Laser Speckle Contrast Imager


Full-field, video frame rate blood flow imaging

  • I expect to be using Moor Instrument’s technology for many years to come!

    Faisel Khan, PhD
    Ninewells Hospital & Medical School

  • I cannot rate the company or the staff highly enough.

    Jim House, PhD
    University of Portsmouth

  • We have found Moor equipment to be extremely dependable and innovative.

    Dean L. Kellogg, Jr., MD, Ph.D
    University of Texas Health Science Center

  • In a nutshell, moorFLPI-2 is the most user-friendly system for studying cerebral blood flow regulation in rodents.

    Chia-Yi (Alex) Kuan, MD, PhD
    Emory University School of Medicine

  • Laser Doppler Imager is a standard accurate method we now use in our cerebral blood flow and brain perfusion in our laboratory.

    Momoh A. Yakubu, PhD
    Texas Southern University

  • Moor Instruments have consistently provided excellent help and support for my research.

    Kim Gooding, PhD
    University of Exeter Medical School

  • It goes without saying that the company's imaging technology itself is superb!

    Gourav Banerjee
    Leeds Beckett University

  • We can't recommend Moor instruments highly enough. The technology is at the cutting edge and the support second to none.

    Paul Sumners, PhD
    London South Bank University

The moorFLPI-2 blood flow imager uses the laser speckle contrast technique to deliver real-time, high-resolution blood flow images, providing outstanding performance in a wide range of pre-clinical and clinical research applications.

Unique user-friendly features are offered by the ergonomically designed scan head and highly refined software package.

NEW! V5 software promote a smooth workflow and enable the high through-put required to scan cohorts quickly and accurately. Advanced analysis functions help you to draw sound conclusions from your blood flow images. For full details please click here.

NEW! New laser package offering image sizes ranging from 5.6mm x 7.5mm right up to 20cm x 30cm using a unique optical zoom function.

moorFLPI-2 highlights include;

  • Image any exposed tissue (skin or surgically exposed tissues) and species.
  • Easy to use, flexible and simple setup helps get you up and running quickly.
  • Three measurement modes with flexible sampling rates (spatial, temporal and sliding window algorithms) to optimise your data for frame rate, spatial resolution and file size.
  • Best spatial resolution of 10 microns per pixel.
  • Real-time video frames rates.
  • Image areas range from 5.6mm x 7.5mm to 20cm x 30cm with a unique, motorised optical zoom and auto focus.
  • Colour photo and blood flow images provided by a unique single camera, RGB illumination system. Blood flow and photo mages precisely matched.
  • Compact design with flexible stand options for clinic or laboratory.
  • Unique protocol control — automation of pressure cuff, tissue heating and iontophoresis protocols with automated reporting, eases workflow and improves accuracy.
  • CE marking and FDA medical device clearance. Well established in the clinical and research communities for best performance and quality.
  • Laser stability hardware for the ultimate in reliable and consistent measurement over minutes, hours and days.

Please contact us, to discuss your specific application requirements with a Moor product specialist. Ask to see the new system in action, evaluate it at your own facility.

Please click here for an informative landmark article in the Institute of Physics publication, OLE (Optics and Lasers Europe). The article gives some background to the Full Field technique and offers a comprehensive history, from early beginnings to the current developments at Moor Instruments. Comments are featured from Dr David Briers, the originator of the speckle technique.

The following products are AVAILABLE TO BUY ONLINE and work with the moorFLPI-2

This section lists the more common questions our customers have with regards to the moorFLPI-2. If you have a question you would like answered that does not appear below then please email us. We are happy to help!

Q. What is the penetration depth of moorFLPI-2?
A. The penetration depth will depend on the optical properties of the tissue sampled as in conventional laser Doppler imaging; however, the signal processed which results in the speckle contrast image is biased towards light coming from the more superficial layers of the tissue. The effective penetration depth will be less than a conventional laser Doppler imager so will focus far more on the nutritive layers and will be less influenced by flow from deeper and larger vessels.

Q. What is the largest area you can image with moorFLPI-2?
A. The image area is dependent on the optical zoom used and the distance from the scan head to the tissue. This allows full flexibility to study areas from 5.6mm x 7.5mm up to 15cm x 20cm.

Q. What is the spatial resolution of the moorFLPI-2?
A. The moorFLPI-2 offers up to 1M pixels per square cm (50um in spatial mode at up to 25Hz and 10um in temporal mode at up to 1Hz).

Q. How can I assess dynamic responses with moorFLPI-2?
A. The moorFLPI-2 is used in the same way as a conventional laser Doppler imager - changes from a baseline are commonly assessed. The only difference is in the image acquisition rate with moorFLPI-2 providing 25 images per second opening up many new and exciting research opportunities.

Q. Can I image blood vessels with moorFLPI-2?
A. Yes, if the blood vessels lie in the surface of the tissue being imaged and if the tissue covering the vessels is effectively transparent to the laser light. This makes the technique ideally suited to cerebral imaging and general open surgery

Q. How often do I need to calibrate the system?
A. The moorFLPI-2 is factory calibrated. The user can check zeroing and calibration as frequently as required; we recommend to check calibration monthly.

Q. Can I analyse the data from moorFLPI-2?
A. Images can be analysed in much the same way as a conventional laser Doppler images and sequences allowing comparisons of flow within the same image or in the same subject over time. The video capability also allows the user to define up to 16 regions of interest (that can be varied in size, shape and position) and plot flow in real time from those regions - akin to a 16 channel laser Doppler monitor. Frame grabbing allows the user to select images from the video at flexible or pre defined intervals to build a sequence for analysis.

There are numerous references where our speckle contrast imagers are cited. The list below is a small selection. Please contact us for reference lists on your chosen subject.

Andersen, H. H., Gazerani, P., and Arendt-Nielsen, L., (2016).
High-concentration L-menthol exhibits counter-irritancy to neurogenic inflammation, thermal and mechanical hyperalgesia caused by TRPA1-agonist trans-cinnamaldehyde.
J Pain. pii: S1526-5900(16), pp30065-7.

Andersen, H. H., Lundgaard, A. C., Petersen, A. S., Hauberg, L. E., Sharma, N., Hansen, S. D., Elberling, J., and Arendt-Nielsen, L., (2016).
The Lancet Weight Determines Wheal Diameter in Response to Skin Prick Testing with Histamine.
PLoS One. 11(5).

Aubdool, A. A., Kodji, X., Abdul-Kader, N., Heads, R., Fernandes, E. S., Bevan, S., and Brain, S. D., (2016).
TRPA1 activation leads to neurogenic vasodilatation: Involvement of reactive oxygen nitrogen species in addition to CGRP and nitric oxide.
Br J Pharmacol. 173(15), pp:2419-33

Bezemer, R., Klijn, E., Khalilzada, M., Lima, A., Heger, M., Bommel , J . Van, and Ince, C., (2010).
Validation of near-infrared laser speckle imaging for assessing microvascular ( re ) perfusion.
Microvascular Research, 79(2), pp.139–143.

Bezemer, R., Legrand, M., Klijn, E., Heger, M., Post, I . C . J . H., van Gulik, T . M., Payen, D., and Ince, C., (2010).
Real-time assessment of renal cortical microvascular perfusion heterogeneities using near-infrared laser speckle imaging.
Optics express, 18(14), pp.15054–61.

Dusch, M., Schley, M., Rukwied, R., and Schmelz, M., (2007).
Rapid flare development evoked by current frequency-dependent stimulation analyzed by full-field laser perfusion imaging.
Neuroreport, 18(11), pp.1101–5.

Cowley, K., and Vanoosthuyze, K., (2016).
The biomechanics of blade shaving.
International Journal of Cosmetic Science. 38(Suppl 1), pp:17-2 3

Craighead, D. H., and Alexander, L. M., (2016).
Topical menthol increases cutaneous blood flow.
Microvasc Res., 107, pp:39-45.

Crapser, J., Ritzel, R., Verma, R., Venna, V. R., Liu, F., Chauhan, A., Koellhoffer, W.,, Patel, A., Ricker, A., Maas, K., Graf, J., and McCullough, L. D., (2016).
Ischemic stroke induces gut permeability and enhances bacterial translocation leading to sepsis in aged mice.
Aging (Albany NY). 8(5), pp:1049-63. doi: 10.18632/aging.100952

Gorbach, a. M., Wang, H., Wiedenbeck, B., Liu, W., Smith, P . D., and Elster, E., (2009).
Functional assessment of hand vasculature using infrared and laser speckle imaging.
Proceedings of SPIE, 7169, pp.716919–716919–9.

Hashimoto, T., Shibata, K., Nobe, K., Hasumi, K., and Honda, K., (2010).
A Novel Embolic Model of Cerebral Infarction and Evaluation of Stachybotrys microspora Triprenyl Phenol-7 (SMTP-7), a Novel Fungal Triprenyl Phenol Metabolite.
Journal of Pharmacological Sciences, 114(1), pp.41–49.

Hecht, N., Woitzik, J., Dreier, J . P., and Vajkoczy, P., (2009).
Intraoperative monitoring of cerebral blood flow by laser speckle contrast analysis.
Neurosurgical focus, 27(4), p.E11.

Hecht. N, Woitzik. J, König. S, Horn. P , V . P., (2013).
Laser speckle imaging allows real-time intraoperative blood flow assessment during neurosurgical procedures.
Journal of Cerebral Blood Flow & Metabolism, doi:10.103(33), pp.1000–1007.

Holstein-Rathlou, Henrik, N., Sosnovtseva , O . V, Pavlov, A . N., Cupples, W . a, Sorensen, C . M., and Marsh, D . J., (2011).
Nephron blood flow dynamics measured by laser speckle contrast imaging. American journal of physiology.
Renal physiology, 300(2), pp.F319–29.

Klijn, E., Hulscher, H . C., Balvers, R . K., Holland, W . P . J., Bakker, J., Vincent , A . J . P . E., Dirven, C . M . F., and Ince, C., (2013).
Laser speckle imaging identification of increases in cortical microcirculatory blood flow induced by motor activity during awake craniotomy.
Journal of neurosurgery, 118(2), pp.280–6.

Klijn, E., Niehof, S., de Jonge, J., Gommers, D., Ince, C., and van Bommel , J.,(2010).
The effect of perfusion pressure on gastric tissue blood flow in an experimental gastric tube model.
Anesthesia and analgesia, 110(2), pp.541–6.

McGuire, P . G., and Howdieshell, T . R., (2010).
The importance of engraftment in flap revascularization: confirmation by laser speckle perfusion imaging.
The Journal of surgical research, 164(1), pp.e201–12.

Milstein, D. M. J., Ince, C., Gisbertz, S. S., Boateng, K. B., Geerts, B. F., Hollmann, M. W., Henegouwen, M. I. van B., and Veelo, D. P., (2016).
Laser speckle contrast imaging identifies ischemic areas on gastric tube reconstructions following esophagectomy.
Medicine (Baltimore), 95(25).

Moretti, R., Leger, P. L., Besson, V. C., Csaba, Z., Pansiot, J., Di Criscio, L., Gentili, A., Titomanlio, L., Bonnin, P., Baud, O., and Charriaut-Marlangue, C., (2016).
Sildenafil, a cyclic GMP phosphodiesterase inhibitor, induces microglial modulation after focal ischemia in the neonatal mouse brain.
Journal of Neuroinflammation, 13(95), DOI: 10.1186/s12974-016-0560-4.

Scully, C., Mitrou, N., Braam, B., Cupples, W., and Chon, K., (2016).
Detecting Interactions between the Renal Autoregulation Mechanisms in Time and Space.
IEEE Trans Biomed Eng. [Epub ahead of print], DOI: 10.1109/TBME.2016.2569453.

Shen, Y. I., Cho, H., Papa, A. E., Burke, J. A., Chan, X. Y., Duh, E. J., and Gerecht, S., (2016).
Engineered human vascularized constructs accelerate diabetic wound healing.
Biomaterials, 102, pp:107-19.

Shih, C-C., Hsu, L-P., Liao, M-H., Yang, S-S., Wang, C-Y., Ho, S-T., and Wu, C-C., (2016).
Role of sterile 20/sps1-related proline/alanine-rich kinase in mice with endotoxic shock.
Journal of Medical Sciences, 36(3), pp.101-107.

Stanhewicz, A., (2014).
Laser-Speckle Contrast Imaging: A Novel Method for Assessment of Cutaneous Blood Flow in Perniosis.
JAMA …, pp.4–6.

Sun, Y .Y., Morozov, Y . M., Yang, D., Li, Y., Dunn, R . S., Rakic, P., Chan, P . H., Abe, K., Lindquist, D . M., and Kuan , C .Y., (2014).
Synergy of Combined tPA-Edaravone Therapy in Experimental Thrombotic Stroke.
PloS one, 9(6), p.e98807.

Themstrup, L., Welzel, J., Ciardo, S., Kaestle, R., Ulrich, M., Holmes, J., Whitehead, R., Sattler, E. C., Kindermann, N., Pellacani, G., and Jemec, G. B., (2016).
Validation of Dynamic optical coherence tomography for non-invasive, in vivo microcirculation imaging of the skin.
Microvascular Research, 107, pp:97-105.

Tian, Y., Huang, Litscher, G., Wang., Wang, G., Jia, S., Zhang, Y, Zhang , W., (2012).
Observation of Microvascular Perfusion in theHegu (LI4) Acupoint Area after Deqi Acupuncture at Quchi (LI11) Acupoint Using Speckle Laser Blood Flow Scanning Technology.

Wang, H., Deng, J., Tu, W., Zhang, L., Chen, H., Wu, X., Li, Y., and Sha, H., (2016).
The hematologic effects of low intensity 650 nm laser irradiation on hypercholesterolemia rabbits.
Am J Transl Res., 8(5), pp:2293-300.

Wang, Z., Schuler, B., Vogel, O., Arras, M., and Vogel, J., (2010).
What is the optimal anesthetic protocol for measurements of cerebral autoregulation in spontaneously breathing mice? Experimental brain research. Experimentelle Hirnforschung.
Expérimentation cérébrale, 207(3-4), pp.249–58.

Woitzik, J., Hecht, N., Pinczolits, A., Sandow, N., Major, S., Winkler, MK., Weber-Carsten, S., Dohmen, C., Graf,R., Strong, AJ., Dreier, JP., V . P . C . study group., (2013).
Propagation of cortical spreading depolarization in the human cortex after malignant stroke. Neurology.

Yu-Chang Yeh., Ming-Jiuh Wang., Chih-Peng Lin., Shou-Zen Fan., Jui-Chang Tsai, W .Z . S., (2012).
Enoxaparin sodium prevents intestinal microcirculatory dysfunction in endotoxemic rats. Critical Care.

Zhang, M.J., Sansbury, B.E., Hellmann, J., Baker, J.F., Guo, L., Parmer, C.M., Prenner, J.C., Conklin, D.J., Bhatnagar, A., Creager, M.A., and Spite, M., (2016).
Resolvin D2 enhances postischemic revascularization while resolving inflammation.
Circulation, 134(9), pp666-680.

Moor Instruments are committed to product development. We reserve the right to change the specifications below without notice.

Measurement Principle

Laser speckle contrast analysis (also known as LASCA).

Laser Safety Classification

Class 1 per IEC 60825-1:2007 — Safe to use without eye protection.


Factory Calibrated.

Image size

from 5.6mm x 7.5mm up to 20cm x 30cm (continuously variable with zoom lens).

Camera/Image Resolution

576 x 748 / 116 x 150 (spatial mode) up to 580 x 752 (temporal mode).

Image Acquisition Rate

From 25 images per second to 1 image every 12 hours.

Acquisition Modes

Single Point (16 channel), Single Image and Video mode.

Optical Design

Motorised optical zoom and auto focus. Single camera / RGB illumination to match colour photo and blood flow images.

Measurement Algorithms

Temporal and Spatial processing (including fixed and sliding window algorithms).

Pixel Resolution

Lowest resolution 14,500 pixels per cm² up to highest resolution of 1,000,000 pixels per cm².


New! V5, refined over 20 years according to customer demands including advanced image acquisition, processing, editing, functionality and analysis.

Stand Options

Scan head has standard VESA mount for desktop stand, Microstand and Clinical Mobile stand. Photographic fitting for use with tripods, etc.

PC Connections

1 x USB and 1 x Firewire (IEEE1394) port.

External Connections

Programmable trigger in / out function with BNC connections. USB connection of Moor Protocol modules for Pressure cuff control, Skin heating and Iontophoresis.


2 years, parts & labour, enhanced service contracts available.

Weights/ Dimensions

Scan head 23cm x 12cm x 25cm, Scan head 2.3kg.

Power Supply

Universal Voltage, 100V-230V. Note acquisition rate is unaffected by frequency of local electrical supply.