{"id":15820,"date":"2026-09-28T11:07:19","date_gmt":"2026-09-28T11:07:19","guid":{"rendered":"https:\/\/www.sanner-group.com\/?post_type=blog&p=15820"},"modified":"2026-09-28T12:31:16","modified_gmt":"2026-09-28T12:31:16","slug":"wearable-pump-design","status":"publish","type":"blog","link":"https:\/\/www.sanner-group.com\/insights\/blog\/wearable-pump-design\/","title":{"rendered":"Designing a Wearable Drug Delivery Pump\u00a0"},"content":{"rendered":"\n

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Wearable drug delivery pumps are reshaping how therapy is delivered. By moving controlled, continuous, and personalised dosing out of the clinic and onto the patient, they improve mobility, support home-based treatment, reduce hospital visits, and enable precise regimens over extended periods.<\/p>\n\n\n\n

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But a wearable pump is not a miniature pump strapped to the body. It is a safety-critical medical electrical system that must deliver the right dose, at the right rate, under shifting environmental, mechanical, electrical, and user conditions. Over-infusion, under-infusion, occlusion, unintended activation, software malfunction, battery failure, or a single mishandled interaction can all cause serious harm.<\/p>\n\n\n\n

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Safety therefore has to be a core design requirement from day one rather than a layer added before submission. A small group of standards frames the work: IEC 60601-1 sets the general requirements for basic safety and essential performance of medical electrical equipment; IEC 62304 defines the software lifecycle; IEC 60601-2-24 addresses infusion pumps and controllers specifically; and ISO 14971 provides the risk management process that ties them together.<\/p>\n\n\n\n

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The Opportunity<\/strong><\/p>\n\n\n\n


The central opportunity is bringing treatment closer to everyday life. Ambulatory therapy lets patients receive medication while remaining mobile, which is valuable across chronic conditions, oncology, insulin delivery, pain management, hormone therapy, and subcutaneous biologics.
Embedded electronics are what make accurate infusion possible. Sensors and closed-loop control support precise flow profiles with bolus and basal delivery, programmable schedules, and lockout periods tuned to the individual. Bluetooth, NFC, or cellular links add configuration, adherence tracking and remote diagnostics; designed well, they also give earlier warning of faults or misuse. Because the device is worn by the patient, it must also be compact, light, discreet, and intuitive. Meeting all of that at once pulls electronics, firmware, mechanical design, and human factors into a single coordinated effort.<\/p>\n\n\n\n

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Safety as the Primary Design Driver<\/strong> <\/p>\n\n\n\n


The core challenge is keeping the pump safe under normal use, foreseeable misuse, and single-fault conditions \u2014 what IEC 60601 calls maintaining basic safety and essential performance. For an infusion device, essential performance typically means accurate delivery rate, prevention of unintended delivery, occlusion detection, alarm generation, and safe shutdown.<\/p>\n\n\n\n


A safety-centred process starts with hazard identification and risk analysis under ISO 14971. Typical hazards for a wearable pump include:<\/p>\n\n\n\n


Over-delivery, under-delivery, or a missed dose
Downstream occlusion, upstream , or free flow
Air ingress
Liquid leakage
Incorrect cartridge installation or patient setup
Accidental use of incorrect drug
Battery depletion mid-therapy
Software lock-up or timing failure
Wireless interference or cybersecurity vulnerabilities
Mechanical damage from impact, moisture, or body movement<\/p>\n\n\n\n


Each hazard must trace to a specific risk control – mechanical, electrical, software, procedural, or, most often, several layers working together.

<\/a> Occlusion and blockage seem to be the same thing. If they are different, could you add a word to two to differentiate them? role requires skills in both of my degree areas, so I\u2019m thankful for the way they prepared me to work in unexpected ways. The psychological aspect is the need to be very empathetic toward users. And as far as engineering goes, while I\u2019m not directly designing products anymore, I communicate with engineers about how to improve their designs. <\/p>\n\n\n\n

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It might seem like my job is to represent the client, but it isn\u2019t. My job is to represent the end user, advocating for their interests to both the client and our engineering team. <\/p>\n\n\n

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Interlocks: A Key Safety Mechanism <\/strong><\/p>\n\n\n\n


An interlock prevents the device from entering a hazardous state unless defined safety conditions are met. In a pump these can live in hardware, software, mechanical design, or the user workflow. These can include cartridge-presence detection, reservoir-door closure, cannula-insertion confirmation, priming and bolus lockouts, occlusion-triggered stops, battery undervoltage lockout, and drug-container authentication.<\/p>\n\n\n\n


A cartridge interlock, for instance, can block operation until the drug cartridge is correctly seated \u2014 implemented with a switch, Hall-effect sensor, optical sensor, RFID tag, or coded mechanical feature. A door interlock can prevent pumping while a reservoir or access panel is open; a priming interlock can stop delivery to the patient while the device is still priming.<\/p>\n\n\n\n


Interlocks are not convenience features. They are risk controls, which means they must be specified, verified, validated, and traceable to the hazards they address. IEC 62304 requires relevant software to be developed through a controlled lifecycle, with the software safety classification setting the level of rigour. <\/p>\n\n\n\n

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Redundancy and Dual-Processor Architectures<\/strong><\/p>\n\n\n\n


For high-risk delivery functions, a single microcontroller controlling the pump, reading sensors, managing alarms, and supervising its own safety may not be enough: one software fault, timing error, memory corruption, or lock-up could drive unsafe delivery.<\/p>\n\n\n\n


A redundant architecture mitigates the single points of failure. A primary processor runs pump operation and the user interface; an independent safety processor monitors the critical parameters \u2014 motor activity, delivery timing, pressure readings, battery voltage, watchdog signals, and state transitions. If the primary processor misbehaves, the safety processor can disable the actuator, raise an alarm, force a safe state, and log the fault, creating an independent layer that does not depend on the main control path.<\/p>\n\n\n\n


A robust dual-processor design typically includes:
Independent watchdog monitoring between processors
Separate clock sources for timing supervision
Independent measurement of motor actuation or flow-related signals
Hardware-controlled pump-enable lines
Safety-processor authority to disable delivery
Cross-checking of dose counters and therapy state
Non-volatile fault logging and a defined safe state after a fault<\/p>\n\n\n\n


Redundancy is not free: a second processor adds communication, synchronisation, power, verification, PCB area, and test burden. It should be justified by risk analysis, not added by reflex. <\/p>\n\n\n\n

Software Safety Under IEC 62304<\/strong><\/p>\n\n\n\n


Software sits at the centre of pump safety by providing dosing algorithms, motor actuation, alarms, user input, connectivity, logging, and fault detection. IEC 62304 calls for a structured lifecycle: planning, requirements, architecture, detailed design, implementation, verification, integration testing, release, maintenance, configuration management, and problem resolution.<\/p>\n\n\n\n


Safety-related behaviour should be captured as explicit requirements, for example:<\/p>\n\n\n\n


Stop delivery when occlusion pressure exceeds the defined threshold
Prevent bolus delivery during lockout periods
Detect motor stall and enter a safe state
Alarm before remaining battery capacity is insufficient for therapy
Prevent therapy start if the cartridge is missing or misfitted
Record safety-critical faults with timestamps
Transition to a predefined safe state after watchdog timeout<\/p>\n\n\n\n


Architecture should isolate safety-critical functions from the rest. Wireless and mobile-app features must never command delivery without passing through safety checks, and the therapy-control layer should be insulated from faults in the UI or communication layers. <\/p>\n\n\n\n

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IEC 60601 Considerations<\/strong><\/p>\n\n\n\n


As a medical electrical device, a wearable pump falls under IEC 60601-1 for protection against electrical and mechanical hazards, excessive temperature, abnormal operation, and single faults. Three collateral standards matter especially here:
IEC 60601-1-11 covers equipment used in the home environment, which is relevant because patients or carers, not clinicians, operate the device.
IEC 60601-1-2 covers electromagnetic compatibility, which matters because a worn device sits among phones, chargers, wireless networks, and security systems all day.
For infusion-specific requirements, IEC 60601-2-24 covers ambulatory, syringe, volumetric, and controller pumps.<\/p>\n\n\n\n

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Key Engineering Challenges<\/strong><\/p>\n\n\n\n


Dose accuracy<\/p>\n\n\n\n


Pump mechanism, motor control, reservoir design, tubing compliance, pressure variation, fluid viscosity, temperature, and body position all influence delivery. The design needs calibration, verification, and fault detection that keep dosing within acceptable limits.<\/p>\n\n\n\n


Occlusion detection<\/p>\n\n\n\n


Low flow rates and small volumes make occlusions hard to catch. Pressure sensing, motor-current monitoring, flow estimation, or displacement sensing may all be needed. The real difficulty is detecting genuine occlusions quickly without flooding the user with false alarms.<\/p>\n\n\n\n

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Power management<\/p>\n\n\n\n


The device must be small and battery-powered, yet watchdogs, alarms, clock accuracy, memory integrity, and fault monitoring have to stay alive throughout therapy. Low-power design must never quietly disable a safety function, and undervoltage behaviour must be predictable and safe.<\/p>\n\n\n\n


Human factors<\/p>\n\n\n\n


Users may have limited training, impaired vision, reduced dexterity, or anxiety about treatment. The device should minimise setup errors, give clear feedback, and make unsafe actions hard \u2014 through interlocks, guided workflows, alarms, and physical keying.<\/p>\n\n\n\n


Environmental robustness<\/p>\n\n\n\n


Sweat, moisture, vibration, impact, temperature swings, and constant movement all act on a worn device. Enclosure design, ingress protection, connector reliability, adhesive performance, and mechanical retention all need deliberate attention.
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A Recommended Safety Architecture<\/p>\n\n\n\n


A safety-focused wearable pump should layer its risk controls: a primary control processor, an independent safety processor, motor-driver enable control, cartridge and door interlocks, pressure sensing, motor feedback, battery monitoring, audible and visual alarms, non-volatile fault logging, and a secure communication interface.<\/p>\n\n\n\n


The primary processor handles scheduling, UI, connectivity, and normal pump control. The safety processor independently checks that the primary is behaving, and critical outputs such as the motor-enable signal pass through a safety gate the safety processor or hardware fault logic can pull. Crucially, safety should not rest on software alone. Wherever possible, hardware interlocks and independent monitoring stop a single fault from reaching the patient.
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Wearable pumps open real opportunities for patient-centred, remote, and personalised care, but because the device controls medication directly, safety has to be designed into the architecture from the outset. IEC 60601 frames basic safety and essential performance, IEC 62304 governs the software lifecycle, IEC 60601-2-24 covers infusion specifics, and ISO 14971 ties the risk picture together.<\/p>\n\n\n\n


The safest designs do not lean on one perfect component or one flawless routine. They are layered systems in which foreseeable failures are detected, controlled, and stopped before they reach the patient. Building those layers well is, in the end, an electronics and embedded-systems problem as much as a clinical one.<\/p>\n\n\n\n

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