and contact skin, transmit to skin and receive the signal of skin reflex.
3. according to a kind of photoacoustic ultrasound joint imaging device accurately measuring melanoma thickness according to claim 1, it is characterized in that: the double-mode integrated detector of described hand-held comprises: shell and the fibre bundle, line collimating lens, line focus lens, the ultrasonic detector array that are successively set in shell; Ultrasonic reception/transmitter unit connects with fibre bundle; The signal of ultrasonic detector array received skin reflex, transmits signals to ultrasonic reception/transmitter unit.
4. according to a kind of photoacoustic ultrasound joint imaging device accurately measuring melanoma thickness according to claim 3, it is characterized in that: described fibre bundle comprises n bar optical fiber, ultrasonic detector array comprises n group array element sheet, ultrasonic reception/transmitter unit comprises n group reception/radiating circuit, an optical fiber and one group of array element sheet correspondence access, one group of reception/radiating circuit; The access FPGA of n group reception/radiating circuit parallel connection controls and signal processing system; Wherein n gets positive integer.
5. according to a kind of photoacoustic ultrasound joint imaging device accurately measuring melanoma thickness according to claim 4, it is characterized in that: described fibre bundle is the multimode fibre of multifiber linearly arrangement architecture.
6., according to a kind of photoacoustic ultrasound joint imaging device accurately measuring melanoma thickness according to claim 4, it is characterized in that: the quantity of described array element sheet is many groups; The quantity often organizing array element sheet is two, the symmetrical both sides being arranged on the signal irradiating skin; Multiple array element sheets of the same side form a line.
7. according to a kind of photoacoustic ultrasound joint imaging device accurately measuring melanoma thickness according to claim 6, it is characterized in that: each array element sheet is all 5 degree to 10 degree angles with skin surface; Two array element sheets with group become splayed, and splay big uncork is towards skin.
8. according to a kind of photoacoustic ultrasound joint imaging device accurately measuring melanoma thickness according to claim 3, it is characterized in that: the shape of described line focus lens is strip, convex surface is downward, and burnt length is 22-30 millimeter.
9. accurately measure a photoacoustic ultrasound joint imaging method for melanoma thickness, use a kind of photoacoustic ultrasound joint imaging device accurately measuring melanoma thickness according to any one of claim 1 to 8, it is characterized in that: comprise the steps:
A. computer control and imaging system control the operation of laser transmitting system, laser transmitting system Emission Lasers, simultaneously for photoacoustic imaging and ultra sonic imaging provide triggering signal, one tunnel triggering signal directly triggers photoacoustic signal collection, i.e. step b, another road triggering signal is through time delay module Triggered ultrasound signals collecting, i.e. step c, realizes photoacoustic imaging and the substep of ultra sonic imaging at same collection position triggers;
B. laser controls and signal processing system through FPGA, signal through ultrasonic reception/transmitter unit amplifies, skin is irradiated again by the double-mode integrated detector of hand-held, the photoacoustic signal of the ultrasonic detector array received skin reflex of the double-mode integrated detector of hand-held, photoacoustic signal is returned ultrasonic reception/transmitter unit and become the signal of telecommunication, the signal of telecommunication controls and arrives computer after signal processing system to control and imaging system through digital to analog converter, FPGA; Wherein FPGA control and signal processing system are under photoacoustic imaging pattern, and gather photoacoustic signal by ultrasonic reception/transmitter unit, be used for carrying out photoacoustic imaging restructuring, ultrasonic reception/transmitter unit only works in receiving mode;
C. laser to control and signal processing system excitation ultrasound reception/transmitter unit transmits through time delay module and FPGA, the double-mode integrated detector of signal excitation hand-held produces ultrasonic signal and irradiates skin, the ultrasonic signal of the ultrasonic detector array received skin reflex of the double-mode integrated detector of hand-held, ultrasonic signal is returned ultrasonic reception/transmitter unit and become the signal of telecommunication, the signal of telecommunication controls and arrives computer after signal processing system to control and imaging system through digital to analog converter, FPGA; Wherein, when FPGA control and signal processing system gauge tap select ultrasound imaging mode time, FPGA controls and signal processing system controls ultrasonic reception/transmitter unit transmitting ultrasonic signal and gathers ultrasonic signal, be used for carrying out ultra sonic imaging restructuring, ultrasonic reception/transmitter unit works in reception/emission mode;
D. computer control and imaging system comprise the double-mode imaging pattern containing photoacoustic imaging and ultra sonic imaging, generate photoacoustic image and ultrasonoscopy, are provided the test result of melanoma thickness by two width images.
10. according to a kind of photoacoustic ultrasound joint imaging method accurately measuring melanoma thickness according to claim 9, it is characterized in that: in steps d, epidermis position is indicated by ultrasonoscopy, melanoma upper surface position is indicated: measure melanoma lower surface signal distance upper surface signal when photoacoustic signal and be greater than 1.5mm by photoacoustic image, or photoacoustic signal lower surface Signal-to-Noise is when being less than 6db, melanoma lower surface position is indicated by ultrasonoscopy, otherwise, then melanoma lower surface position is indicated by photoacoustic image.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201510788892.0A CN105232004A (en) | 2015-11-16 | 2015-11-16 | Opto-acoustic-ultrasonic united imaging device and imaging method for precisely measuring thickness of melanoma |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201510788892.0A CN105232004A (en) | 2015-11-16 | 2015-11-16 | Opto-acoustic-ultrasonic united imaging device and imaging method for precisely measuring thickness of melanoma |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CN105232004A true CN105232004A (en) | 2016-01-13 |
Family
ID=55030039
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN201510788892.0A Pending CN105232004A (en) | 2015-11-16 | 2015-11-16 | Opto-acoustic-ultrasonic united imaging device and imaging method for precisely measuring thickness of melanoma |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN105232004A (en) |
Cited By (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN106085962A (en) * | 2016-06-20 | 2016-11-09 | 上海交通大学 | A kind of device for detecting and separate circulation melanoma cell |
| CN106308750A (en) * | 2016-08-22 | 2017-01-11 | 重庆医科大学附属儿童医院 | Melanin content change detection method |
| CN108594714A (en) * | 2018-05-18 | 2018-09-28 | 南京大学 | A kind of acquisition and the pretreatment system of restructural echo impulse and photoacoustic signal |
| CN109507117A (en) * | 2018-11-12 | 2019-03-22 | 中国科学技术大学 | A kind of micro-nano image checking experimental provision based on optoacoustic beam shaping |
Citations (10)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN1555764A (en) * | 2004-01-06 | 2004-12-22 | 华南师范大学 | Method of biological tissue optical and ultrasonic collection and tomographic imaging and its device |
| CN101301201A (en) * | 2008-07-03 | 2008-11-12 | 刘国栋 | Detecting device integrated with light sound ultrasonic excitation and sensor |
| CN101563035A (en) * | 2006-12-19 | 2009-10-21 | 皇家飞利浦电子股份有限公司 | Combined photoacoustic and ultrasound imaging system |
| US20110117028A1 (en) * | 2007-12-13 | 2011-05-19 | Board Of Trustees Of The University Of Arkansas | Device and method for in vivo noninvasive magnetic manipulation of circulating objects in bioflows |
| CN102551810A (en) * | 2012-03-09 | 2012-07-11 | 华南师范大学 | Multichannel synchronous real-time digitalized photoacoustic imaging device and method |
| CN102621115A (en) * | 2012-02-27 | 2012-08-01 | 华南师范大学 | Confocal simultaneous opto-acoustic imaging and fluorescence imaging method and device |
| CN102743191A (en) * | 2012-06-28 | 2012-10-24 | 华南师范大学 | Focusing rotary scanning photoacoustic ultrasonic blood vessel endoscope imaging device and focusing rotary scanning photoacoustic ultrasonic blood vessel endoscope imaging method |
| CN103654867A (en) * | 2013-12-27 | 2014-03-26 | 深圳先进技术研究院 | Imaging probe and imaging device with same |
| CN103690141A (en) * | 2013-12-26 | 2014-04-02 | 广州佰奥廷电子科技有限公司 | Internal rectal optical, optoacoustic and ultrasonic multimode imaging endoscope and imaging method thereof |
| CN104545991A (en) * | 2013-10-22 | 2015-04-29 | 三星电子株式会社 | Wideband ultrasonic probe for photoacoustic image and ultrasound image |
-
2015
- 2015-11-16 CN CN201510788892.0A patent/CN105232004A/en active Pending
Patent Citations (10)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN1555764A (en) * | 2004-01-06 | 2004-12-22 | 华南师范大学 | Method of biological tissue optical and ultrasonic collection and tomographic imaging and its device |
| CN101563035A (en) * | 2006-12-19 | 2009-10-21 | 皇家飞利浦电子股份有限公司 | Combined photoacoustic and ultrasound imaging system |
| US20110117028A1 (en) * | 2007-12-13 | 2011-05-19 | Board Of Trustees Of The University Of Arkansas | Device and method for in vivo noninvasive magnetic manipulation of circulating objects in bioflows |
| CN101301201A (en) * | 2008-07-03 | 2008-11-12 | 刘国栋 | Detecting device integrated with light sound ultrasonic excitation and sensor |
| CN102621115A (en) * | 2012-02-27 | 2012-08-01 | 华南师范大学 | Confocal simultaneous opto-acoustic imaging and fluorescence imaging method and device |
| CN102551810A (en) * | 2012-03-09 | 2012-07-11 | 华南师范大学 | Multichannel synchronous real-time digitalized photoacoustic imaging device and method |
| CN102743191A (en) * | 2012-06-28 | 2012-10-24 | 华南师范大学 | Focusing rotary scanning photoacoustic ultrasonic blood vessel endoscope imaging device and focusing rotary scanning photoacoustic ultrasonic blood vessel endoscope imaging method |
| CN104545991A (en) * | 2013-10-22 | 2015-04-29 | 三星电子株式会社 | Wideband ultrasonic probe for photoacoustic image and ultrasound image |
| CN103690141A (en) * | 2013-12-26 | 2014-04-02 | 广州佰奥廷电子科技有限公司 | Internal rectal optical, optoacoustic and ultrasonic multimode imaging endoscope and imaging method thereof |
| CN103654867A (en) * | 2013-12-27 | 2014-03-26 | 深圳先进技术研究院 | Imaging probe and imaging device with same |
Non-Patent Citations (5)
| Title |
|---|
| CHULHONG KIM等: "In Vivo Molecular Photoacoustic Tomography of Melanomas Targeted by Bioconjugated Gold Nanocages", 《ACSNANO》 * |
| K. DAOUDI等: "Handheld probe integrating laser diode and ultrasound transducer array for ultrasound/photoacoustic dual modality imaging", 《OPTICS EXPRESS》 * |
| LIHONG V. WANG等: "Photoacoustic Tomography: In Vivo Imaging from Organelles to Organs", 《SCIENCE》 * |
| 吴宁等: "光声层析成像研究进展", 《中国医疗设备》 * |
| 王雅婷: "光声超声双模态显微成像在皮肤黑色素瘤检测中的应用基础研究", 《华南师范大学硕士学位论文》 * |
Cited By (6)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN106085962A (en) * | 2016-06-20 | 2016-11-09 | 上海交通大学 | A kind of device for detecting and separate circulation melanoma cell |
| CN106085962B (en) * | 2016-06-20 | 2022-03-22 | 上海交通大学 | Device for detecting and separating circulating melanoma cells |
| CN106308750A (en) * | 2016-08-22 | 2017-01-11 | 重庆医科大学附属儿童医院 | Melanin content change detection method |
| CN108594714A (en) * | 2018-05-18 | 2018-09-28 | 南京大学 | A kind of acquisition and the pretreatment system of restructural echo impulse and photoacoustic signal |
| CN109507117A (en) * | 2018-11-12 | 2019-03-22 | 中国科学技术大学 | A kind of micro-nano image checking experimental provision based on optoacoustic beam shaping |
| CN109507117B (en) * | 2018-11-12 | 2020-04-03 | 中国科学技术大学 | Micro-nano imaging detection experimental device based on photoacoustic beam shaping |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| CN102596049B (en) | Photo-acoustic device | |
| CN105092705B (en) | The multi-modal signal detecting method and device of a kind of steel rail defect | |
| CN100456016C (en) | Multi-channel electronic parallel scanning photoacoustic real-time tomo graphic-imaging method and apparatus thereof | |
| CN100446730C (en) | Photoacoustic imaging and chromatographic imaging method based on acoustic lens and apparatus thereof | |
| JP5538856B2 (en) | Photoacoustic device | |
| CN103356234B (en) | Subject information acquisition device | |
| CN105232004A (en) | Opto-acoustic-ultrasonic united imaging device and imaging method for precisely measuring thickness of melanoma | |
| CN101690672A (en) | Array probe-based real-time photoacoustic imaging device | |
| CN104545811A (en) | Intravascular imaging system and method | |
| JP2000517414A (en) | Method and apparatus for three-dimensional ultrasonic microscopy using short pulse excitation and three-dimensional ultrasonic microscope used therein | |
| JP2012081251A (en) | Object information acquiring apparatus | |
| CN104706323A (en) | High-speed large-view-field multi-spectral photoacoustic imaging method and device | |
| CN102525550A (en) | Measuring apparatus | |
| CN100434042C (en) | Method of biological tissue optical and ultrasonic collection and tomographic imaging and its device | |
| CN107115098A (en) | Based on one-dimensional non-focusing and the double array scanning imaging devices of focusing ultrasound and method | |
| CN108606777A (en) | Optoacoustic computed tomography system based on adjustable focus type fibre optical sensor | |
| WO2020167870A1 (en) | Transparent ultrasound transducers for photoacoustic imaging | |
| CN101336832A (en) | Pulse type optical acoustic scanning soft-tissue imaging method and device | |
| CN106500635A (en) | Cuboid workpiece dimension measuring system based on laser-ultrasound | |
| CN101290351A (en) | Optical recognition and distance measurer | |
| CN105043524A (en) | Laser speckle defocused imaging-based vibration detection method | |
| JP5572023B2 (en) | measuring device | |
| CN104856728A (en) | Photoacoustic device | |
| JP2012173136A (en) | Optoacoustic imaging device, probe unit used therefor, and operation method of optoacoustic imaging device | |
| CN105686800B (en) | Subject information acquisition device and its control 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 | ||
| RJ01 | Rejection of invention patent application after publication | ||
| RJ01 | Rejection of invention patent application after publication |
Application publication date: 20160113 |