<i>In vivo</i> volumetric monitoring of revascularization of traumatized skin using extended depth-of-field photoacoustic microscopy

doi:10.1007/s12200-020-1040-0

Front. Optoelectron.

2020, Vol. 13

Issue (4) : 307-317 https://doi.org/10.1007/s12200-020-1040-0

RESEARCH ARTICLE

In vivo volumetric monitoring of revascularization of traumatized skin using extended depth-of-field photoacoustic microscopy

Zhongwen CHENG¹, Haigang MA², Zhiyang WANG², Sihua YANG^1,²(

)

¹. MOE Key Laboratory of Laser Life Science & Institute of Laser Life Science, College of Biophotonics, South China Normal University, Guangzhou 510631, China
². Guangdong Provincial Key Laboratory of Laser Life Science, College of Biophotonics, South China Normal University, Guangzhou 510631, China

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Abstract

Faster and better wound healing is a critical medical issue. Because the repair process of wounds is closely related to revascularization, accurate early assessment and postoperative monitoring are very important for establishing an optimal treatment plan. Herein, we present an extended depth-of-field photoacoustic microscopy system (E-DOF-PAM) that can achieve a constant spatial resolution and relatively uniform excitation efficiency over a long axial range. The superior performance of the system was verified by phantom and in vivo experiments. Furthermore, the system was applied to the imaging of normal and trauma sites of volunteers, and the experimental results accurately revealed the morphological differences between the normal and traumatized skin of the epidermis and dermis. These results demonstrated that the E-DOF-PAM is a powerful tool for observing and understanding the pathophysiology of cutaneous wound healing.

Keywords photoacoustic microscopy (PAM) extended depth-of-field traumatized skin

Corresponding Author(s): Sihua YANG

Just Accepted Date: 08 June 2020 Online First Date: 13 July 2020 Issue Date: 31 December 2020

Cite this article:

Zhongwen CHENG,Haigang MA,Zhiyang WANG, et al. In vivo volumetric monitoring of revascularization of traumatized skin using extended depth-of-field photoacoustic microscopy[J]. Front. Optoelectron., 2020, 13(4): 307-317.

URL:

https://academic.hep.com.cn/foe/EN/10.1007/s12200-020-1040-0
https://academic.hep.com.cn/foe/EN/Y2020/V13/I4/307

Fig.1 Schematic illustration of the E-DOF-PAM (with an EF lens) and conventional GB-PAM (without an EF lens) systems. (a) Schematic of the E-DOF-PAM system. (b) Optical path of the GB-PAM system. E-DOF-PAM, extended depth-of-field photoacoustic microscopy; GB-PAM, Gaussian beam photoacoustic microscopy; L1, L2, L3, lenses; Mir., mirror; SMF, single-mode fiber; EF, elongated focus; NDF, neutral density filter; PD, photodiode; T1, T2, trigger; DAS, data acquisition system; FPGA, field programmable gate array; WT, water; UT, ultrasound transducer

Fig.2 Numerical simulation intensity distributions of the laser beams generated with and without elongated focus (EF) lenses in the x-z and x-y planes. (a) Calculated intensity distribution of the Bessel beam (with EF lens) along the z axis (optical axis) at the focal zone. (b) Corresponding laser beam intensity maps indicated by the dashed line A-A' in (a). (c) Calculated intensity distribution of the Gaussian beam (without EF lens) along the z axis. (d) Corresponding laser beam intensity maps indicated by the dashed line B-B' in (c)

Fig.3 Performance of the E-DOF-PAM system. (a) Acoustic pressure distribution of the transducer. (b) Pulse response of the detector at the focus. (c) Amplitude–frequency response of the detector. (d) Edge spread function (ESF) extracted from (e) along the dashed line and the line spread function (LSF) obtained by taking the derivative of the ESF by the conventional GB-PAM (without an EF lens) and E-DOF-PAM (with an EF lens) systems, respectively. (e) Photo of a sharp-edged surgical blade. (f) Lateral resolution of the GB-PAM and E-DOF-PAM systems vs. the depth along the z axis

Fig.4 PA image of human hairs acquired by the E-DOF-PAM and GB-PAM systems. (a) 3D schematic diagram of the phantom. (b) and (c) Maximum amplitude projection (MAP) PA images acquired by the E-DOF-PAM and GB-PAM systems, respectively. (d) and (e) Corresponding line profiles at positions indicated by dashed lines 1 and 2 are shown in (b) and (c). (f) Normalized PA amplitude versus the depth for the two systems

Fig.5 Verification of in vivo imaging abilities of the GB-PAM and E-DOF-PAM systems on uneven tissue in the middle finger of a volunteer. (a) and (b) MAP PA images acquired by the GB-PAM and E-DOF-PAM systems, respectively. (c) and (d) PA cross-sectional images along the dashed lines A-A' and B-B' in (a) and (b), respectively. (e) and (g) Corresponding PA cross-sectional images along the dashed lines at positons I and II in (c), respectively. (f) and (h) Corresponding PA cross-sectional images along the dashed lines at positons III and IV in (d), respectively. (i) and (j) Corresponding PA amplitude profiles along the dashed lines at positions I–IV in (c) and (d), respectively. EP, epidermis; SC, stratum corneum layer; SB, stratum basale. Scalar bar, 500 μm

Fig.6 Feasibility of the E-DOF-PAM system in the detection of uneven traumatized skin. (a) Photograph of another volunteer’s skin, where the normal and trauma sites, which are enclosed by dashed black and white boxes, were chosen for PA imaging. (b) and (c) MAP PA images corresponding to the normal and trauma sites. (d) and (e) PA cross-sectional images along dashed lines A-A' and B-B' in (c), respectively. (f)–(h) MAP PA images of the SC layer, SB layer, and vascular network beneath the epidermis, respectively. (i) Statistical analysis of the measured thickness and normalized PA amplitude of the SC of the normal and traumatized skin. (j) Corresponding line profiles along the lines C-C' and D-D' in (h). SC, stratum corneum; SB, stratum basale; ROI, region of interest. Scalar bar, 500 μm

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[1]	Guo HE,Bingbing LI,Sihua YANG. In vivo imaging of a single erythrocyte with high-resolution photoacoustic microscopy[J]. Front. Optoelectron., 2015, 8(2): 122-127.

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