La ricerca è sostenuta dalla borsa di Tier 2 finanziata dal Ministero dell&#39;Istruzione di Singapore (ARC2 / 15: M4020238) e dal Consiglio Nazionale di Ricerca Medica del Ministero della Salute di Singapore (NMRC / OFIRG / 0005/2016: M4062012). Gli autori vorrebbero ringraziare il signor Chow Wai Hoong Bobby per l&#39;aiuto della macchina.

Tutti gli esperimenti su animali sono stati eseguiti secondo le linee guida ei regolamenti approvati dal Comitato istituzionale per la cura e l&#39;uso degli animali della Nanyang Technological University di Singapore (numero di protocollo animale ARF-SBS / NIE-A0263). 1. Descrizione del sistema <ol><li> Montare il PLD all&#39;interno dello scanner circolare, come mostrato nella Figura 1a . Collegare il PLD all&#39;unità laser driver (LDU). NOTA: Il PLD fornisce impulsi ~ 136 ns ad una lunghezza d&#39;onda di ~ 803 nm, con un&#39;energia di impulso massima di ~ 1,42 mJ e una velocità di ripetizione fino a 7 kHz. L&#39;unità di azionamento laser (LDU) comprende: un regolatore di temperatura, un&#39;alimentazione variabile, un alimentatore (12 V) e un generatore di funzioni; Vedere la tabella dei materiali. L&#39;alimentatore variabile viene utilizzato per controllare l&#39;energia laser e il generatore di funzioni viene utilizzato per modificare la frequenza di ripetizione del PLD. </li><li> Accendere il laser PLD. Impostare la frequenza di ripetizione PLD su &quot;7.000&quot; HZ utilizzando il generatore di funzioni nella LDU. Aumenta l&#39;energia di impulso a 1,42 mJ impostando la tensione dell&#39;alimentazione variabile a &quot;3.1&quot; V. </li><li> Montare il diffusore ottico (OD) davanti alla finestra di uscita PLD per rendere omogeneo il fascio di uscita, come mostrato nella Figura 1a . NOTA: Utilizzare un diffusore con una grana fine ( cioè 1.500 polvere di graniglia). </li><li> Montare l&#39;UST focalizzato sul supporto UST, in modo tale che si affaccia al centro dell&#39;area di scansione, come mostrato nella Figura 1a . NOTA: La frequenza centrale dell&#39;UST è di 2,25 MHz e la lunghezza focale è di 1,9 pollici. </li><li> Posizionare il rivelatore ad ultrasuoni all&#39;interno del serbatoio acrilico, come mostrato nella Figura 1a . Riempire il serbatoio con acqua in modo che l&#39;UST sia completamente immersa. NOTA: Un mezzo d&#39;acqua è usato per abbinare il segnale fotoacustico dal cervello (campione) all&#39;UST. Un serbatoio acrilico d&#39;acqua (WT; vedi la tabella dei materiali) è stato personalizzato-designed per l&#39;imaging di piccole animali. Lo schema del disegno del serbatoio dell&#39;acqua è mostrato in figura 1b . </li><li> Controllare il segnale PA dal campione usando un impianto pulser / ricevitore (PRU, vedere la tabella dei materiali ). NOTA: Questi segnali sono stati digitalizzati da una scheda DAQ a 12 bit (vedere la tabella dei materiali ) ad una velocità di campionamento di 100 MS / s e sono stati salvati in un computer. </li></ol> 2. Preparazione degli animali per la formazione del cervello del cervello NOTA: Il sistema PLD-PAT sopra descritto è stato dimostrato per l&#39;imaging di cervelli animali piccoli. Per questi esperimenti sono stati utilizzati ratti femmine sani (vedi tabella dei materiali ). <ol><li> Anestetizza l&#39;animale mediante iniezione di un cocktail di 2 ml di ketamina, 1 ml di xilazina e 1 ml di soluzione salina (dosaggio di 0,2 ml / 100 g). </li><li> Rimuovere la pelliccia sul cuoio capelluto dell&#39;animale usando un tagliatore di capelli. Applicare delicatamente la crema di rimozione dei capelli alla rasataZona per ulteriore esaurimento della pelliccia. <ol><li> Rimuovere la crema applicata dopo 4-5 minuti utilizzando un tampone di cotone. </li><li> Applicare unguento artificiale di lacrima agli occhi dell&#39;animale per evitare la secchezza dovuta all&#39;anestesia e all&#39;illuminazione laser. </li></ol></li><li> Montare il supporto animale su misura (vedi tabella dei materiali ) dotato di una maschera di respirazione (vedere la tabella dei materiali ) su una presa di laboratorio. </li><li> Posizionare l&#39;animale in posizione predisposta sul supporto. Fissarlo al supporto usando un nastro chirurgico per evitare il movimento dell&#39;animale durante l&#39;imaging. </li><li> Assicurarsi che la maschera respiratoria copre il naso e la bocca del ratto per fornire l&#39;anestetico inalato. </li></ol> 3. In Vivo Rat Brain Imaging <ol><li> Collegare la maschera di respirazione alla macchina di anestesia. Accendere la macchina anestesia e impostarla per fornire 1,0 L / min di ossigeno con 0,75% isoflurano. <ol><li> Bloccare l&#39;ossimetro ad impulsi ad essoPer controllare la condizione fisiologica dell&#39;animale. </li></ol></li><li> Applicare uno strato di gel ecografico incolore al cuoio capelluto del ratto. Regolare la posizione del jack del laboratorio al centro dello scanner. La maschera di respirazione è personalizzata in base alla finestra di imaging. Il 10% del cono a cono commercialmente disponibile viene tagliato poi collegato ad un pezzo di guanto. <ol><li> Regolare manualmente l&#39;altezza del jack di laboratorio in modo che il piano di imaging sia al centro dell&#39;UST. </li></ol></li><li> Impostare i parametri nel software di acquisizione dati (vedere la tabella dei materiali) come richiesto. Esegui il programma software di acquisizione dati per avviare l&#39;acquisizione ( ossia, l&#39; imaging). NOTA: il programma viene utilizzato per ruotare l&#39;UST e raccogliere segnali A-line PA. Le linee A raccolte verranno salvate sul computer. </li><li> Osservare l&#39;animale durante l&#39;intero periodo di imaging e procedere alla ricostruzione PAT dopo che l&#39;imaging è completo. </li><li> Dopo l&#39;acquisizione dei dati è finita,Ricostruire l&#39;immagine del cervello trasversale dalle linee A utilizzando il programma software di ricostruzione. </li><li> Spegnere il sistema di anestesia, rimuovere l&#39;animale dal palco, riportarlo nella sua gabbia e controllarlo fino a quando non ricupera la coscienza. NOTA: Ad esempio, se l&#39;UST è ruotato per 5 s, il PLD fornisce 35.000 (= 5 x 7.000) impulsi e l&#39;UST raccoglie 35.000 linee A. Le 35.000 linee A vengono ridotte a 500 con una media di oltre 70 segnali (dopo aver effettuato la mediazione di linee A = 35.000 / 70 = 500). La figura 1c illustra l&#39;illuminazione degli impulsi laser e della collezione A-line. Dovrebbe essere utilizzato un programma di ricostruzione basato sull&#39;algoritmo di proiezione di ritardo e somma. </li></ol><img alt="Figura 1" class="xfigimg" src="/files/ftp_upload/55811/55811fig1.jpg" /> Figura 1: Schemi del sistema PLD-PAT. (A) Schema del PLD-PAT. PLD: diodo pulsato-laser, CSP: circuitoUnità di pulser / ricevitore, UST: trasduttore ad ultrasuoni, WT: serbatoio d&#39;acqua, PF: film polimerici e DAQ: unità di controllo laser, AM: anestesia, M: motore, MPU: Scheda di acquisizione dati. ( B ) Schema del serbatoio dell&#39;acqua, vista dall&#39;alto (1) e vista in sezione trasversale (2) per l&#39;imaging cerebrale in animale in vivo . A: metrico Vite, B: piastra anulare acrilica, C: anello &quot;O&quot; in silicone, D: copertura in polietilene trasparente di 100 μm. Il serbatoio aveva un foro di diametro di 9 cm al suo fondo ed è stato sigillato con una membrana in polietilene ad ultrasuoni e otticamente trasparente di 100 μm. ( C ) Schema dell&#39;illuminazione degli impulsi laser dalle linee PLD e A, raccolta in un tempo di scansione continuo di 5 s. <a href="http://ecsource.jove.com/files/ftp_upload/55811/55811fig1large.jpg" target="_blank">Clicca qui per visualizzare una versione più grande di questa figura.</a>

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Gli autori non hanno alcun interesse finanziario rilevante nel manoscritto e nessun altro potenziale conflitto di interessi da divulgare.

Questo lavoro presenta un protocollo per eseguire un&#39;immagine cerebrale in vivo su ratti utilizzando un sistema PLD-PAT. Il protocollo include una descrizione dettagliata del sistema di imaging e del suo allineamento, nonché un&#39;illustrazione dell&#39;immagine cerebrale sui ratti. I sistemi PAT esistenti basati su OPO sono costosi e ingombranti e possono fornire un&#39;immagine trasversale in 5-10 min. Il sistema PLD-PAT è compatto, portatile e a basso costo e può fornire immagini di buona qualità in...

<html> La tomografia fotoacustica (PAT) è una modalità di imaging ibrida che ha molte applicazioni in studi clinici e preclinici 1 , 2 , 3 , 4 , 5 . In PAT, gli impulsi laser nanosecondi irradiano il tessuto biologico. L&#39;assorbimento della luce incidente dai cromofori tessuti porta ad un aumento locale della temperatura, che produce quindi onde di pressione emesse sotto forma di onde sonore. Un rilevatore ad ultrasuoni raccoglie i segnali fotoacustici in varie posizioni attorno al campione. I segnali fotoacustici (PA) vengono ricostruiti utilizzando vari algoritmi (come un algoritmo di ritardo e somma) 6 per generare l&#39;immagine fotoacustica. Questa modalità di imaging ibrida offre immagini ad alta risoluzione, tessuto profondo e elevato contrasto di assorbimento ottico 7 ,Class = &quot;xref&quot;&gt; 8. Recentemente, una profondità di imaging di ~ 12 cm è stata raggiunta nel tessuto del petto di pollo con l&#39;aiuto di una lunghezza d&#39;onda più lunga (~ 1.064 nm) e un agente di contrasto esogeno chiamato fosforoftalocyanina. Questa sensibilità di profondità è molto più alta della sensibilità della profondità di altri metodi ottici, come la microscopia a fluorescenza confocale, la microscopia a fluorescenza a due fotoni, la tomografia a 10 coerenza ottica, 11 ecc. Utilizzando più di una lunghezza d&#39;onda, il PAT può dimostrare cambiamenti strutturali e funzionali negli organi . Per molte malattie umane, i modelli di piccoli animali sono stati ben consolidati 12 , 13 , 14 , 15 . Per l&#39;imaging di piccoli animali sono state dimostrate diverse modalità. Su tutti questi approcci, l&#39;imaging PA ha guadagnato l&#39;attenzione piuttosto rapidamente a causa dei vantaggi di cui sopra. PAPÀT ha mostrato il suo potenziale di imaging dei vasi sanguigni nei tessuti e negli organi ( cioè cuore, polmoni, fegato, occhi, milza, cervello, pelle, midollo spinale, rene, ecc. ) Dei piccoli animali 4 , 16 , 17 , 18 . PAT è una modalità ben consolidata per l&#39;imaging cerebrale di piccoli animali. Le onde PA vengono prodotte a causa dell&#39;assorbimento di luce dai cromofori, quindi la PAT a lunghezza d&#39;onda multipla consente la mappatura della concentrazione totale di emoglobina (HbT) e della saturazione dell&#39;ossigeno (SO 2 ) 19 , 20 , 21 , 22 . L&#39;imaging neurovascolare cerebrale è stato ottenuto con l&#39;aiuto di agenti di contrasto esogeni 12 , 23 , 24 . La modalità PA può contribuire a dare una migliore comprensione della salute del cervelloFornendo informazioni a livello molecolare e genetico. Per l&#39;imaging di piccole animali, i laser Nd: YAG / OPO sono ampiamente utilizzati come sorgenti di eccitazione PAT. Questi laser erogano ~ 5 ns impulsi a infrarossi vicino ad energia (~ 100 mJ alla finestra di uscita OPO) ad una frequenza di ripetizione ~ 10 Hz. Il sistema PA dotato di tali laser è costoso e ingombrante e consente l&#39;imaging a bassa velocità con trasduttori ad ultrasuoni a singolo elemento (UST) a causa della bassa frequenza di ripetizione della sorgente laser. Un tipico tempo di acquisizione A-line in tali sistemi PA è ~ 5 min per sezione 25 . Un sistema di imaging con un così lungo tempo di misurazione non è l&#39;ideale per l&#39;imaging di piccole animali, perché è difficile controllare i parametri fisiologici per l&#39;imaging a tutto il corpo, l&#39;imaging funzionale risolti in tempo, ecc. Adottando più UST di un singolo elemento, array O un laser ad alta repetizione, è possibile aumentare la velocità di imaging di PAsistemi. Utilizzando solo un UST a un singolo elemento per raccogliere tutti i segnali PA intorno al campione limiterà la velocità di imaging del sistema. Sono stati dimostrati più UST di un singolo elemento disposti in geometria circolare o semicircolare per tecniche di imaging ad alta velocità e altamente sensibili. Gli UST 26 basati sugli array, come gli array array lineari, semicircolari, circolari e volumetrici, sono stati utilizzati con successo per l&#39;imaging in tempo reale 1 . Questi UST basati su matrici aumenteranno la velocità di imaging e riducono la sensibilità di misura, ma sono costosi. Tuttavia, la velocità di imaging dei sistemi PA che utilizzano UST a matrice è ancora limitata dalla velocità di ripetizione del laser. La tecnologia laser a pulsazione avanzata per produrre diodi ad impulsi ad alta reputazione (PLD). 7.000 fotogrammi / s di imaging fotoacustico B-scansione è stata dimostrata con PLD utilizzando una piattaforma clinica a ultrasuoni 27 . Tali PLD possono migliorare la velocità di imaging di thE PAT, anche con la geometria di scansione circolare UST a singolo elemento. Gli UST a singolo elemento sono meno costosi e molto sensibili, a differenza degli UST basati su matrici. Negli ultimi dieci anni, sono stati riportati scarsi risultati sull&#39;utilizzo di PLD ad alta ripetizione come fonte di eccitazione per l&#39;imaging PA. È stata dimostrata una PLD vicino a infrarossi a fibra per l&#39;imaging PA di fantasmi 28 . L&#39;imaging in vivo dei vasi sanguigni ad una profondità di 1 mm sotto la pelle umana è stato dimostrato utilizzando PLD a basso consumo energetico 29 . È stato riportato un microscopio fotoacustico a risoluzione ottica (ORPAM) basato su PLD. Utilizzando PLD, è stata dimostrata un&#39;immagine profonda di 1,5 cm ad una velocità di fotogramma di 0,43 Hz. Recentemente, un sistema PLD-PAT è stato riferito che ha fornito immagini in breve come ~ 3 s e ad una ~ 2 cm profondità di imaging nel tessuto biologico 25 , 31 . Questo studio ha dimostrato che un tale sistema a basso costo e compatto può offrire un alto quaAnche a velocità elevate. Il sistema PLD-PAT può essere utilizzato per l&#39;imaging fotoacoustico ad alta velocità (7.000 fps), l&#39;imaging surgelico dei vasi sanguigni, l&#39;imaging delle dita, l&#39;imaging dei tessuti a due centimetri, l&#39;immagine cerebrale a piccole animali, ecc. La lunghezza singola e Impulsi a basso impulso di energia da PLD limitano la sua applicazione a immagini multi-spettrali e profonde. Sono stati condotti esperimenti su piccoli animali che utilizzano lo stesso sistema PLD-PAT usato per applicazioni pre-cliniche. Lo scopo di questo lavoro è quello di fornire la dimostrazione sperimentale visualizzata del sistema PLD-PAT per l&#39;imaging cerebrale a sezione trasversale 2D in animali vivi.

<table><tbody><tr><td>Pulsed laser diode</td><td>Quantel, France</td><td>QD-Q1910-SA-TEC</td><td>It is the excitation laser source with specifications 803 nm, 1.4 mJ per pulse, 136 ns pulse, 7 kHz maximum, dimentions : 11.0 x 6.0 x 3.6 cm, weight: ~150 gm</td></tr><tr><td>Stepper motor with gearbox</td><td>LIN Engineering (Servo Dynamics)</td><td>Motor: CO-5718-01P, Gearbox: DPL64/1, I = 10 for NEMA 23; power supply PW100-48</td><td>To move the detector holder in a circular geometry. Torque: 2.08 N-m, Rotor inertia: 2.6 kg-cm2</td></tr><tr><td>Ultrasonic pulser/receiver</td><td>Olympus</td><td>5072PR</td><td>To receive, filter and ampligy the PA signal from UST. Its bandwidth is 35 MHz, and gain is &amp;plusmn;59 dB.</td></tr><tr><td>Ultrasound Transducer</td><td>Olympus</td><td>V306-SU-NK-CF1.9IN/Q4200069</td><td>Ultrasonic sensors used for photoacoustic detection. Central freqency 2.25 MHz, 0.5 in, Cylindrical focus 1.9 inch</td></tr><tr><td>PCIe DAQ (Data acquisition) Card</td><td>GaGe</td><td>CSE4227/ A6000610/B0E00610</td><td>12 bit, 100 Ms/s, 2 channels, 1 Gs on board memory, PCIe x16 interface</td></tr><tr><td>Rats</td><td>In Vivos Pte Ltd, Singapore</td><td>NTac:SD, Sprague Dawley / SD</td><td>Female, weight 100 &amp;plusmn;10g</td></tr><tr><td>Acrylic water tank&amp;nbsp;</td><td>NTU workshop</td><td>Custom-made</td><td>It contains the water that acts as an acoustic coupling medium between brain and detector</td></tr><tr><td>Circular Scanner&amp;nbsp;</td><td>NTU workshop</td><td>Custom-made</td><td>Scanner is made out of Alluminum&amp;nbsp;</td></tr><tr><td>Anesthetic Machine</td><td>medical plus pte ltd</td><td>Non-Rebreathing Anaesthesia machine with oxygen concentrator.</td><td>Supplies oxygen and isoflurane to animal</td></tr><tr><td>Pulse Oxymeter portable</td><td>Medtronic</td><td>PM10N with veterinary sensor</td><td>Monitors the pulse oxymetry of the animal</td></tr><tr><td>Ultrasound gel</td><td>Progress/parker acquasonic gel</td><td>PA-GEL-CLEA-5000</td><td>Clear ultrasound gel</td></tr><tr><td>Data acqusison software</td><td>National Instruments Corporation,Austin,TX,USA)</td><td>NI LabVIEW 2015 SP1</td><td>LabVIEW based program was developed in our laboratory for controlling the stepper motor and acquring the PA singnals from the detector</td></tr><tr><td>Data processing software</td><td>Matlab (Mathworks, Natick, MA, USA)</td><td>Matlab R2012b</td><td>Matlab code for reconstruction of PA images was developed in our lab</td></tr><tr><td>Temperature controller&amp;nbsp;</td><td>LaridTech, MO,USA</td><td>MTTC1410</td><td>It will constantly control temperature of the PLD&amp;nbsp;</td></tr><tr><td>12 V power supply&amp;nbsp;</td><td>Voltcraft&amp;nbsp;</td><td>PPS-11810</td><td>To supply operating voltage for PLD</td></tr><tr><td>Variable power supply&amp;nbsp;</td><td>BASETech</td><td>BT-153</td><td>To change the laser output power</td></tr><tr><td>Funtion generator&amp;nbsp;</td><td>Funktionsgenerator</td><td>FG250D</td><td>To change the repetetion rate of the PLD. It will provide TTL signal to synchronize the DAQ with the laser excitation.</td></tr><tr><td>Animal distributor</td><td>In Vivos Pte Ltd, Singapore</td><td></td><td>Animal distributor that supplies small animals for research purpose.</td></tr><tr><td>Animal holder</td><td>NTU workshop</td><td>Custom-made</td><td>Used for holding the animal on its abdomen</td></tr><tr><td>Breathing mask</td><td>NTU workshop</td><td>Custom-made</td><td>Used along with animal holder to supply anesthesia mixture to the animal</td></tr><tr><td>Pentobarbital sodium</td><td>Valabarb</td><td></td><td>Used for euthanizing the animal after the expeirment.</td></tr><tr><td>Optical diffuser</td><td>Thorlabs</td><td>DG10-1500</td><td>Used to to make the laser beam homogeneous</td></tr></tbody></table>

a high-performance compact photoacoustic tomography system for in vivo small-animal brain imaging

L&#39; imaging in animale in vivo ha un ruolo importante da svolgere negli studi preclinici. La tomografia fotoacoustica (PAT) è una modalità di imaging ibrida emergente che presenta un grande potenziale sia per applicazioni precliniche che cliniche. I sistemi PAT (OPO-PAT) basati su oscillatori ottici convenzionali sono ingombranti e costosi e non possono fornire immagini ad alta velocità. Recentemente, i diodi pulsati (PLD) sono stati dimostrati con successo come sorgente di eccitazione alternativa per PAT. Il diodo a pulsazione laser PAT (PLD-PAT) è stato dimostrato con successo per l&#39;imaging ad alta velocità su fantasmi fotoacustici e tessuti biologici. Questo lavoro fornisce un protocollo sperimentale visualizzato per l&#39;imaging cerebrale in vivo usando PLD-PAT. Il protocollo comprende la configurazione compatta del sistema PLD-PAT e la sua descrizione, la preparazione degli animali per l&#39;imaging del cervello e una tipica procedura sperimentale per l&#39;imaging cerebrale a sezione trasversale 2D. Il sistema PLD-PAT è compatto e cost-efIn grado di fornire immagini ad alta velocità e di alta qualità. Le immagini del cervello raccolte in vivo a diverse velocità di scansione sono presentate.

I risultati in vivo di immagini cerebrali che dimostrano le capacità del sistema PLD-PAT descritto sono mostrate in questa sezione. Per dimostrare le capacità di imaging ad alta velocità del sistema PLD-PAT, è stata eseguita l&#39;imaging cerebrale in vivo di due diversi ratti sani. La Figura 2 mostra le immagini del cervello di un ratto femminile (93 g) a diverse velocità di scansione. Figura 2a e b mostr...

Watch this Scientific Journal Video about A High-performance Compact Photoacoustic Tomography System for In Vivo Small-animal Brain Imaging at JoVE.com

A High-performance Compact Photoacoustic Tomography System for In Vivo Small-animal Brain Imaging

È stato dimostrato un sistema compatto di tomografia fotoacoustica (PLD-PAT) basato su diodi laser a pulsazione per immagini ad alta velocità in cervello in vivo in piccoli animali.

Un sistema compatto di Tomografia Photoacoustico ad alte prestazioni per<em&gt; In Vivo</em&gt; Imaging cerebrale di piccole dimensioni

In vivo small-animal imaging has an important role to play in preclinical studies. Photoacoustic tomography (PAT) is an emerging hybrid imaging modality ...

a-high-performance-compact-photoacoustic-tomography-system-for-vivo

Universidad de Cartagena UDEC

Research

JoVE Journal

Bioengineering

A High-performance Compact Photoacoustic Tomography System for In Vivo Small-animal Brain Imaging

10.4K Views.  Nanyang Technological University.  È stato dimostrato un sistema compatto di tomografia fotoacoustica (PLD-PAT) basato su diodi laser a pulsazione per immagini ad alta velocità in cervello in vivo in piccoli animali. 

Video: A High-performance Compact Photoacoustic Tomography System for In Vivo Small-animal Brain Imaging

Three-dimensional Optical-resolution Photoacoustic Microscopy

Optical microscopy, providing valuable insights at the cellular and organelle levels, has been widely recognized as an enabling biomedical technology. As the mainstays of in vivo three-dimensional (3-D) optical microscopy, single-/multi-photon fluorescence microscopy and optical coherence tomography (OCT) have demonstrated their extraordinary sensitivities to fluorescence and optical scattering contrasts, respectively. However, the optical absorption contrast of biological tissues, which encodes essential physiological/pathological information, has not yet been assessable. 
The emergence of biomedical photoacoustics has led to a new branch of optical microscopy optical-resolution photoacoustic microscopy (OR-PAM)1, where the optical irradiation is focused to the diffraction limit to achieve cellular1 or even subcellular2 level lateral resolution. As a valuable complement to existing optical microscopy technologies, OR-PAM brings in at least two novelties. First and most importantly, OR-PAM detects optical absorption contrasts with extraordinary sensitivity (i.e., 100%). Combining OR-PAM with fluorescence microscopy3 or with optical-scattering-based OCT4 (or with both) provides comprehensive optical properties of biological tissues. Second, OR-PAM encodes optical absorption into acoustic waves, in contrast to the pure optical processes in fluorescence microscopy and OCT, and provides background-free detection. The acoustic detection in OR-PAM mitigates the impacts of optical scattering on signal degradation and naturally eliminates possible interferences (i.e., crosstalks) between excitation and detection, which is a common problem in fluorescence microscopy due to the overlap between the excitation and fluorescence spectra. 
Unique for optical absorption imaging, OR-PAM has demonstrated broad biomedical applications since its invention, including, but not limited to, neurology5, 6, ophthalmology7, 8, vascular biology9, and dermatology10. In this video, we teach the system configuration and alignment of OR-PAM as well as the experimental procedures for in vivo functional microvascular imaging.

Optical-resolution photoacoustic microscopy (OR-PAM) is an emerging technology capable of imaging optical absorption contrasts in vivo with cellular resolution and sensitivity. Here, we provide a visualized instruction on the experimental protocols of OR-PAM, including system configuration, system alignment, typical in vivo experimental procedures, and functional imaging schemes.

Tridimensionale con risoluzione ottica Microscopia fotoacustico

Optical microscopy, providing valuable insights at the cellular and organelle levels, has been widely recognized as an enabling biomedical technology. As ...

Ricerca

Bioingegneria

Computed Tomography-guided Time-domain Diffuse Fluorescence Tomography in Small Animals for Localization of Cancer Biomarkers

Small animal fluorescence molecular imaging (FMI) can be a powerful tool for preclinical drug discovery and development studies1. However, light absorption by tissue chromophores (e.g., hemoglobin, water, lipids, melanin) typically limits optical signal propagation through thicknesses larger than a few millimeters2. Compared to other visible wavelengths, tissue absorption for red and near-infrared (near-IR) light absorption dramatically decreases and non-elastic scattering becomes the dominant light-tissue interaction mechanism. The relatively recent development of fluorescent agents that absorb and emit light in the near-IR range (600-1000 nm), has driven the development of imaging systems and light propagation models that can achieve whole body three-dimensional imaging in small animals3.
Despite great strides in this area, the ill-posed nature of diffuse fluorescence tomography remains a significant problem for the stability, contrast recovery and spatial resolution of image reconstruction techniques and the optimal approach to FMI in small animals has yet to be agreed on. The majority of research groups have invested in charge-coupled device (CCD)-based systems that provide abundant tissue-sampling but suboptimal sensitivity4-9, while our group and a few others10-13 have pursued systems based on very high sensitivity detectors, that at this time allow dense tissue sampling to be achieved only at the cost of low imaging throughput. Here we demonstrate the methodology for applying single-photon detection technology in a fluorescence tomography system to localize a cancerous brain lesion in a mouse model.
The fluorescence tomography (FT) system employed single photon counting using photomultiplier tubes (PMT) and information-rich time-domain light detection in a non-contact conformation11. This provides a simultaneous collection of transmitted excitation and emission light, and includes automatic fluorescence excitation exposure control14, laser referencing, and co-registration with a small animal computed tomography (microCT) system15. A nude mouse model was used for imaging. The animal was inoculated orthotopically with a human glioma cell line (U251) in the left cerebral hemisphere and imaged 2 weeks later. The tumor was made to fluoresce by injecting a fluorescent tracer, IRDye 800CW-EGF (LI-COR Biosciences, Lincoln, NE) targeted to epidermal growth factor receptor, a cell membrane protein known to be overexpressed in the U251 tumor line and many other cancers18. A second, untargeted fluorescent tracer, Alexa Fluor 647 (Life Technologies, Grand Island, NY) was also injected to account for non-receptor mediated effects on the uptake of the targeted tracers to provide a means of quantifying tracer binding and receptor availability/density27. A CT-guided, time-domain algorithm was used to reconstruct the location of both fluorescent tracers (i.e., the location of the tumor) in the mouse brain and their ability to localize the tumor was verified by contrast-enhanced magnetic resonance imaging.
Though demonstrated for fluorescence imaging in a glioma mouse model, the methodology presented in this video can be extended to different tumor models in various small animal models potentially up to the size of a rat17.

Diffuse fluorescence tomography offers a relatively low-cost and potentially high-throughout approach to preclinical in vivo tumor imaging. The methodology of optical data collection, calibration, and image reconstruction is presented for a computed tomography-guided non-contact time-domain system using fluorescent targeting of the tumor biomarker epidermal growth factor receptor in a mouse glioma model.

Tomografia Computerizzata guidata nel dominio del tempo Tomography Diffuse fluorescenza in animali di piccola taglia per la localizzazione dei biomarcatori tumorali

Small animal fluorescence molecular imaging (FMI) can be a powerful tool for preclinical drug discovery and development studies1. However, light ...

Medicina

Universal Hand-held Three-dimensional Optoacoustic Imaging Probe for Deep Tissue Human Angiography and Functional Preclinical Studies in Real Time

The exclusive combination of high optical contrast and excellent spatial resolution makes optoacoustics (photoacoustics) ideal for simultaneously attaining anatomical, functional and molecular contrast in deep optically opaque tissues. While enormous potential has been recently demonstrated in the application of optoacoustics for small animal research, vast efforts have also been undertaken in translating this imaging technology into clinical practice. We present here a newly developed optoacoustic tomography approach capable of delivering high resolution and spectrally enriched volumetric images of tissue morphology and function in real time. A detailed description of the experimental protocol for operating with the imaging system in both hand-held and stationary modes is provided and showcased for different potential scenarios involving functional and molecular studies in murine models and humans. The possibility for real time visualization in three dimensions along with the versatile handheld design of the imaging probe make the newly developed approach unique among the pantheon of imaging modalities used in today&#8217;s preclinical research and clinical practice.

We provide herein a detailed description of the experimental protocol for imaging with a newly developed hand-held optoacoustic (photoacoustic) system for three-dimensional functional and molecular imaging in real time. The demonstrated powerful performance and versatility may define new application areas of the optoacoustic technology in preclinical research and clinical practice.

Universale Mano libera tridimensionale optoacustica Imaging Probe per Deep Tissue angiografia umana e funzionali studi preclinici in tempo reale

The exclusive combination of high optical contrast and excellent spatial resolution makes optoacoustics (photoacoustics) ideal for simultaneously ...

Non-invasive Parenchymal, Vascular and Metabolic High-frequency Ultrasound and Photoacoustic Rat Deep Brain Imaging

Photoacoustics and high frequency ultrasound stands out as powerful tools for neurobiological applications enabling high-resolution imaging on the central nervous system of small animals. However, transdermal and transcranial neuroimaging is frequently affected by low sensitivity, image aberrations and loss of space resolution, requiring scalp or even skull removal before imaging. To overcome this challenge, a new protocol is presented to gain significant insights in brain hemodynamics by photoacoustic and high-frequency ultrasounds imaging with the animal skin and skull intact. The procedure relies on the passage of ultrasound (US) waves and laser directly through the fissures that are naturally present on the animal cranium. By juxtaposing the imaging transducer device exactly in correspondence to these selected areas where the skull has a reduced thickness or is totally absent, one can acquire high quality deep images and explore internal brain regions that are usually difficult to anatomically or functionally describe without an invasive approach. By applying this experimental procedure, significant data can be collected in both sonic and optoacoustic modalities, enabling to image the parenchymal and the vascular anatomy far below the head surface. Deep brain features such as parenchymal convolutions and fissures separating the lobes were clearly visible. Moreover, the configuration of large and small blood vessels was imaged at several millimeters of depth, and precise information were collected about blood fluxes, vascular stream velocities and the hemoglobin chemical state. This repertoire of data could be crucial in several research contests, ranging from brain vascular disease studies to experimental techniques involving the systemic administration of exogenous chemicals or other objects endowed with imaging contrast enhancement properties. In conclusion, thanks to the presented protocol, the US and PA techniques become an attractive noninvasive performance-competitive means for cortical and internal brain imaging, retaining a significant potential in many neurologic fields.

The present work describes a new protocol to perform non-invasive high-frequency ultrasound and photoacoustic based imaging on rat brain, to efficiently visualize deep subcortical regions and their vascular patterns by directing signals on skull foramina naturally present on animal cranium.

Non invasiva parenchimale, vascolare e metabolica ad alta frequenza ad ultrasuoni e fotoacustico Rat profonda Brain Imaging

Photoacoustics and high frequency ultrasound stands out as powerful tools for neurobiological applications enabling high-resolution imaging on the central ...

Neuroscienze

Switchable Acoustic and Optical Resolution Photoacoustic Microscopy for In Vivo Small-animal Blood Vasculature Imaging

Photoacoustic microscopy (PAM) is a fast-growing invivo imaging modality that combines both optics and ultrasound, providing penetration beyond the optical mean free path (~1 mm in skin) with high resolution. By combining optical absorption contrast with the high spatial resolution of ultrasound in a single modality, this technique can penetrate deep tissues. Photoacoustic microscopy systems can have either a low acoustic resolution and probe deeply or a high optical resolution and probe shallowly. It is challenging to achieve high spatial resolution and large depth penetration with a single system. This work presents an AR-OR-PAM system capable of both high-resolution imaging at shallow depths and low-resolution deep-tissue imaging of the same sample in vivo. A lateral resolution of 4 &#181;m with 1.4 mm imaging depth using optical focusing and a lateral resolution of 45 &#181;m with 7.8 mm imaging depth using acoustic focusing were successfully demonstrated using the combined system. Here,&#160;in vivo&#160;small-animal blood vasculature imaging is performed to demonstrate its biological imaging capability.

Switchable Acoustic and Optical Resolution Photoacoustic Microscopy for In Vivo Small-animal Blood Vasculature Imaging

Here a switchable acoustic resolution (AR) and optical resolution (OR) photoacoustic microscopy (AR-OR-PAM) system capable of both high resolution imaging at shallow depth and low resolution deep tissue imaging on the same sample in vivo is demonstrated.

Microscopio fotoacustico acustico e ottico<em&gt; In Vivo</em&gt; Piccolo animale Blood Imaging di Vasculature

Photoacoustic microscopy (PAM) is a fast-growing invivo imaging modality that combines both optics and ultrasound, providing penetration beyond the ...

Hand-held Clinical Photoacoustic Imaging System for Real-time Non-invasive Small Animal Imaging

Translation of photoacoustic imaging into the clinic is a major challenge. Handheld real-time clinical photoacoustic imaging systems are very rare. Here, we report a combined photoacoustic and clinical ultrasound imaging system by integrating an ultrasound probe with light delivery for small animal imaging. We demonstrate this by showing sentinel lymph node imaging in small animals along with minimally invasive real-time needle guidance. A clinical ultrasound platform with access to raw channel data allows the integration of photoacoustic imaging leading to a handheld real-time clinical photoacoustic imaging system. Methylene blue was used for sentinel lymph node imaging at 675 nm wavelength. Additionally, needle guidance with dual modal ultrasound and photoacoustic imaging was shown using the imaging system. Depth imaging of up to 1.5 cm was demonstrated with a 10 Hz laser at a photoacoustic imaging frame rate of 5 frames per second.

A clinical handheld photoacoustic imaging system will be demonstrated for real-time non-invasive small animal imaging.

Mano clinico fotoacustico sistema di Imaging per Imaging animale piccolo Non-invasivo in tempo reale

Translation of photoacoustic imaging into the clinic is a major challenge. Handheld real-time clinical photoacoustic imaging systems are very rare. Here, ...

Pulsed Laser Diode-Based Desktop Photoacoustic Tomography for Monitoring Wash-In and Wash-Out of Dye in Rat Cortical Vasculature

Photoacoustic (PA) tomography (PAT) imaging is an emerging biomedical imaging modality useful in various preclinical and clinical applications. Custom-made circular ring array-based transducers and conventional bulky Nd:YAG/OPO lasers inhibit translation of the PAT system to clinics. Ultra-compact pulsed laser diodes (PLDs) are currently being used as an alternative source of near-infrared excitation for PA imaging. High-speed dynamic in vivo imaging has been demonstrated using a compact PLD-based desktop PAT system (PLD-PAT). A visualized experimental protocol using the desktop PLD-PAT system is provided in this work for dynamic in vivo brain imaging. The protocol describes the desktop PLD-PAT system configuration, preparation of animal for brain vascular imaging, and procedure for dynamic visualization of indocyanine green (ICG) dye uptake and clearance process in rat cortical vasculature.&#160;

A compact pulsed laser diode-based desktop photoacoustic tomography (PLD-PAT) system is demonstrated for high-speed dynamic in vivo imaging of small animal cortical vasculature.

Tomografia fotoacustica basata su diodo laser pulsata per il monitoraggio del lavaggio e del lavaggio del colorante nella Vasculatura corticale del ratto

Photoacoustic (PA) tomography (PAT) imaging is an emerging biomedical imaging modality useful in various preclinical and clinical applications. ...

Dual Raster-Scanning Photoacoustic Small-Animal Imager for Vascular Visualization

Imaging of vascular networks on small animals has played an important role in basic biomedical research. Photoacoustic imaging technology has great potential for application in the imageology of small animals. The wide-field photoacoustic imaging of small animals can provide images with high spatiotemporal resolution, deep penetration, and multiple contrasts. Also, the real-time photoacoustic imaging system is desirable to observe the hemodynamic activities of small-animal vasculature, which can be used to research the dynamic monitoring of small-animal physiological features. Here, a dual-raster-scanning photoacoustic imager is presented, featuring a switchable double-mode imaging function. The wide-field imaging is driven by a two-dimensional motorized translation stage, while the real-time imaging is realized with galvanometers. By setting different parameters and imaging modes, in vivo visualization of small-animal vascular network can be performed. The real-time imaging can be used to observe pulse change and blood flow change of drug-induced, etc. The wide-field imaging can be used to track the growth change of tumor vasculature. These are easy to be adopted in various areas of basic biomedicine research.

A dual raster-scanning photoacoustic imager was designed, which integrated wide-field imaging and real-time imaging.

Doppia scansione Raster Photoacoustic Small-Animal Imager per la visualizzazione vascolare

Imaging of vascular networks on small animals has played an important role in basic biomedical research. Photoacoustic imaging technology has great ...

A High-Throughput Image-Guided Stereotactic Neuronavigation and Focused Ultrasound System for Blood-Brain Barrier Opening in Rodents

The blood-brain barrier (BBB) has been a major hurdle for the treatment of various brain diseases. Endothelial cells, connected by tight junctions, form a physiological barrier preventing large molecules (&#62;500 Da) from entering the brain tissue. Microbubble-mediated focused ultrasound (FUS) can be used to induce a transient local BBB opening, allowing larger drugs to enter the brain parenchyma.
In addition to large-scale clinical devices for clinical translation, preclinical research for therapy response assessment of drug candidates requires dedicated small animal ultrasound setups for targeted BBB opening. Preferably, these systems allow high-throughput workflows with both high-spatial precision as well as integrated cavitation monitoring, while still being cost effective in both initial investment and running costs.
Here, we present a bioluminescence and X-ray guided stereotactic small animal FUS system that is based on commercially available components and fulfills the aforementioned requirements. A particular emphasis has been placed on a high degree of automation facilitating the challenges typically encountered in high-volume preclinical drug evaluation studies. Examples of these challenges are the need for standardization in order to ensure data reproducibility, reduce intra-group variability, reduce sample size and thus comply with ethical requirements and decrease unnecessary workload. The proposed BBB system has been validated in the scope of BBB opening facilitated drug delivery trials on patient-derived xenograft models of glioblastoma multiforme and diffuse midline glioma.

The blood-brain barrier (BBB) can be temporarily disrupted with microbubble-mediated focused ultrasound (FUS). Here, we describe a step-by-step protocol for high-throughput BBB opening in vivo using a modular FUS system accessible for non-ultrasound experts.

Un neuronavigation stereotattico guidato da immagini ad alta produttività e un sistema ad ultrasuoni focalizzati per l'apertura della barriera ematico-encefalica nei roditori

The blood-brain barrier (BBB) has been a major hurdle for the treatment of various brain diseases. Endothelial cells, connected by tight junctions, form a ...

Imaging non invasivo integrato PAUSAT dell'intero cervello dell'ictus ischemico

Integrated Photoacoustic, Ultrasound, and Angiographic Tomography (PAUSAT) for NonInvasive Whole-Brain Imaging of Ischemic Stroke

Presented here is an experimental ischemic stroke study using our newly developed noninvasive imaging system that integrates three acoustic-based imaging technologies: photoacoustic, ultrasound, and angiographic tomography (PAUSAT). Combining these three modalities helps acquire multi-spectral photoacoustic tomography (PAT) of the brain blood oxygenation, high-frequency ultrasound imaging of the brain tissue, and acoustic angiography of the cerebral blood perfusion. The multi-modal imaging platform allows the study of cerebral perfusion and oxygenation changes in the whole mouse brain after stroke. Two commonly used ischemic stroke models were evaluated: the permanent middle cerebral artery occlusion (pMCAO) model and the photothrombotic (PT) model. PAUSAT was used to image the same mouse brains before and after a stroke and quantitatively analyze both stroke models. This imaging system was able to clearly show the brain vascular changes after ischemic stroke, including significantly reduced blood perfusion and oxygenation in the stroke infarct region (ipsilateral) compared to the uninjured tissue (contralateral). The results were confirmed by both laser speckle contrast imaging and triphenyltetrazolium chloride (TTC) staining. Furthermore, stroke infarct volume in both stroke models was measured and validated by TTC staining as the ground truth. Through this study, we have demonstrated that PAUSAT can be a powerful tool in noninvasive and longitudinal preclinical studies of ischemic stroke.

Autore in primo piano: Tomografia fotoacustica, ecografica e angiografica integrata (PAUSAT) per l'imaging non invasivo dell'intero cervello dell'ictus ischemico  

This work demonstrates the use of a multimodal ultrasound-based imaging platform for noninvasive imaging of ischemic stroke. This system allows for the quantification of blood oxygenation through photoacoustic imaging and impaired perfusion in the brain through acoustic angiography.

Tomografia fotoacustica, ecografica e angiografica integrata (PAUSAT) per l'imaging non invasivo dell'intero cervello dell'ictus ischemico

Presented here is an experimental ischemic stroke study using our newly developed noninvasive imaging system that integrates three acoustic-based imaging ...

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